SILICONE HYDROGELS COMPRISING POLYAMIDES

Description

TECHNICAL FIELD

[0001] The present invention relates to ionic silicone hydrogels displaying improved biocompatibility. More specifically, the present invention relates to a polymer formed from reactive components comprising at least one hydrophilic monomer, at least two hydroxyl substituted silicone containing components having different silicone contents, and at least one acyclic polyamide. The silicone hydrogels of the present invention display excellent physical, mechanical, and biological properties, making them suitable for ophthalmic applications such as contact lens materials.

BACKGROUND

[0002] It is well known that contact lenses can be used to improve vision. Various contact lenses have been commercially produced for many years. Hydrogel contact lenses are formed from hydrophilic polymers and copolymers containing repeating units such as 2-hydroxyethyl methylacrylate (HEMA). Of these, contact lenses formed from copolymers of HEMA and methacrylic acid, are among the most comfortable, and have the lowest rate of adverse events. Contact lenses formed from copolymers of HEMA and MAA, such ACUVUE^®2 brand contact lenses, display substantial amounts of lysozyme uptake (greater than 500 µg) and retain a majority of the uptaken proteins in their native state. However, hydrogel contact lenses generally have oxygen permeabilities that are less than about 30.

[0003] Contact lenses made from silicone hydrogels have been disclosed. These silicone hydrogel lenses have oxygen permeabilities greater than about 60, and many provide reduced levels of hypoxia compared to conventional hydrogel contact lenses. Silicone hydrogel lenses may be exposed to extended periods of wear such as for several days in a row, for example, up to about 30 days.
US 2007/222095 discloses aqueous processes for the production of silicone hydrogel contact lenses.
US 2012/245248 discloses silicone hydrogels formed from mixtures comprising one or more hydrophilic high molecular weight polymers, one or more hydroxyl-functionalized silicone containing monomers, one or more crosslinkers and a compatabilizing diluent, but without a substantial amount of a reactive hydrophilic monomer or macromer.
US 2013/184372 discloses a silicone polymer comprising a sulfonic acid component formed from reactive components comprising (i) at least one silicone component and (ii) at least one sulfonic acid-containing component, wherein the sulfonic acid-containing component is comprised of a non-polymerizable, hydrophobic cation and a polymerizable sulfonic acid.

[0004] U.S. Patent No. 8,815,972 (Rathore) is directed to ionic silicone hydrogels having improved hydrolytic stability and desirable protein uptake.

[0005] U.S. Patent No. 7,786,185 is directed to wettable hydrogels comprising acyclic polyamides.

SUMMARY

[0006] The invention is defined by the claims. Silicone hydrogels disclosed herein exhibit improved biocompatibility with regards to interactions and absorption of tear film components as well as interactions and absorption of preservatives used for disinfecting contact lenses made from such silicone hydrogels. The lack of protein, lipid, or other biological deposits on the surface of contact lenses may limit, reduce, or eliminate any immunological responses or microbial fouling.

[0007] For reusable wear modalities, in which contact lenses are disinfected with multipurpose cleaning solutions between uses, another important characteristic of biocompatibility is low absorption of preservatives which may be released into the ocular environment upon subsequent wear.

[0008] The silicone hydrogels of the present invention exhibit many of these biocompatible properties, while achieving an excellent balance of physical and mechanical properties.

[0009] The present invention provides a silicone hydrogel formed from a reactive monomer mixture comprising:

a. between about 1 and about 15 wt% at least one polyamide;

b. at least one first mono-functional, hydroxyl substituted poly(disubstituted siloxane) having 4 to 8 siloxane repeating units;

c. at least one second hydroxyl substituted poly(disubstituted siloxane) selected from the group consisting of mono-functional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200 or 10-100 siloxane repeating units and multifunctional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200, or 10 to 100 siloxane repeating units, and mixtures thereof;

d. about 5 to about 30 wt% at least one additional hydrophilic monomer;

e. wherein the first hydroxyl substituted, linear poly(disubstituted siloxane) and the second mono-functional hydroxyl substituted, linear poly(disubstituted siloxane) are present in concentrations to provide a ratio of wt% of all first hydroxyl substituted, linear poly(disubstituted siloxane) to wt% of all one second hydroxyl substituted poly(disubstituted siloxane)s of 0.4-1.3, or 0.4-1.0.

[0010] The present invention provides a silicone hydrogel formed from a reactive monomer mixture comprising:

i. between about 1 and about 15 wt% at least one polyamide;

ii. at least one hydroxyl silicone-containing monomer;

iii. at least one hydroxyl substituted poly(disubstituted siloxane) selected from the group consisting of poly(disubstituted siloxane) having 4 to 8 siloxane repeating units, monofunctional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200 or 10-100 siloxane repeating units and multifunctional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200, or 10 to 100 siloxane repeating units, and mixtures thereof;

iv. about 5 to about 20 wt% at least one additional hydrophilic monomer;

v. wherein the first hydroxyl substituted, linear poly(disubstituted siloxane) and the second monofunctional hydroxyl substituted, linear poly(disubstituted siloxane) are present in concentrations to provide a ratio of wt% of all first hydroxyl substituted, linear poly(disubstituted siloxane) to wt% of all one second hydroxyl substituted poly(disubstituted siloxane)s of 0.4-1.3, or 0.4-1.0.

[0011] The present invention also provides biomedical devices, ophthalmic devices and contact lenses comprising the silicone hydrogels described herein.

[0012] These and other embodiments of the invention will become apparent from the following description, which are illustrative of the invention. The description does not limit the scope of the invention, which is defined by the claims and equivalents thereof. Variations and modifications of the invention may be effected without departing from the scope of the novel contents of the disclosure.

DETAILED DESCRIPTION

[0013] Provided are silicone hydrogels formed from a reactive monomer mixture comprising: a first hydroxyl substituted, linear poly(disubstituted siloxane) having 4 to 8 siloxane repeating units; a second hydroxyl substituted, linear poly(disubstituted siloxane) selected from the group consisting of a monofunctional hydroxyl substituted, linear poly(disubstituted siloxane) having 10 to 20 siloxane repeating units and a multifunctional hydroxyl substituted, linear poly(disubstituted siloxane) having 10 to 200, or 10 to 100 siloxane repeating units; and at least one polyamide; wherein the ratio of the first hydroxyl substituted linear poly(disubstituted siloxane) to the second hydroxyl substituted, linear poly(disubstituted siloxane) is in a range of 0.4 to 1.2, or 0.4 to 1.0.

[0014] With respect to the terms used in this disclosure, the following definitions are provided. The polymer definitions are consistent with those disclosed in the Compendium of Polymer Terminology and Nomenclature, IUPAC Recommendations 2008, edited by: Richard G. Jones, Jaroslav Kahovec, Robert Stepto, Edward S. Wilks, Michael Hess, Tatsuki Kitayama, and W. Val Metanomski.

[0015] As used herein, the term "about" refers to a range of +/-5% of the number that is being modified. For example, the phrase "about 10" would include both 9.5 and 10.5.

[0016] The term "(meth)" designates optional methyl substitution. Thus, a term such as "(meth)acrylate" denotes both methacrylate and acrylate radicals.

[0017] Wherever chemical structures are given, it should be appreciated that alternatives disclosed for the substituents on the structure may be combined in any combination. Thus, if a structure contained substituents R* and R**, each of which contained three lists of potential groups, 9 combinations are disclosed. The same applies for combinations of properties.

[0018] When a subscript, such as "n" in the generic formula [***]_n, is used to depict the number of repeating units in a polymer's chemical formula, the formula should be interpreted to represent the number average molecular weight of the macromolecule.

[0019] A "macromolecule" is an organic compound having a molecular weight of greater than 1500, and may be reactive or non-reactive.

[0020] A "polymer" is a macromolecule of repeating chemical units linked together into a chain or network structure and is composed of repeating units derived from the monomers and macromers included in the reactive mixture.

[0021] A "homopolymer" is a polymer made from one monomer or macromer; a "copolymer" is a polymer made from two or more monomers, macromers or a combination thereof; a "terpolymer" is a polymer made from three monomers, macromers or a combination thereof. A "block copolymer" is composed of compositionally different blocks or segments. Diblock copolymers have two blocks. Triblock copolymers have three blocks. "Comb or graft copolymers" are made from at least one macromer.

[0022] A "repeating unit" or "repeating chemical unit" is the smallest repeating group of atoms in a polymer that result from the polymerization of monomers and macromers.

[0023] "Biomedical device" is any article that is designed to be used while either in or on mammalian tissues or fluid, and preferably in or on human tissue or fluids. Examples of these devices include but are not limited to wound dressings, sealants, tissue fillers, drug delivery systems, coatings, adhesion prevention barriers, catheters, implants, stents, sutures, and ophthalmic devices such as intraocular lenses and contact lenses. The biomedical devices may be ophthalmic devices, such as contact lenses, including contact lenses made from silicone hydrogels.

[0024] "Individual" includes humans and vertebrates.

[0025] "Ocular surface" includes the surface and glandular epithelia of the cornea, conjunctiva, lacrimal gland, accessory lacrimal glands, nasolacrimal duct and meibomian gland, and their apical and basal matrices, puncta and adjacent or related structures, including eyelids linked as a functional system by both continuity of epithelia, by innervation, and the endocrine and immune systems.

[0026] "Ophthalmic device" refers to any device which resides in or on the eye or any part of the eye, including the ocular surface. These devices can provide optical correction, cosmetic enhancement, vision enhancement, therapeutic benefit (for example as bandages) or delivery of active components such as pharmaceutical and nutraceutical components, or a combination of any of the foregoing. Examples of ophthalmic devices include, but are not limited to, lenses and optical and ocular inserts, including, but not limited to punctal plugs and the like. The "term lens" includes soft contact lenses, hard contact lenses, hybrid contact lenses, intraocular lenses, and overlay lenses. The ophthalmic device may comprise a contact lens.

[0027] "Contact lens" refers to an ophthalmic device that can be placed on the cornea of an individual's eye. The contact lens may provide corrective, cosmetic, therapeutic benefit, including wound healing, delivery of active components such as drugs or neutraceuticals, diagnostic evaluation or monitoring, or UV blocking and visible light or glare reduction, or a combination thereof. A contact lens can be of any appropriate material known in the art, and can be a soft lens, a hard lens, or a hybrid lens containing at least two distinct portions with different properties, such as modulus, water content, light absorbing characteristics or combinations thereof.

[0028] The biomedical devices, ophthalmic devices, and lenses of the present invention may be comprised of silicone hydrogels. These silicone hydrogels typically contain a silicone component and/or hydrophobic and hydrophilic monomers that are covalently bound to one another in the cured device.

[0029] "Silicone hydrogel contact lens" refers to a contact lens comprising at least one silicone hydrogel material. Silicone hydrogel contact lenses generally have increased oxygen permeability compared to conventional hydrogels. Silicone hydrogel contact lenses use both their water and polymer content to transmit oxygen to the eye.

[0030] A "polymeric network" is cross-linked macromolecule that can swell but cannot dissolve in solvents, because the polymeric network is essentially one macromolecule. "Hydrogel" or "hydrogel material" refers to a polymeric network that contains water in an equilibrium state. Hydrogels generally contain at least about 10 wt.% water, or at least about 15 wt.% water

[0031] " Conventional hydrogels" refer to polymeric networks made from monomers without any siloxy, siloxane or carbosiloxane groups. Conventional hydrogels are prepared from monomeric mixtures predominantly containing hydrophilic monomers, such as 2-hydroxyethyl methacrylate ("HEMA"), N-vinyl pyrrolidone ("NVP"), N, N-dimethylacrylamide ("DMA"), or vinyl acetate. United States Patent Nos. 4,436,887, 4,495,313, 4,889,664, 5,006,622, 5,039459, 5,236,969, 5,270,418, 5,298,533, 5,824,719, 6,420,453, 6,423,761, 6,767,979, 7,934,830, 8,138,290, and 8,389,597 disclose the formation of conventional hydrogels. Commercially available hydrogel formulations include, but are not limited to, etafilcon, polymacon, vifilcon, genfilcon, lenefilcon, hilafilcon, nesofilcon, and omafilcon, including all of their variants.

[0032] "Silicone hydrogel" refers to a hydrogel obtained by copolymerization of at least one silicone-containing component with at least one hydrophilic component. Hydrophilic components may also include non-reactive polymers. Each of the silicone-containing components and the hydrophilic components may be a monomer, macromer or combination thereof. A silicone-containing component contains at least one siloxane or carbosiloxane group. Examples of commercially available silicone hydrogels include balafilcon, acquafilcon, lotrafilcon, comfilcon, delefilcon, enfilcon, fanfilcon, foimofilcon, galyfilcon, senofilcon, narafilcon, falcon II, asmofilcon A, samfilcon, riofilcon, stenficlon, somofilcon, as well as silicone hydrogels as prepared in US Patent Nos. 4,659,782, 4,659,783, 5,244,981, 5,314,960, 5,331,067, 5,371,147, 5,998,498, 6,087,415, 5,760,100, 5,776,999, 5,789,461, 5,849,811, 5,965,631, 6,367,929, 6,822,016, 6,867,245, 6,943,203, 7,247,692, 7,249,848, 7,553,880, 7,666,921, 7,786,185, 7,956,131, 8,022,158, 8,273,802, 8,399,538, 8,470,906, 8,450,387, 8,487,058, 8,507,577, 8,637,621, 8,703,891, 8,937,110, 8,937,111, 8,940,812, 9,056,878, 9,057,821, 9,125,808, 9,140,825, 9156,934, 9,170,349, 9,244,196, 9,244,197, 9,260,544, 9,297,928, 9,297,929 as well as WO 03/22321, WO 2008/061992, and US 2010/048847.

[0033] "Silicone-containing component" refers to a monomer, macromer, prepolymer, cross-linker, initiator, additive, or polymer that contains at least one silicon-oxygen bond, in the form of siloxane [-Si-O-Si] group or carbosiloxane group. Examples of silicone-containing components include, but are not limited to, silicone macromers, prepolymers, and monomers. Examples of silicone macromers include, but are not limited to, polydimethylsiloxane methacrylated with pendant hydrophilic groups. Examples of silicone-containing components which are useful in this invention may be found in U.S. Patent Nos. 3,808,178, 4,120,570, 4,136,250, 4,153,641, 4,740,533, 5,034,461, 5,962,548, 5,244,981, 5,314,960, 5,331,067, 5,371,147, 5,760,100, 5,849,811, 5,962,548, 5,965,631, 5,998,498, 6,367,929, 6,822,016, and 5,070,215, and European Patent No. 080539.

[0034] "Reactive mixture" and "reactive monomer mixture" refer to the mixture of components (both reactive and non-reactive) which are mixed together and when subjected to polymerization conditions, form the silicone hydrogels and lenses of the present invention. The reactive mixture comprises reactive components such as monomers, macromers, prepolymers, cross-linkers, initiators, diluents, and additional components such as wetting agents, release agents, dyes, light absorbing compounds such as UV absorbers, pigments, dyes and photochromic compounds, any of which may be reactive or non-reactive but are capable of being retained within the resulting biomedical device, as well as active components such as pharmaceutical and nutraceutical compounds, and any diluents. It will be appreciated that a wide range of additives may be added based upon the biomedical device which is made, and its intended use. Concentrations of components of the reactive mixture are given in weight % of all components in the reaction mixture, excluding diluent. When diluents are used their concentrations are given as weight % based upon the amount of all components in the reaction mixture and the diluent.

[0035] "Monomer" is a molecule having non-repeating functional groups, which can undergo chain growth polymerization, and in particular, free radical polymerization. Some monomers have di-functional impurities that can act as cross-linking agents. "Macromers" are linear or branched polymers having a repeating structure and at least one reactive group that can undergo chain growth polymerization. Monomethacryloxypropyl terminated mono-n-butyl terminated polydimethylsiloxane (molecular weight = 500-1500 g/mol) (mPDMS) and mono-(2-hydroxy-3-methacryloxypropyl)-propyl ether terminated mono-n-butyl terminated polydimethylsiloxane (molecular weight = 500-1500 g/mol) (OH-mPDMS) are referred to as macromers. Typically, the chemical structure of the macromer is different than the chemical structure of the target macromolecule, that is, the repeating unit of the macromer's pendent group is different than the repeating unit of the target macromolecule or its mainchain.

[0036] "Reactive components" are the components in the reactive mixture which become part of the structure of the polymeric network of the resulting silicone hydrogel, by covalent bonding, hydrogen bonding or the formation of an interpenetrating network. Diluents and processing aids which do not become part of the structure of the polymer are not reactive components.

[0037] "Polymerizable" means that the compound comprises at least one reactive group which can undergo chain growth polymerization, such as free radical polymerization. Examples of reactive groups include the monovalent reactive groups listed below. "Non-polymerizable" means that the compound does not comprises such a polymerizable group.

[0038] "Monovalent reactive groups" are groups that can undergo chain growth polymerization, such as free radical and/or cationic polymerization. Non-limiting examples of free radical reactive groups include (meth)acrylates, styrenes, vinyl ethers, (meth)acrylamides, N-vinyllactams, N-vinylamides, O-vinylcarbamates, O-vinylcarbonates, and other vinyl groups. In one embodiment, the free radical reactive groups comprise (meth)acrylate, (meth)acrylamide, N-vinyl lactam, N-vinylamide, and styryl functional groups, or (meth)acrylates, (meth)acrylamides, and mixtures of any of the foregoing.

[0039] Examples of the foregoing include substituted or unsubstituted C_1-6alkyl(meth)acrylates, C_1-6alkyl(meth)acrylamides, C_2-12alkenyls, C_2-12alkenylphenyls, C_2-12alkenylnaphthyls, C_2-6alkenylphenylC_1-6alkyls, where suitable substituents on said C_1-6 alkyls include ethers, hydroxyls, carboxyls, halogens and combinations thereof.

[0040] Other polymerization routes such as living free radical and ionic polymerization can also be employed. The device-forming monomers may form hydrogel copolymers. For hydrogels, the reactive mixture will typically include at least one hydrophilic monomer.

[0041] Hydrophilic components are those which yield a clear single phase when mixed with deionized water at 25°C at a concentration of 10 wt.%.

[0042] "Interpenetrating polymer networks" or "IPNs" are polymers comprising two or more polymeric networks which are at least partially interlaced on a molecular scale, but not covalently bonded to each other and cannot be separated unless chemical bonds are broken.

[0043] "Semi-interpenetrating polymer networks" or "semi-IPNs" are polymer comprising one or more polymer network(s) and one or more linear or branched polymer(s) characterized by the penetration on a molecular scale of at least one of the networks by at least some of the linear or branched chains.

[0044] A "cross-linking agent" is a di-functional or multi-functional component which can undergo free radical polymerization at two or more locations on the molecule, thereby creating branch points and a polymeric network. Common examples are ethylene glycol dimethacrylate, tetraethylene glycol dimethacrylate, trimethylolpropane trimethacrylate, methylene bisacrylamide, triallyl cyanurate, and the like.

[0045] The phrase "without a surface treatment" means that the exterior surfaces of the devices (e.g. silicone hydrogels, contact lenses) of the present invention are not separately treated to improve the wettability of the device. Treatments which may be foregone include, plasma treatments, grafting, coating, and the like. Coatings, however, which provide properties other than improved wettability, such as, but not limited to antimicrobial coatings and the application of color or other cosmetic enhancement may be applied to devices of the present invention.

[0046] Non-SI units disclosed in this description are convertible as following:

• 1 inch = 25.4 mm
• 1 psi = 6894.76 Pa
• 1 lb = 453.592 g.

[0047] A silicone hydrogel may be formed from a reactive monomer mixture comprising at least one anionic monomer, at least one first mono-functional hydroxyl-substituted poly(disubstituted siloxane), at least one second mono-functional hydroxyl-substituted poly(disubstituted siloxane), at least one hydroxyl functional monomer, and at least one acylic polyamide.

Polyamide

[0048] The reactive monomer mixture includes at least one polyamide. As used herein, the term "polyamide" refers to polymers and copolymers comprising repeating units containing amide groups. The polyamide may comprise cyclic amide groups, acyclic amide groups and combinations thereof, and may be any polyamide known to those of skill in the art.

[0049] Acyclic polyamides comprise pendant acyclic amide groups and are capable of association with hydroxyl groups. Cyclic polyamides comprise cyclic amide groups and are capable of association with hydroxyl groups.

[0050] Examples of suitable acyclic polyamides include polymers and copolymers comprising repeating units of Formula I or Formula II:

wherein X is a direct bond, -(CO)-, or -(CO)-NHR^e-, wherein R^e is a C₁ to C₃ alkyl group; R^a is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups; R^b is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups, amino groups having up to two carbon atoms, amide groups having up to four carbon atoms, and alkoxy groups having up to two carbon groups; R^c is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups, or methyl, ethoxy, hydroxyethyl, and hydroxymethyl; R^d is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups; or methyl, ethoxy, hydroxyethyl, and hydroxymethyl wherein the number of carbon atoms in R^a and R^b taken together is 8 or less, including 7, 6, 5, 4, 3, or less, and wherein the number of carbon atoms in R^c and R^d taken together is 8 or less, including 7, 6, 5, 4, 3, or less. The number of carbon atoms in R^a and R^b taken together may be 6 or less or 4 or less. The number of carbon atoms in R^c and R^d taken together may be 6 or less. As used herein substituted alkyl groups include alkyl groups substituted with an amine, amide, ether, hydroxyl, carbonyl, carboxy groups or combinations thereof.

R^a and R^b can be independently selected from H, substituted or unsubstituted C₁ to C₂ alkyl groups. X may be a direct bond, and R^a and R^b may be independently selected from H, substituted or unsubstituted C₁ to C₂ alkyl groups.

R^c and R^d can be independently selected from H, substituted or unsubstituted C₁ to C₂ alkyl groups, methyl, ethoxy, hydroxyethyl, and hydroxymethyl.

[0051] The acyclic polyamides of the present invention may comprise a majority of the repeating unit of Formula I or Formula II, or the acyclic polyamides can comprise at least about 50 mole % of the repeating unit of Formula I or Formula II, including at least about 70 mole %, and at least 80 mole %.

[0052] Specific examples of repeating units of Formula I and Formula II include repeating units derived from N-vinyl-N-methylacetamide, N-vinylacetamide, N-vinyl-N-methylpropionamide, N-vinyl-N-methyl-2-methylpropionamide, N-vinyl-2-methyl-propionamide, N-vinyl-N,N'-dimethylurea, N, N-dimethylacrylamide, methacrylamide, and acyclic amides of Formulae IIIa and IIIb:

[0053] The acyclic polyamides may also be copolymers comprising both acyclic and cyclic amide repeating units. Examples of suitable cyclic amides that can be used to form the acyclic polyamides include α-lactam, β-lactam, γ-lactam, δ-lactam, and ε-lactam. Examples of suitable cyclic amides include repeating units of Formula IV:

wherein R¹ is independently a hydrogen atom or methyl; f is a number from 1 to 10, X is a direct bond, -(CO)-, or -(CO)-NH-R^e-, wherein R^e is a C₁ to C₃ alkyl group. In Formula IV, f may be 8 or less, including 7, 6, 5, 4, 3, 2, or 1. In Formula IV, f may be 6 or less, including 5, 4, 3, 2, or 1. In Formula IV, f may be from 2 to 8, including 2, 3, 4, 5, 6, 7, or 8. In Formula IV, f may be 2 or 3.

[0054] When X is a direct bond, f may be 2. In such instances, the cyclic polyamide may be poly(vinyl pyrrolidone) (PVP).

[0055] Specific examples of repeating units of Formula IV include repeating units derived from N-vinylpyrrolidone (NVP).

[0056] Additional repeating units may be formed from monomers selected from N-vinyl amides, acrylamides, hydroxyalkyl(meth)acrylates, alkyl(meth)acrylates and siloxane substituted acrylates or methacrylates. Specific examples of monomers which may be used to form the additional repeating units of the acyclic polyamides include as N-vinylpyrrolidone, N,N-dimethylacrylamide (DMA), 2-hydroxyethylmethacrylate, vinyl acetate, acrylonitrile, hydroxypropyl methacrylate, 2-hydroxyethyl acrylate, methyl methacrylate and butyl methacrylate, hydroxybutyl methacrylate, GMMA, PEGS, , and the like and mixtures thereof. Ionic monomers may also be included. Examples of ionic monomers include acrylic acid, methacrylic acid, 2-methacryloyloxyethyl phosphorylcholine, 3-(dimethyl(4-vinylbenzyl)ammonio)propane-1-sulfonate (DMVBAPS), 3-((3-acrylamidopropyl)dimethylammonio)propane-1-sulfonate (AMPDAPS), 3-((3-methacrylamidopropyl)dimethylammonio)propane-1-sulfonate (MAMPDAPS), 3-((3-(acryloyloxy)propyl)dimethylammonio)propane-1-sulfonate (APDAPS), methacryloyloxy)propyl)dimethylammonio)propane-1-sulfonate (MAPDAPS), ), 1-propanaminium,N-(2-carboxyethyl)-N,N-dimethyl-3-[(1-oxo-2-propen-1-yl)amino]-, inner salt (CBT, carboxybetaine; CAS 79704-35-1), 1-propanaminium, N,N-dimethyl-N-[3-[(1-oxo-2-propen-1-yl)amino]propyl]-3-sulfo-, inner salt (SBT, sulfobetaine, CAS 80293-60-3), 3,5-Dioxa-8-aza-4-phosphaundec-10-en-1-aminium, 4-hydroxy-N,N,N-trimethyl-9-oxo-, inner salt, 4-oxide (9CI) (PBT, phosphobetaine, CAS 163674-35-9).

[0057] The at least one acylic polyamide may be selected from the group consisting of polyvinylmethylacrylamide (PVMA), polyvinylacetamide (PNVA), polydimethylacrylamide (PDMA), polyacrylamide and poly[N-vinyl N-alkyl acetamide] wherein the N-alkyl group is selected from the group consisting of linear and branched alkyl groups containing between one (C₁) and five (C₅) carbon atoms.

[0058] The reactive monomer mixture may comprise both an acyclic polyamide and a cyclic polyamide or copolymers thereof. The acyclic polyamide can be any of those acyclic polyamides described herein or copolymers thereof, and the cyclic polyamide can be formed from any combination of the repeating units of Formula IV, either alone or with other repeating units. Examples of cyclic polyamides include PVP and PVP copolymers. Other polymeric internal wetting agents, such as poly(hydroxyethyl(meth)acrylamide), may also be included.

[0059] Without intending to be bound by theory, the polyamide functions as an internal wetting agent in the resulting silicone hydrogel. The polyamides of the present invention may be non-polymerizable, and in this case is incorporated into the silicone hydrogels as a semi-interpenetrating network. The non-polymerizable polyamide is "entrapped", or physically retained within a hydrogel matrix. Alternatively, the polyamides of the present invention may be polymerizable, for example as polyamide macromers, which are covalently incorporated into the silicone hydrogels. Reactive polyamides may be functionalized to contain at least one monovalent reactive group.

[0060] When the polyamides are incorporated into the reactive monomer mixture they may have a weight average molecular weight of at least about 100,000 Daltons; greater than about 150,000; between about 150,000 to about 2,000,000 Daltons, between about 300,000 to about 1,800,000 Daltons.

[0061] The polyamides may also comprise at least one reactive group. For polyamides having molecular weights of 10,000 Daltons, a single reactive group may be included. For polyamides having molecular weights greater than about 10,000, greater than about 30,000, or greater than about 100,000 Daltons, more than one reactive group may be included. Mixtures of reactive and non-reactive polyamides may also be used.

[0062] The polyamides may be incorporated into the hydrogel by a variety of methods. For example, the polyamide may be added to the reaction mixture such that the hydrogel polymerizes "around" the polyamide, forming a semi-interpenetrating network.

[0063] The total amount of all polyamides in the reactive mixture may be from about 1 to about 15 wt%, between about 3 and about 15 wt%, or between about 3 and about 12 wt%, based upon the total weight of the reactive components of the reactive monomer mixture.

[0064] The reactive monomer mixture also includes a mixture of hydroxyl-containing silicone components of different molecular weights or different compositions. The first hydroxyl-containing silicone component may be selected from hydroxyl-containing silicone monomers, and hydroxyl containing polydisubstituted siloxanes having at least 4 polydisubstituted siloxane repeating units or 4-8 polydisubstituted siloxane repeating units; and at least one monovalent reactive group. When the first hydroxyl-containing silicone component is a hydroxyl-containing silicone monomer, the second hydroxyl-containing silicone component may be selected from hydroxyl substituted poly(disubstituted siloxane) having 4 to 8 siloxane repeating units, monofunctional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200, 10-100 or 10-20 siloxane repeating units and multifunctional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200, or 10 to 100 siloxane repeating units, and mixtures thereof. When the first hydroxyl-containing silicone component is a hydroxyl-substituted poly(disubstituted siloxane) having 4 to 8 siloxane repeating units, the second hydroxyl-containing silicone component may be selected from monofuntional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200, 10-100 or 10-20 siloxane repeating units and multifunctional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200, or 10 to 100 siloxane repeating units, and mixtures thereof.

[0065] Hydroxyl-containing silicone components having 4 polydisubstituted siloxane repeating units in the siloxane chain are not a distribution and have four repeating units in each monomer. For all hydroxyl-containing silicone components having more than four polydisubstituted siloxane repeating units in the siloxane chain the number of repeating units is a distribution, with the peak of the distribution centered around the listed number of repeat units.

[0066] The elemental Si content of the hydroxyl containing silicone component is greater than about 20 weight percent, to about 38 weight percent of the total molecular weight of the hydroxyl containing silicone component.

Hydroxyl-Containing Silicone Components

[0067] Examples of hydroxyl-containing silicone monomers include propenoic acid-2-methyl-2-hydroxy-3-[3-[1,3,3,3-tetramethyl-1-[(trimethylsilyl)oxy]-1-disiloxanyl]propoxy]propyl ester ("SiGMA"), and 2-hydroxy-3-methacryloxypropyloxypropyl-tris(trimethylsiloxy)silane, and compounds of Formula VI:

wherein R¹ is a hydrogen atom or methyl group and R² is a linear, branched or cyclic alkyl groups containing 1 to 8 carbon atoms or a trimethylsiloxy group.

[0068] The hydroxyl-containing silicone components may be selected from monofunctional hydroxyl substituted, poly(disubstituted siloxane)s of Formula VII-1:

wherein Z is selected from O, N, S or NCH₂CH₂O, when Z is O or S R² is not present;

R¹ is independently H or methyl;

R² is H or is a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amide, ether, and combinations thereof;

R³ and R⁴ are independently a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, and which may be optionally substituted with amide, ether, and combinations thereof; R³ and R⁴ may be independently selected from methyl, ethyl or phenyl, or may be methyl;

n is the number of siloxane units and is from 4 to 8 for the first monofunctional hydroxyl substituted poly(disubstituted siloxane) monomer (or, when the compound is present as a second hydroxyl substituted poly(disubstituted siloxane), n may be 10 to 200, or 10-100, or 10-50, or 10-20, or 12-18), and

R⁵ is selected from straight or branched C₁ to C₈ alkyl groups, which may be optionally substituted with one or more hydroxyl, amide, ether, and combinations thereof. R⁵ may be straight or branched C₄ alkyl, either of which may optionally be substituted with hydroxyl, or may be methyl.

[0069] The hydroxyl-containing silicone components may be selected from monofunctional hydroxyl substituted, poly(disubstituted siloxane)s of Formula VII-2:

wherein Z is selected from O, N, S or NCH₂CH₂O, when Z is O or S R² is not present;

R¹ is independently H or methyl;

R² is H or is a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amide, ether, and combinations thereof;

R³ and R⁴ are independently a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, and which may be optionally substituted with amide, ether, and combinations thereof; R³ and R⁴ may be independently selected from methyl, ethyl or phenyl, or may be methyl;

n is the number of siloxane units and is from 10 to 200, or 10-100, or 10-50, or 10-20, or 12-18 for the second monofunctional hydroxyl substituted poly(disubstituted siloxane); and

R⁵ is selected from straight or branched C₁ to C₈ alkyl groups, which may be optionally substituted with one or more hydroxyl, amide, ether, and combinations thereof. R⁵ may be straight or branched C₄ alkyl, either of which may optionally be substituted with hydroxyl, or may be methyl.

[0070] Examples of monofunctional hydroxyl containing silicone components include mono-(2-hydroxy-3-methacryloxypropyl)-propyl ether terminated mono-n-butyl terminated polydimethylsiloxanes (OH-mPDMS) as shown in Formula VIIa wherein n is between 4 and 30, 4-8 or 10-20 or 4 to 15; and polydimethylsiloxanes having the chemical structures as shown in Formulae VIIb through VIIId, where n is between 4 and 30, 4 and 8 or 10 and 20; n¹ and n² are independently between 4 to 100; 4 to 50; 4 to 25; n³ is 1-50, 1-20, or 1-10; R⁵ is selected from straight or branched C1 to C8 alkyl groups, which may be optionally substituted with one or more hydroxyl, amide, ether, polyhydroxyl groups selected from straight or branched C1 to C8 groups having a formula of C_fH_g(OH)_h wherein f=1-8 and g+h=2f+1 and cyclic C1 to C8 groups having a formula of C_fH_g(OH)_h wherein f=1-8 and g+h=2f-1, and combinations thereof; or R⁵ may be selected from methyl, butyl or hydroxyl substituted C2-C5 alkyl, including hydroxyl ethyl, hydroxyl propyl, hydroxyl butyl, hydroxyl pentyl and 2,3-dihydroxypropyl; and polycarbosiloxanes of Formula IXa and IXb wherein "a" = 4-8 for the first hydroxyl-containing silicone component and "a" is between 4-100 for the second hydroxyl-containing silicone component, R¹ and R⁵ are as defined above; wherein Z is selected from O, N, S or NCH₂CH₂O, when Z is O or S R² is not present; R² is independently selected from the group consisting of a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, and which may be optionally substituted with amide, ether, and combinations thereof; and R³ and R⁴ are independently a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, and which may be optionally substituted with amide, ether, and combinations thereof; R³ and R⁴ may be independently selected from methyl, ethyl or phenyl, or may be methyl.

[0071] The second hydroxyl-containing silicone component may be selected from the group consisting of a second monofunctional hydroxyl substituted, poly(disubstituted siloxane) of general Formula VI, or compounds of Formulae VIIa-IX having 10 to 200 siloxane repeating units and a multifunctional hydroxyl substituted, poly(disubstituted siloxane) of Formula X having 10 to 500, or 10 to 200, or 10 to 100 siloxane repeating units, and mixtures thereof:

wherein in Formula X, Z is selected from O, N, S or NCH₂CH₂O; wherein R¹ is independently a hydrogen atom or methyl group; for Z = O and S, R² is not required;

R², R³, R⁴, R⁵, R⁶, R⁷ are independently selected from the group consisting of a hydrogen atom or any of the substituents defined for R⁸ through R¹¹;

R⁸, R⁹, R¹⁰, R¹¹ are independently selected from the group consisting of a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amido, ether, amino, carboxyl, carbonyl groups and combinations; a linear or branched alkyleneoxy group, specifically ethyleneoxy groups, [CH₂CH₂O]_p wherein p is between 1 and 200, or 1 and 100, or 1 and 50, or 1 and 25, or 1 and 20, optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a C₁-C₆ linear or branched fluoroalkyl groups optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a substituted or un-substituted aryl groups, specifically phenyl groups, wherein the substituents are selected from halogen, hydroxyl, alkoxy, alkylcarbonyl, carboxy, and linear or branched or cyclic alkyl groups which may be further substituted with halogen, hydroxyl, alkoxy, alkylcarbonyl, and carboxyl groups, and combinations thereof;

a, b, c, x, y and z are independently between 0 and 100, between 0 and 50, between 0 and 20, between 0 and 10, or between 0 and 5, and may be ordered in any molecular sequence to make a wide range of substituted hydroxy-oxa-alkylene chains, and n is the number of siloxane repeating units and is from 10 to 500; 10 to 200; 10 to 100; 10 to 50; 10 to 20.

[0072] The weight ratio of the first mono-functional hydroxyl-substituted poly(disubstituted siloxane) to the second hydroxyl-substituted poly(disubstituted siloxane) is in a range of 0.1 to 2, or 0.1 to 1.

[0073] The hydroxyl-containing silicone components may comprise a mixture of a first mono-functional hydroxyl-substituted poly(disubstituted siloxane) of Formula VI, or VIIa-IX where n is from 4 to 8 and a second hydroxyl-substituted poly(disubstituted siloxane) selected from the group consisting of a mono-functional hydroxyl-substituted poly(disubstituted siloxane) of Formula VI or VIIa to IX, wherein n is from 10-200, 10-100 or 10-20 and a di-functional hydroxyl-substituted poly(disubstituted siloxane) of Formula XI

wherein R¹ is independently a hydrogen atom or methyl group; R² and R³ are independently a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amido, ether, amino, carboxyl, carbonyl groups and combinations thereof; or are independently selected from unsubstituted C_1-4 alkyl groups and C_1-4 alkyl groups substituted with hydroxyl or ether; or are selected from methyl, ethyl or -(CH₂CH₂O)_xOCH₃ where x = 1-5-, 1-20, and 1-20; and n = 1-200, 1-100, and 1-50.

[0074] The hydroxyl-containing silicone components may comprise a mixture of a first mono-functional hydroxyl-substituted poly(disubstituted siloxane) of Formula VI, or VIIa-IX where n is from 4 to 8, a second hydroxyl-substituted poly(disubstituted siloxane) selected from the group consisting of a mono-functional hydroxyl-substituted poly(disubstituted siloxane) of Formula VI or VIIa to IX, wherein n is from 10-200, 10-100 or 10-20, and a di-functional hydroxyl-substituted poly(disubstituted siloxane) of Formula XI.

[0075] Examples of multifunctional hydroxyl containing silicones include α-(2-hydroxy-1-methacryloxypropyloxypropyl)-ω-butyl-decamethylpentasiloxane and those of Formula XII:

wherein in Formula XII, Z is selected from O, N, S or NCH₂CH₂O; wherein R¹ is independently a hydrogen atom or methyl group; for Z = O and S, R² is not required; R² is selected from the group consisting of H or a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amido, ether, amino, carboxyl, carbonyl groups and combinations; a linear or branched alkyleneoxy group, specifically ethyleneoxy groups, [CH₂CH₂O]_p wherein p is between 1 and 200, or 1 and 100, or 1 and 50, or 1 and 25, or 1 and 20, optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a C₁-C₆ linear or branched fluoroalkyl groups optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a substituted or un-substituted aryl groups, specifically phenyl groups, wherein the substituents are selected from halogen, hydroxyl, alkoxy, alkylcarbonyl, carboxy, and linear or branched or cyclic alkyl groups which may be further substituted with halogen, hydroxyl, alkoxy, alkylcarbonyl, and carboxyl groups, and combinations thereof; and n¹ and n² are independently selected from is 4 to 100; 4 to 50; or 4 to 25, and n³ is 1-50, 1-20, and 1-10.

[0076] The ratio of the first hydroxyl-containing silicone component to any of the above described second hydroxyl substituted, poly(disubstituted siloxane) can be in a range of 0.2-1.3, 0.4-1.3, 0.4-1 and 0.6-1.

[0077] The hydroxyl-containing silicone components may be present in amounts between about 40-about 70wt%, or about 45-about 70wt%.

Silicone-Containing Compounds without Hydroxyl Functionality

[0078] Additional silicone-containing compounds without hydroxyl functionality may also be included. Suitable examples include those of Formula XIII:

wherein in Formula XIII at least one R¹ is a monovalent reactive group, and the remaining R¹ are independently selected from monovalent reactive groups, monovalent alkyl groups, or monovalent aryl groups, any of the foregoing which may further comprise functionality selected from hydroxy, amino, oxa, carboxy, alkyl carboxy, alkoxy, amido, carbamate, carbonate, halogen or combinations thereof; fluoroalkyl alkyl or aryl groups; partially fluorinated alkyl or aryl groups; halogens; linear, branched or cyclic alkoxy or aryloxy groups; linear or branched polyethyleneoxyalkyl groups, polypropyleneoxyalkyl groups, or poly(ethyleneoxy-co-propyleneoxyalkyl groups; and monovalent siloxane chains comprising between 1-100 siloxane repeat units which may further comprise functionality selected from alkyl, alkoxy, hydroxy, amino, oxa, carboxy, alkyl carboxy, alkoxy, amido, carbamate, halogen or combinations thereof; and wherein n is 0 to 500 or 0 to 200, or 0 to 100,or 0 to 20, where it is understood that when n is other than 0, n is a distribution having a mode equal to a stated value.

[0079] In Formula XIII, from one to three R¹ may comprise monovalent reactive groups. Suitable monovalent alkyl and aryl groups include unsubstituted and substituted monovalent linear, branched or cyclic C₁ to C₁₆ alkyl groups, or unsubstituted monovalent C₁ to C₆ alkyl groups, such as substituted and unsubstituted methyl, ethyl, propyl, butyl, substituted or unsubstituted C₆-C₁₄ aryl groups, or a substituted or un-substituted C₆ aryl group, wherein the substituents include amido, ether, amino, halo, hydroxyl, carboxyl, carbonyl groups; or a phenyl or benzyl group, combinations thereof and the like.

[0080] When one R¹ is a monovalent reactive group, the additional silicone containing compounds may be selected from the polydisubstituted siloxane macromer of Formula XIVa or XIVb; the styryl polydisubstituted siloxane macromer of Formula XVa or XVb; or the carbosilane of Formula XVc:









wherein R¹ is a hydrogen atom or methyl; Z is selected from O, N, S or NCH₂CH₂O; when Z = O or S, R² is not required; wherein R² is selected from the group consisting of H or a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amido, ether, amino, carboxyl, carbonyl groups and combinations; a linear or branched alkyleneoxy group, specifically ethyleneoxy groups, [CH₂CH₂O]_p wherein p is between 1 and 200, or 1 and 100, or 1 and 50, or 1 and 25, or 1 and 20, optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a C₁-C₆ linear or branched fluoroalkyl groups optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a substituted or un-substituted aryl groups, specifically phenyl groups, wherein the substituents are selected from halogen, hydroxyl, alkoxy, alkylcarbonyl, carboxy, and linear or branched or cyclic alkyl groups which may be further substituted with halogen, hydroxyl, alkoxy, alkylcarbonyl, and carboxyl groups, and combinations thereof; wherein R³ is a substituted or unsubstituted C_1-6, C_1-4 or C_2-4 alkylene segment (CH₂)_r each methylene group may optionally be independently substituted with ethers, amines, carbonyls, carboxylates, carbamates and combinations thereof; or an oxyalkylene segment (OCH₂)_k and k is a whole number from one to three, or wherein R³ may be a mixture of alkylene and oxyalkylene segments and the sum of r and k is between 1 and 9; wherein each R⁴ is independently a linear, branched, or cyclic alkyl group containing between one and six carbon atoms, a linear, branched, or cyclic alkoxy group containing between one and six carbon atoms, a linear or branched polyethyleneoxyalkyl group, a phenyl group, a benzyl group, a substituted or un-substituted aryl group, a fluoroalkyl group, a partially fluorinated alkyl group, a perfluoroalkyl group, a fluorine atom, or combinations thereof; wherein R⁵ is a substituted or un-substituted linear or branched alkyl group having 1 to eight carbon atoms, or 1 to 4 carbon atoms, or methyl or butyl; or an aryl group, any of which may be substituted with one or more fluorine atoms; wherein j is a whole number between 1 and 20; wherein q is up to 50, 5 to 30 or 10-25; and wherein n¹ and n² are independently selected from is 4 to 100; 4 to 50; or 4 to 25, and n³ is 1-50, 1-20, and 1-10.

[0081] When Z is O, non-limiting examples of polysiloxane macromers include monomethacryloxypropyl terminated mono-n-butyl terminated polydimethylsiloxanes (mPDMS) as shown in Formula XVI wherein n is between 3 and 15; monomethacryloxypropyl terminated mono-n-alkyl terminated polydimethylsiloxanes, mono-n-alkyl terminated, polydimethyl, polyethylene glycol siloxanes as shown in Formula XVIIa and XVIIb wherein R¹ is a proton or methyl group; wherein R⁵ may be C₁-C₄ alkyl or methyl or butyl; wherein n is 3-15; wherein n¹ and n² are between 4 to 100, 4 to 50, or 4 to 25, and n³ is 1-50, 1-20, or 1-10; and macromers having the chemical structures as shown in formulae XVIIIa through XXIb wherein R¹ is a proton or methyl group; wherein n is between 4-100, 4 and 20, or between 3 and 15; wherein n¹ and n² are between 4 to 100, 4 to 50, or 4 to 25, and n³ is 1-50, 1-20, or 1-10; and R⁵ may be C₁-C₄ alkyl or methyl or butyl.

[0082] Examples of suitable mono(meth)acryloxyalkylpolydisubstituted siloxanes include mono(meth)acryloxypropyl terminated mono-n-butyl terminated polydimethylsiloxane, mono(meth)acryloxypropyl terminated mono-n-methyl terminated polydimethylsiloxane, mono(meth)acryloxypropyl terminated mono-n-butyl terminated polydiethylsiloxane, mono(meth)acryloxypropyl terminated mono-n-methyl terminated polydiethylsiloxane, mono(meth)acrylamidoalkylpolydialkylsiloxanes mono(meth)acryloxyalkyl terminated mono-alkyl polydiarylsiloxanes, and mixtures thereof.

[0083] In Formula XIII, when n is zero, one R¹ may be a monovalent reactive group, and at least 3 R¹ are selected from monovalent alkyl groups having 1 to 16, 1 to 6 or 1-4 carbon atoms. Non-limiting examples of silicone components include, 3-methacryloxypropyltris(trimethylsiloxy)silane (TRIS), 3-methacryloxypropyl-bis(trimethylsiloxy)methylsilane, and 3-methacryloxypropylpentamethyl disiloxane.

[0084] The number of siloxane repeating units, n, may also be 2 to 50, 3 to 25, or 3 to 15; wherein at least one terminal R¹ comprises a monovalent reactive group and the remaining R¹ are selected from monovalent alkyl groups having 1 to 16 carbon atoms, or from monovalent alkyl groups having 1 to 6 carbon atoms. Non-hydroxyl containing silicone compounds may also include those where n is 3 to 15, one terminal R¹ comprises a monovalent reactive group, the other terminal R¹ comprises a monovalent alkyl group having 1 to 6 carbon atoms and the remaining R¹ comprise monovalent alkyl group having 1 to 3 carbon atoms. Non-limiting examples of silicone components include monomethacryloxypropyl n-butyl terminated polydimethylsiloxanes (M_n=800-1000), (mPDMS, as shown in XXII).

[0085] Formula XIII may also include compounds where n is 5 to 400 or from 10 to 300, both terminal R¹ comprise monovalent reactive groups and the remaining R¹ are independently of one another selected from monovalent alkyl groups having 1 to 18 carbon atoms which may have ether linkages between carbon atoms and may further comprise halogen.

[0086] One to four R¹ in Formula XIII may comprise a vinyl carbonate or vinyl carbamate of Formula XXIIIa:

wherein Y denotes O-, S- or NH-; R¹ denotes a hydrogen atom or methyl.

[0087] The silicone-containing vinyl carbonate or vinyl carbamate monomers specifically include: 1,3-bis[4-(vinyloxycarbonyloxy)but-1-yl]tetramethyl-disiloxane; 3-(vinyloxycarbonylthio) propyl-[tris (trimethylsiloxy)silane]; 3-[tris(trimethylsiloxy)silyl] propyl allyl carbamate; 3-[tris(trimethylsiloxy)silyl] propyl vinyl carbamate; trimethylsilylethyl vinyl carbonate; trimethylsilylmethyl vinyl carbonate, and the crosslinking agent of Formula XXIIIb.

[0088] Where biomedical devices with moduli below about 200 psi are desired, only one R¹ comprises a monovalent reactive group and no more than two of the remaining R¹ groups comprise monovalent siloxane groups.

[0089] Another suitable silicone-containing macromer is compound of Formula XXIV in which the sum of x and y is a number in the range of 10 to 30. The silicone containing macromer of Formula XXIV is formed by the reaction of fluoroether, hydroxy-terminated polydimethylsiloxane, isophorone diisocyanate and isocyanatoethylmethacrylate.

[0090] The non-hydroxyl containing silicone-containing component may be selected from non-hydroxyl containing acrylamide silicones of U.S. Patent No. 8,415,405. Other silicone components suitable for use in this invention include those described is WO 96/31792 such as macromers containing polysiloxane, polyalkylene ether, diisocyanate, polyfluorinated hydrocarbon, polyfluorinated ether and polysaccharide groups. Another class of suitable silicone-containing components includes silicone-containing macromers made via GTP, such as those disclosed in U.S. Patent Nos. 5,314,960, 5,331,067, 5,244,981, 5,371,147, and 6,367,929. U.S. Patent Nos. 5,321,108, 5,387,662, and 5,539,016 describe polysiloxanes with a polar fluorinated graft or side group having a hydrogen atom attached to a terminal difluoro-substituted carbon atom. US 2002/0016383 describes hydrophilic siloxanyl methacrylates containing ether and siloxanyl linkages and crosslinkable monomers containing polyether and polysiloxanyl groups. Any of the foregoing polysiloxanes can also be used as the silicone-containing component in this invention.

[0091] In one embodiment where a modulus of less than about 120 psi is desired, the majority of the mass fraction of the silicone-containing components used in the lens formulation should contain only one polymerizable functional group.

[0092] The non-hydroxyl containing silicone component may be selected from the group consisting of monomethacryloxypropyl terminated, mono-n-alkyl terminated linear polydisubstituted siloxane; methacryloxypropyl-terminated linear polydisubstituted siloxane; and mixtures thereof.

[0093] The non-hydroxyl containing silicone component may also be selected from monomethacrylate terminated, C₁-C₄ alkyl terminated, linear polydimethylsiloxanes; and mixtures thereof.

[0094] In some instances, the non-hydroxyl functionalized silicone-containing component may be used in amounts up to about 10 wt%. Examples include those selected from mPDMS of Formula XXII where R⁵ is methyl or butyl, compounds of Formulae XXVIa, XVIIb through XVIIIb, XX, XXIa, XXIb and the macromers shown in Formula XXV or XXVI where n is n is 1-50 and m is 1-50, 1-20 or 1-10:

[0095] Specific examples of non-hydroxyl functionalized silicone-containing components include mPDMS of Formula XVIIa, compounds of Formulae XVIII or XIX where R¹ is methyl and R⁵ is selected from methyl or butyl and the macromers shown in Formula XXV where n is 1-50 or 4-40, 4-20.

[0096] Specific examples of silicone containing crosslinkers include bismethacryloxypropyl polydimethyl siloxane, where n may be 4-200, or 4-150, and the following compounds of Formula XXVIIa-XXVIIIc, where n¹ and n² are independently selected from 4 to 100; 4 to 50; or 4 to 25; n³ is 1-50, 1-20 or 1-10; n is 1-100, 1-50, 1-20 or 1-10; m is 1-100, 1-50, 1-20 or 1-10; s is up to 50, 5-30 or 10-25; and q is up to 50, 5-30 or 10-25.

[0097] The non-hydroxyl containing silicone component may have an average molecular weight of from about 400 to about 4000 Daltons.

[0098] The silicone-containing component(s) (both hydroxyl and non-hydroxyl containing) may be present in amounts up to about 85 weight %, or from about 10 and about 80, or from about 20 and about 75 weight %, based upon all reactive components of the reactive mixture (e.g., excluding diluents).

Charged Reactive Component

[0099] The reactive monomer mixture may further comprise at least one reactive component which is charged under physiological conditions. The charged monomer may be selected from anions, cations, zwitterions, betaines, and mixtures thereof.

[0100] The charged monomers, when incorporated into the silicone hydrogels of the present invention, provide a net negative charge distribution. Anionic monomers comprise at least one anionic group and at least one reactive group. Specifically, the anionic group can include, but is not limited to, carboxylate groups, phosphates, sulfates, sulfonates, phosphonates, borates, and mixtures thereof. The anionic groups may comprise from three to ten carbon atoms, or from three to eight carbon atoms. The anionic groups may comprise carboxylic acid groups. Specifically, the charged monomer may be a carboxylic acid monomer selected from the group consisting of acrylic acid, methacrylic acid, furmaric acid, maelic acid, itaconic acid, crotonic acid, cinnamic acid, vinylbenzoic acid, monoesters of furmaric acid, maelic acid, and itaconic acid, and mixtures thereof.

[0101] The charged monomer may also comprise a mixture of anionic and cationic monomer.

[0102] The charged monomer can be a zwitterionic monomer. Zwitterionic monomers comprise at least one zwitterionic group and at least one reactive group. As used herein, the term "zwitterion" refers to a neutral chemical compound with both a positive and negative electrical charge. Zwitterionic monomers include betaine monomers.

[0103] The charged monomer can be a betaine monomer. Betaine monomers comprise at least one betaine group and at least one reactive group. As used herein, the term "betaine" refers to a neutral chemical compound with a positively charged cationic functional group such as a quaternary ammonium or phosphonium cation which bears no hydrogen atom and with negatively charged functional group such as a carboxylate group which may not be adjacent to the cationic site.

[0104] The charged monomer contains at least one polymerizable group, or reactive group. Reactive groups include groups that can undergo free radical polymerization. Non-limiting examples of free radical reactive groups include (meth)acrylates, styryls, vinyls, vinyl ethers, C_1-6 alkyl(meth)acrylates, (meth)acrylamides, C_1-6 alkyl (meth)acrylamides, N-vinyllactams, N-vinylamides, C_2-12 alkenyls, C_2-12 alkenylphenyls, C_2-12 alkenylnaphthyls, C_2-6 alkenylphenyl, C_1-6 alkyls, O-vinylcarbamates, and O-vinylcarbonates.

[0105] Examples of "charged monomers" include (meth)acrylic acid, N-[(ethenyloxy)carbonyl]-β-alanine (VINAL, CAS #148969-96-4), 3-acrylamidopropanoic acid (ACA1), 5-acrylamidopropanoic acid (ACA2), 3-acrylamido-3-methylbutanoic acid (AMBA), 2-(methacryloyloxy)ethyl trimethylammonium chloride (Q Salt or METAC), 2-acrylamido-2-methylpropane sulfonic acid (AMPS), 1-propanaminium, N-(2-carboxyethyl)-N,N-dimethyl-3-[(1-oxo-2-propen-1-yl)amino]-, inner salt (CBT, carboxybetaine; CAS 79704-35-1), 1-propanaminium, N,N-dimethyl-N-[3-[(1-oxo-2-propen-1-yl)amino]propyl]-3-sulfo-, inner salt (SBT, sulfobetaine, CAS 80293-60-3), 3,5-Dioxa-8-aza-4-phosphaundec-10-en-1-aminium, 4-hydroxy-N,N,N-trimethyl-9-oxo-, inner salt, 4-oxide (9CI) (PBT, phosphobetaine, CAS 163674-35-9, 2-methacryloyloxyethyl phosphorylcholine, 3-(dimethyl(4-vinylbenzyl)ammonio)propane-1-sulfonate (DMVBAPS), 3-((3-acrylamidopropyl)dimethylammonio)propane-1-sulfonate (AMPDAPS), 3-((3-methacrylamidopropyl)dimethylammonio)propane-1-sulfonate (MAMPDAPS), 3-((3-(acryloyloxy)propyl)dimethylammonio)propane-1-sulfonate (APDAPS), methacryloyloxy)propyl)dimethylammonio)propane-1-sulfonate (MAPDAPS).

[0106] The charged monomer may be selected from (meth)acrylic acid, 3-acrylamidopropanoic acid (ACA1), 5-acrylamidopropanoic acid (ACA2), and mixtures thereof..

[0107] The charged monomer can be present in an amount up to about 10 weight percent (wt. %), based on the total weight of the reaction monomer mixture, including a range of about 0.5 to about 5 wt.%, about 0.5 to about 3 wt.%, about 0.5 to about 2 wt.%, about 1 to about 10 wt.%, about 1 to about 5 wt.%, about 1 to about 3 wt.%, and about 1 to about 2 wt.%.

Hydrophilic Components

[0108] The reactive monomer mixture also includes at least one hydrophilic component selected from hydrophilic monomers and macromers. Hydrophilic monomers can be any of the hydrophilic monomers known to be useful to make hydrogels. Examples of suitable families of hydrophilic monomers include N-vinyl amides, N-vinylimides, N-vinyl lactams, (meth)acrylates, (meth)acrylamides, styrenes, vinyl ethers, O-vinyl carbonates, O-vinyl carbamates, N-vinyl ureas, other hydrophilic vinyl compounds and mixtures thereof.

[0109] The hydrophilic monomers that may be used to make the polymers of this invention have at least one polymerizable double bond and at least one hydrophilic functional group. Such hydrophilic monomers may themselves be used as crosslinking agents, however, where hydrophilic monomers having more than one polymerizable functional group are used, their concentration should be limited as discussed above to provide a contact lens having the desired modulus. The term "vinyl-type" or "vinyl-containing" monomers refer to monomers containing the vinyl grouping (-CH=CH₂) and are generally highly reactive. Such hydrophilic vinyl-containing monomers are known to polymerize relatively easily.

[0110] "Acrylic-type" or "acrylic-containing" monomers are those monomers containing an acrylic group (CH₂=CRCOX) wherein R is H or CH₃, and X is O or N, which are also known to polymerize readily, such as N,N-dimethyl acrylamide (DMA), 2-hydroxyethyl methacrylamide, polyethyleneglycol monomethacrylate, methacrylic acid, acrylic acid, mixtures thereof and the like.

[0111] Non-limiting examples of hydrophilic (meth)acrylate and (meth)acrylamide monomers include: acrylamide, N-isopropyl acrylamide, N,N-dimethylaminopropyl (meth)acrylamide, N,N-dimethyl acrylamide (DMA), N-2-hydroxyethyl (meth)acrylamide, 2,3-dihydroxypropyl (meth)acrylamide, N,N-bis(2-hydroxyethyl) (meth)acrylamide, N-(2-hydroxypropyl) (meth)acrylamide, N,N-bis(2-hydroxypropyl) (meth)acrylamide, N-(3-hydroxypropyl) (meth)acrylamide, vinyl acetate, acrylonitrile, and mixtures thereof.

[0112] Non-limiting examples of hydrophilic N-vinyl lactam and N-vinyl amide monomers include: N-vinyl pyrrolidone (NVP), N-vinyl-2-piperidone, N-vinyl-2-caprolactam, N-vinyl-3-methyl-2-caprolactam, N-vinyl-3-methyl-2-piperidone, N-vinyl-4-methyl-2-piperidone, N-vinyl-4-methyl-2-caprolactam, N-vinyl-3-ethyl-2- pyrrolidone, N-vinyl-4,5-dimethyl-2-pyrrolidone, N-vinyl acetamide (NVA), N-vinyl-N-methylacetamide (VMA), N-vinyl-N-ethyl acetamide, N-vinyl-N-ethyl formamide, N-vinyl formamide, N-vinyl-N-methylpropionamide, N-vinyl-N-methyl-2-methylpropionamide, N-vinyl-2-methylpropionamide, N-vinyl-N,N'-dimethylurea, 1-methyl-3-methylene-2-pyrrolidone, 1-methyl-5-methylene-2-pyrrolidone, 5-methyl-3-methylene-2-pyrrolidone; 1-ethyl-5-methylene-2-pyrrolidone, N-methyl-3-methylene-2-pyrrolidone, 5-ethyl-3-methylene-2-pyrrolidone, 1-N-propyl-3-methylene-2-pyrrolidone, 1-N-propyl-5-methylene-2-pyrrolidone, 1-isopropyl-3-methylene-2-pyrrolidone, 1-isopropyl-5-methylene-2-pyrrolidone, N-vinyl-N-ethyl acetamide, N-vinyl-N-ethyl formamide, N-vinyl formamide, N-vinyl isopropylamide, N-vinyl caprolactam, N-carboxyvinyl-β-alanine (VINAL), N-carboxyvinyl-α-alanine, N-vinylimidazole, and mixtures thereof.

[0113] Non-limiting examples of hydrophilic O-vinyl carbamates and O-vinyl carbonates monomers include: N-2-hydroxyethyl vinyl carbamate and N-carboxy-β-alanine N-vinyl ester. Further examples of the hydrophilic vinyl carbonate or vinyl carbamate monomers are disclosed in U.S. Patent No. 5,070,215, and the hydrophilic oxazolone monomers are disclosed in U.S. Patent No. 4,910,277.

[0114] Other hydrophilic vinyl compounds include ethylene glycol vinyl ether (EGVE), di(ethylene glycol) vinyl ether (DEGVE), allyl alcohol, 2-ethyl oxazoline, vinyl acetate, acrylonitrile, and mixtures thereof.

[0115] Other suitable hydrophilic monomers will be apparent to one skilled in the art.

[0116] The hydrophilic components of the present invention may also be macromers of linear or branched poly(ethylene glycol), poly(propylene glycol), or statistically random or block copolymers of ethylene oxide and propylene oxide. The macromers of these polyethers have one or more reactive group. Non-limiting examples of such reactive groups are acrylates, methacrylates, styrenes, vinyl ethers, acrylamides, methacrylamides, and other vinyl compounds. In one embodiment, the macromers of these polyethers comprise (meth)acrylates, (meth)acrylamides, and mixtures thereof.

[0117] The hydrophilic monomers which may be incorporated into the polymers disclosed herein may be selected from N,N-dimethyl acrylamide (DMA), 2-hydroxyethyl acrylamide, 2-hydroxyethyl methacrylamide, N-hydroxypropyl methacrylamide, bishydroxyethyl acrylamide, 2,3-dihydroxypropyl (meth)acrylamide, N-vinylpyrrolidone (NVP), N-vinyl-N-methyl acetamide, N-vinyl methacetamide (VMA), and polyethyleneglycol monomethacrylate.

[0118] The hydrophilic monomers may be selected from DMA, NVP, VMA, NVA, and mixtures thereof.

[0119] It is a surprising effect of the present invention that silicone hydrogels with a desirable balance of wettability, water content and biocompatibility may be formed from reaction mixtures with 35 wt%, or less or less than about 30 wt%, or less than about 25 wt%, or less than about 20 wt% hydrophilic amide monomers. The hydrophilic amide monomers may be included in the reactive mixtures of the present invention in amounts between about 5 and 28 wt%, or 5 and about 25 wt%, or between about 8 and about 20 wt%.

[0120] The hydrophilic components (including the charged components and the hydrophilic hydroxyl components (discussed below), but excluding the polyamide) may be present in amounts up to about 50 wt%, or in an amount in the range of about 10 to about 50 wt. %, or in the range of about 10 to about 40 wt. %, based on the total weight of the reactive components in the reactive monomer mixture.

Hydroxyl alkyl methacrylate monomer

[0121] The reactive mixtures of the present invention may further comprise, in addition to the hydrophilic monomer described above, at least one hydroxyalkyl (meth)acrylate where the hydroxyl alkyl group may be selected from C₂-C₄ mono or dihydroxy substituted alkyl, and poly(ethylene glycol) having 1-10 repeating units; or is selected from 2-hydroxyethyl, 2,3-dihydroxypropyl, or 2-hydroxypropyl.

[0122] Examples of suitable hydroxyalkyl (meth)acrylate monomer include 2-hydroxyethyl (meth)acrylate, 3-hydroxypropyl (meth)acrylate, 2-hydroxypropyl (meth)acrylate, 2,3-dihydroxypropyl (meth)acrylate, 2-hydroxybutyl (meth)acrylate, 3-hydroxybutyl (meth)acrylate, 1-hydroxypropyl-2-(meth)acrylate, 2-hydroxy-2-methylpropyl (meth)acrylate, 3-hydroxy-2,2-dimethyl-propyl (meth)acrylate, 4-hydroxybutyl (meth)acrylate, glycerol (meth)acrylate, polyethyleneglycol monomethacrylate, and mixtures thereof.

[0123] The hydroxyalkyl monomer may also be selected from the group consisting of 2-hydroxyethyl methacrylate, glycerol methacrylate, 2-hydroxypropyl methacrylate, hydroxybutyl methacrylate, 3-hydroxy-2,2-dimethyl-propyl methacrylate, and mixtures thereof.

[0124] The hydroxyalkyl monomer may comprise 2-hydroxyethyl methacrylate, 3-hydroxy-2,2-dimethyl-propyl methacrylate, hydroxybutyl methacrylate or glycerol methacrylate.

[0125] Hydroxyl containing (meth)acrylamides are generally too hydrophilic to be included as compatibilizing hydroxyalkyl monomers, and when included are hydrophilic monomers.

[0126] When at least one hydroxyalkyl methacrylate is included, the lower amount of hydroxyalkyl monomers may be selected to provide a haze value to the final lens of less than about 50% or less than about 30%.

[0127] It will be appreciated that the amount of hydroxyl component will vary depending upon a number of factors, including, the number of hydroxyl groups on the hydroxyalkyl monomer, the amount, molecular weight and presence of hydrophilic functionality on the silicone containing components. The hydrophilic hydroxyl component may be present in the reactive mixture in amounts up to about 15%, up to about 10 wt%, between about 3 and about 15 wt% or about 5 and about 15 wt%.

Cross-linking Agent

[0128] It is generally desirable to add one or more cross-linking agents to the reaction mixture. The cross-linking agents may be selected from bifunctional cross-linkers, trifunctional cross-linkers, tetrafunctional cross-linkers, including silicone-containing and non-silicone containing cross-linking agents, and mixtures thereof. Non-silicone containing cross-linking agents include ethylene glycol dimethacrylate ("EGDMA"), diethyleneglycol dimethacrylate; tetraethylene glycol dimethacrylate (TEGDMA), trimethylolpropane trimethacrylate ("TMPTMA"), glycerol trimethacrylate, 1,3-propanediol dimethacrylate; 2,3-propanediol dimethacrylate; 1,6-hexanediol dimethacrylate; 1,4-butanediol dimethacrylate; triallyl cyanurate (TAC), methacryloxyethyl vinylcarbonate (HEMAVc), allylmethacrylate, methylene bisacrylamide (MBA), polyethylene glycol dimethacrylate (wherein the polyethylene glycol has a molecular weight up to about 5000 Daltons). The cross-linking agents are used in amounts from about 0.000415 to about 0.0156 moles per 100 grams of reactive components in the reaction mixture. Alternatively, if the hydrophilic monomers and/or the silicone-containing components are multifunctional or contain multifunctional impurities, the addition of a crosslinking agent to the reaction mixture is optional. Examples of hydrophilic monomers which can act as the crosslinking agent and when present do not require the addition of an additional crosslinking agent to the reaction mixture include (meth)acrylate and (meth)acrylamide endcapped polyethers.

Further Constituents

[0129] The reactive monomer mixture may contain additional components such as, but not limited to, diluents, wetting agents, light absorbing compounds, including UV absorbers and photochromic compounds, tints, pigment and dyes, any of which may be reactive or non-reactive, but capable of being retained in the biomedical device, medicinal agents, antimicrobial compounds, pharmaceutical compounds, nutriceutical compounds, release agents, releasable wetting agents, and combinations thereof.

[0130] The reactive components may be mixed in a diluent to form a reaction mixture. Suitable diluents are known in the art. For silicone hydrogels suitable diluents are disclosed in WO 03/022321 and US6020445.

[0131] Classes of suitable diluents for silicone hydrogel reaction mixtures include alcohols having 2 to 20 carbons, amides having 10 to 20 carbon atoms derived from primary amines, and carboxylic acids having 8 to 20 carbon atoms. Primary and tertiary alcohols may be used. Preferred classes include alcohols having 5 to 20 carbons and carboxylic acids having 10 to 20 carbon atoms.

[0132] Specific diluents which can be used include 1-ethoxy-2-propanol, diisopropylaminoethanol, isopropanol, 3,7-dimethyl-3-octanol, 1-decanol, 1-dodecanol, 1-octanol, 1-pentanol, 2-pentanol, 1-hexanol, 2-hexanol, 2-octanol, 3-methyl- 3-pentanol, tert-amyl alcohol, tert-butanol, 2-butanol, 1-butanol, 2-methyl-2-pentanol, 2-propanol, 1-propanol, ethanol, 2-ethyl-1-butanol, (3-acetoxy-2-hydroxypropyloxy) propylbis(trimethylsiloxy)methylsilane, 1-tert-butoxy-2-propanol, 3,3-dimethyl-2-butanol, tert-butoxyethanol, 2-octyl-1-dodecanol, decanoic acid, octanoic acid, dodecanoic acid, 2-(diisopropylamino)ethanol mixtures thereof and the like.

[0133] The diluents may include 3,7-dimethyl-3-octanol, 1-dodecanol, 1-decanol, 1-octanol, 1-pentanol, 1-hexanol, 2-hexanol, 2-octanol, 3-methyl-3-pentanol, 2-pentanol, t-amyl alcohol, tert-butanol, 2-butanol, 1-butanol, 2-methyl-2-pentanol, 2-ethyl-1-butanol, ethanol, 3,3-dimethyl-2-butanol, 2-octyl-1-dodecanol, decanoic acid, octanoic acid, dodecanoic acid, mixtures thereof and the like.

[0134] The diluents may include 3,7-dimethyl-3-octanol, 1-dodecanol, 1-decanol, 1-octanol, 1-pentanol, 1-hexanol, 2-hexanol, 2-octanol, 1-dodecanol, 3-methyl-3-pentanol, 1-pentanol, 2-pentanol, t-amyl alcohol, tert-butanol, 2-butanol, 1-butanol, 2-methyl-2-pentanol, 2-ethyl-1-butanol, 3,3-dimethyl-2-butanol, 2-octyl-1-dodecanol, mixtures thereof and the like.

[0135] Mixtures of diluents may be used. If a diluent is present, generally there are no particular restrictions with respect to the amount of diluent present. When diluent is used, the diluent may be present in an amount in the range of about 2 to about 70 wt%, including in the range of about 5 to about 50 wt%, about 5 to about 45wt%, about 15 to about 40 wt%, based on the total weight of the reactive mixtures (including reactive and nonreactive components).

[0136] A polymerization catalyst may be used in the reaction mixture. The polymerization catalyst or initiator can include at least one of lauryl peroxide, benzoyl peroxide, iso- propyl percarbonate, azobisisobutyronitrile, and the like, that generate free radicals at moderately elevated temperatures, and photoinitiator systems such as aromatic alpha-hydroxy ketones, alkoxyoxybenzoins, acetophenones, acylphosphine oxides, bisacylphosphine oxides, and a tertiary amine plus a diketone, mixtures thereof and the like. Illustrative examples of photoinitiators are 1-hydroxycyclohexyl phenyl ketone, 2-hydroxy-2-methyl-1-phenyl-propan-1-one, bis(2,6-dimethoxybenzoyl)-2,4-4-trimethylpentyl phosphine oxide (DMBAPO), bis(2,4,6-trimethylbenzoyl)-phenyl phosphinthere of eoxide (Irgacure 819), 2,4,6-trimethylbenzyldiphenyl phosphine oxide and 2,4,6-trimethylbenzoyl diphenylphosphine oxide, benzoin methyl ester and a combination of cam- phorquinone and ethyl 4-(N,N-dimethylamino)benzoate.

[0137] Commercially available visible light initiator systems include Irgacure^® 819, Irgacure^® 1700, Irgacure^® 1800, Irgacure^® 819, Irgacure^® 1850 (all from Ciba Specialty Chemicals) and Lucrin^® TPO initiator (available from BASF). Commercially available UV photoinitiators include Darocur^® 1173 and Darocur^® 2959 (Ciba Specialty Chemicals). These and other photoinitiators which may be used are disclosed in Volume III, Photoinitiators for Free Radical Cationic & Anionic Photopolymerization, 2nd Edition by J. V. Crivello & K. Dietliker; edited by G. Bradley; John Wiley and Sons; New York; 1998. The initiator is used in the reaction mixture in effective amounts to initiate photopolymerization of the reaction mixture, e.g., from about 0.1 to about 2 parts by weight per 100 parts of reactive monomer. Polymerization of the reaction mixture can be initiated using the appropriate choice of heat or visible or ultraviolet light or other means depending on the polymerization initiator used. Alternatively, initiation can be conducted without a photoinitiator using, for example, e-beam. However, when a photoinitiator is used, the preferred initiators are bisacylphosphine oxides, such as bis(2,4,6-trimethylbenzoyl)-phenyl phosphine oxide (Irgacure^® 819) or a combination of 1-hydroxycyclohexyl phenyl ketone and bis(2,6-dimethoxybenzoyl)-2,4-4-trimethylpentyl phosphine oxide (DMBAPO), and in another embodiment the method of polymerization initiation is via visible light activation.

[0138] Polymerization of the reaction mixture can be initiated using the appropriate choice of heat or visible or ultraviolet light or other means depending on the polymerization initiator used. Alternatively, initiation can be conducted without a photoinitiator using, for example, e-beam.

Curing of Silicone Polymer/Hydrogel and Manufacture of Lens

[0139] The reactive mixtures of the present invention can be formed by any of the methods known in the art, such as shaking or stirring, and used to form polymeric articles or devices by known methods. The reactive components (hydrophilic monomer, hydroxyl-containing silicone component, cross-linking agent, polyamide, etc.) are mixed together either with or without a diluent to form the reactive mixture.

[0140] For examples, the silicone hydrogels may be prepared by mixing reactive components, and, optionally, diluent(s), with a polymerization initiator and curing by appropriate conditions to form a produce that can be subsequently formed into the appropriate shape by lathing, cutting, and the like. Alternatively, the reaction mixture may be placed in a mold and subsequently cure into the appropriate article.

[0141] The reactive mixture of the present invention may be cured via any known process for molding the reaction mixture in the production of contact lenses, including spincasting and static casting. Spincasting methods are disclosed in US3,408,429 and US3,660,545, and static casting methods are disclosed in US 4,113,224 and US4,197,266. The contact lenses of this invention may be formed by the direct molding of the silicone hydrogels, which is economical, and enables precise control over the final shape of the hydrated lens. For this method, the reaction mixture is placed in a mold having the shape of the final desired silicone hydrogel and the reaction mixture is subjected to conditions whereby the monomers polymerize, to thereby produce a polymer in the approximate shape of the final desired product.

[0142] After curing, the lens may be subjected to extraction to remove unreacted components and release the lens from the lens mold. The extraction may be done using conventional extraction fluids, such organic solvents, such as alcohols or may be extracted using aqueous solutions.

[0143] Aqueous solutions are solutions which comprise water. The aqueous solutions of the present invention may comprise at least about 30 weight % water, or at least about 50 weight % water, or at least about 70% water, or at least about 90 weight % water. Aqueous solutions may also include additional water soluble components such as release agents, wetting agents, slip agents, pharmaceutical and nutraceutical components, combinations thereof and the like. Release agents are compounds or mixtures of compounds which, when combined with water, decrease the time required to release a contact lens from a mold, as compared to the time required to release such a lens using an aqueous solution that does not comprise the release agent. The aqueous solutions may comprise less than about 10 weight %, or less than about 5 weight % organic solvents such as isopropyl alcohol, or may be free from organic solvents. The aqueous solutions may not require special handling, such as purification, recycling or special disposal procedures.

[0144] In various embodiments, extraction can be accomplished, for example, via immersion of the lens in an aqueous solution or exposing the lens to a flow of an aqueous solution. In various embodiments, extraction can also include, for example, one or more of: heating the aqueous solution; stirring the aqueous solution; increasing the level of release aid in the aqueous solution to a level sufficient to cause release of the lens; mechanical or ultrasonic agitation of the lens; and incorporating at least one leach aid in the aqueous solution to a level sufficient to facilitate adequate removal of unreacted components from the lens. The foregoing may be conducted in batch or continuous processes, with or without the addition of heat, agitation or both.

[0145] Some embodiments can also include the application of physical agitation to facilitate leach and release. For example, the lens mold part to which a lens is adhered can be vibrated or caused to move back and forth within an aqueous solution. Other embodiments may include ultrasonic waves through the aqueous solution.

[0146] The lenses may be sterilized by known means such as, but not limited to autoclaving.

[0147] The contact lenses of the present invention display desirable combination of both mechanical and biological properties including water content, haze, contact angle, modulus, oxygen permeability, lipid uptake, lysozyme uptake and PQ1 uptake, as shown in the following table. All values are prefaced by "about", and the ophthalmic devices of the present invention may have any combination of the listed properties.

Table 1

[H2O] %	>20	>30	>40	20-60	30-60
% haze	>50	>30
DCA (°)	>90	>70	≥50	≥40	≥20
Modulus (psi)	>120	>110	50-120	50-110
Dk (barrers)	>80	80-200	90-180	100-160
Lipid uptake (µg/lens)	<20	<10	<5
Lysozyme uptake (µg/lens)	>50	>100	>200	>500	>700
PQ1 uptake (%)	<10	<5

[0148] Lysozyme uptake may also be at least about 800 or between 50 and 1500, 100-1500 or 200-1500 µg/lens.

[0149] In addition to displaying desirable stability, the lenses of the present invention also display compatibility with the components of human tears.

Test Methods

[0150] It will be appreciated that all of the tests specified herein have a certain amount of inherent error. Standard deviations are shown in parentheses. Accordingly, the results reported herein are not to be taken as absolute numbers, but numerical ranges based upon the precision of the particular test.

[0151] Haze was measured by placing a hydrated test lens in borate buffered saline in a clear glass cell at ambient temperature above a flat black background, illuminating from below with a fiber optic lamp (Dolan-Jenner PL-900 fiber optic light with 0.5 inch diameter light guide) at an angle of 66° normal to the lens cell, and capturing an image of the test lens from above, normal to the glass cell with a video camera (DVC 1310C RGB camera or equivalent equipped with a suitable zoom camera lens) placed 14 cm above the lens holder. The background scatter is subtracted from the scatter of the test lens by subtracting an image of a blank cell with borate buffered saline (baseline) using EPIX XCAP V 3.8 software. The subtracted scattered light image is quantitatively analyzed by integrating over the central 10 mm of the test lens and then compared to a frosted glass standard.

[0152] The light intensity/power setting was adjusted to achieve a mean grayscale value in the range of 900-910 for the frosted glass standard; at this setting, the baseline mean grayscale value was in the range of 50-70. The mean grayscale values of the baseline and frosted glass standard are recorded and used to create a scale from zero to 100, respectively. In the grayscale analysis, the mean and standard deviations of the baseline, frosted glass, and every test lens was recorded. For each lens, a scaled value was calculated according to the equation: scaled value equals the mean grayscale value (lens minus baseline) divided by the mean grayscale value (frosted glass minus baseline) times by 100. Three to five test lenses are analyzed, and the results are averaged.

[0153] Water content was measured gravimetrically. Lenses were equilibrated in packing solution for 24 hours. Each of three test lens are removed from packing solution using a sponge tipped swab and placed on blotting wipes which have been dampened with packing solution. Both sides of the lens are contacted with the wipe. Using tweezers, the test lens are placed in a tared weighing pan and weighed. The two more sets of samples are prepared and weighed. All weight measurements were done in triplicate, and the average of those values used in the calculations. The wet weight is defined as the combined weight of the pan and wet lenses minus the weight of the weighing pan alone.

[0154] The dry weight was measured by placing the sample pans in a vacuum oven which has been preheated to 60°C for 30 minutes. Vacuum was applied until the pressure reaches at least 1 inch of Hg is attained; lower pressures are allowed. The vacuum valve and pump are turned off and the lenses are dried for at least 12 hours; typically overnight. The purge valve is opened allowing dry air or dry nitrogen gas to enter. The oven is allowed reach atmospheric pressure. The pans are removed and weighed. The dry weight is defined as the combined weight of the pan and dry lenses minus the weight of the weighing pan alone. The water content of the test lens was calculated as follows:

[0155] The average and standard deviation of the water content were calculated and the average value reported as the percent water content of the test lens.

[0156] The refractive index (RI) of a contact lens was measured by a Leica ARIAS 500 Abbe refractometer in manual mode or by a Reichert ARIAS 500 Abbe refractometer in automatic mode with a prism gap distance of 100 microns. The instrument was calibrated using deionized water at 20°C (+/- 0.2 °C). The prism assembly was opened and the test lens placed on the lower prism between the magnetic dots closest to the light source. If the prism is dry, a few drops of saline were applied to the bottom prism. The front curve of the lens was against the bottom prism. The prism assembly was then closed. After adjusting the controls so that the shadow line appeared in the reticle field, the refractive index was measured. The RI measurement was made on five test lenses. The average RI calculated from the five measurements was recorded as the refractive index as well as its standard deviation.

[0157] Oxygen permeability (Dk) was determined by the polarographic method generally described in ISO 9913-1:1996 and ISO 18369-4:2006, but with the following modifications. The measurement was conducted at an environment containing 2.1% oxygen created by equipping the test chamber with nitrogen and air inputs set at the appropriate ratio, for example, 1800 mL/min of nitrogen and 200 mL/min of air. The t/Dk is calculated using the adjusted oxygen concentration. Borate buffered saline was used. The dark current was measured by using a pure humidified nitrogen environment instead of applying MMA lenses. The lenses were not blotted before measuring. Four lenses were stacked instead of using lenses of various thickness (t) measured in centimeters. A curved sensor was used in place of a flat sensor; radius was 7.8 mm. The calculations for a 7.8 mm radius sensor and 10% (v/v) air flow are as follows:

[0158] The edge correction was related to the Dk of the material.

[0159] For all Dk values less than 90 barrers:

[0160] For Dk values between 90 and 300 barrers:

[0161] For Dk values greater than 300 barrers:

[0162] Non-edge corrected Dk was calculated from the reciprocal of the slope obtained from the linear regression analysis of the data wherein the x variable was the center thickness in centimeters and the y variable was the t/Dk value. On the other hand, edge corrected Dk was calculated from the reciprocal of the slope obtained from the linear regression analysis of the data wherein the x variable was the center thickness in centimeters and the y variable was the edge corrected t/Dk value. The resulting Dk value was reported in barrers.

[0163] Wettability of lenses was determined using the methods below. Dynamic contact angle (DCA) was determined by a Wilhelmy plate method using a Cahn DCA-315 instrument at room temperature and using deionized water as the probe solution. The experiment was performed by dipping the lens specimen of known parameter into the packing solution of known surface tension while measuring the force exerted on the sample due to wetting by a sensitive balance. The advancing contact angle of the packing solution on the lens is determined from the force data collected during sample dipping. The receding contact angle is likewise determined from force data while withdrawing the sample from the liquid. The Wilhelmy plate method is based on the following formula: Fg = γρcosθ - B, wherein F = the wetting force between the liquid and the lens (mg), g = gravitational acceleration (980.665 cm/sec²), γ = surface tension of probe liquid (dyne/cm), ρ = the perimeter of the contact lens at the liquid/lens meniscus (cm), θ = the dynamic contact angle (degree), and B = buoyancy (mg). B is zero at the zero depth of immersion. Four test strips were cut from the central area of the contact lens. Each strip was approximately 5 mm in width and equilibrated in packing solution. Then, each sample was cycled four times, and the results were averaged to obtain the advancing and receding contact angles of the lens.

[0164] Wettability of lenses was also determined using a sessile drop technique measured using KRUSS DSA-100 TM instrument at room temperature and using DI water as probe solution. The lenses to be tested (3-5/sample) were rinsed in DI water to remove carry over from packing solution. Each test lens was placed on blotting lint free wipes which were dampened with packing solution. Both sides of the lens were contacted with the wipe to remove surface water without drying the lens. To ensure proper flattening, lenses were placed "bowl side down" on the convex surface of contact lens plastic molds. The plastic mold and the lens were placed in the sessile drop instrument holder, ensuring proper central syringe alignment. A 3 to 4 microliter drop of deionized water was formed on the syringe tip using DSA 100-Drop Shape Analysis software ensuring the liquid drop was hanging away from the lens. The drop was released smoothly on the lens surface by moving the needle down. The needle was withdrawn away immediately after dispensing the drop. The liquid drop was allowed to equilibrate on the lens for 5 to 10 seconds, and the contact angle was measured between the drop image and the lens surface.

[0165] The mechanical properties of the contact lenses were measured by using a tensile testing machine such as an Instron model 1122 or 5542 equipped with a load cell and pneumatic grip controls. Minus one diopter lens is the preferred lens geometry because of its central uniform thickness profile. A dog-bone shaped sample cut from a -1.00 power lens having a 0.522 inch length, 0.276 inch "ear" width and 0.213 inch "neck" width was loaded into the grips and elongated at a constant rate of strain of 2 inches per minute until it breaks. The center thickness of the dog-bone sample was measured using an electronic thickness gauge prior to testing. The initial gauge length of the sample (Lo) and sample length at break (Lf) were measured. At least five specimens of each composition were measured, and the average values were used to calculate the percent elongation to break: percent elongation = [(Lf - Lo)/Lo] × 100. The tensile modulus was calculated as the slope of the initial linear portion of the stress-strain curve; the units of modulus are pounds per square inch or psi. The tensile strength was calculated from the peak load and the original cross-sectional area: tensile strength = peak load divided by the original cross-sectional area; the units of tensile strength are psi. Toughness was calculated from the energy to break and the original volume of the sample: toughness = energy to break divided by the original sample volume; the units of toughness are in-lbs/in³.

[0166] PQ1 uptake was measured chromatographically. The HPLC was calibrated using a series of standard PQ1 solutions having concentrations 2, 4, 6, 8, 12 and 15 µg/mL. Lenses were placed into polypropylene contact lens cases with 3 mL of Optifree Replenish or similar lens solution (PQ1 concentration = 10 micrograms/mL) which is commercially available from Alcon. A control lens case, containing 3 mL of solution, but no contact lens was also prepared. The lenses and control solutions were stored at room temperature for 72 hours. 1 mL of solution was removed from each of the samples and controls and mixed with trifluoroacetic acid (10 µL). The analysis was conducted using HPLC/ELSD and a Phenomenex Luna C5 (4.6 mm × 5 mm; 5 µm particle size) column with the following equipment and conditions: Agilent 1200 HPLC or equivalent with an ELSD operating at T= 100°C, Gain = 12, Pressure = 4.4 bar, Filter = 3s; ELSD parameters may vary from instrument to instrument; using mobile phase A of water (0.1% TFA) and mobile phase B of acetonitrile (0.1% TFA), a column temperature of 40°C and an injection volume of 100 µL. An elution profile was used and listed in Table A. A calibration curve was created by plotting the peak area value as a function of the concentration of the PQ1 standard solutions. The concentration of PQ1 in a sample was then calculated by solving the quadratic equation representing the calibration curve. Three lenses were run for each analysis, and the results were averaged. PQ1 uptake was reported as the percentage loss of PQ1 after soak with lens compared to the PQ1 present in the control without lens.

Table A. HPLC Elution Profile

Time (minutes)	% A	% B	Flow Rate (mL/min)
0.00	100	0	1.2
1.00	100	0	1.2
5.00	0	100	1.2
8.50	0	100	1.2
8.60	100	0	1.2
11.00	100	0	1.2

[0167] The amount of cholesterol absorbed by a contact lens was determined by a LC-MS method (lipid uptake in the data tables). Lenses were soaked in a cholesterol solution and then extracted with dichloromethane. The dichloromethane extract was evaporated and reconstituted with a heptane/isopropanol mixture with subsequent analysis by LC-MS. The results were reported as micrograms of cholesterol per lens. A deuterated cholesterol internal standard was used to improve accuracy and precision of the method.

[0168] A cholesterol stock solution was prepared by placing 15.0 ± 0.5 milligrams of cholesterol into a wide-mouth 10 mL glass volumetric flask followed by dilution with isopropanol.

[0169] A cholesterol soak solution was prepared by placing 0.430 ± 0.010 grams of lysozyme (purity = 93%), 0.200 ± 0.010 grams of albumin, and 0.100 ± 0.010 grams of β-lactoglobulin into a 200 mL glass volumetric flask, adding approximately 190 milliliters of PBS to the flask, and swirling to dissolve the contents. 2 Milliliters of the cholesterol stock solution was then added and diluted to volume with PBS. The volumetric flask was capped and shaken well. The concentration of the cholesterol soak solution was approximately 15 µg/mL. Note: The mass of these components may be adjusted to account for lot-to-lot purity variability so that the target concentrations can be achieved.

[0170] Six contact lenses were removed from their packages and blotted with lint-free paper towels to remove excess packing solution. The lenses were placed into six separate 8 mL glass vials (one lens per vial), and 3.0 mL of the cholesterol soak solution was added to each vial. The vials were capped and placed into a New Brunswick Scientific incubator-shaker for 72 hours at 37°C and 100 rpm. After incubation, each lens was rinsed three times with PBS in 100 mL beakers and placed into a 20-mL scintillation vial.

[0171] To each lens-containing scintillation vial, 5 mL of dichloromethane and 100 µL of the internal standard solution were added. After a minimum of 16 hours of extraction time, the supernatant liquid was transferred into a 5 mL disposable glass culture tube. The tube was placed into the Turbovap and the solvent completely evaporated. Place 1mL of the diluent into the culture tube and re-dissolve the contents. The aforementioned diluent was a 70:30 (v/v) mixture of heptane and isopropanol. The diluent was also the mobile phase. The resulting solution was carefully transferred into an autosampler vial and ready for LC-MS analysis.

[0172] An internal standard stock solution was prepared by weighing approximately 12.5 + 2 mg of deuterated cholesterol (2,2,3,4,4,6-d6-cholesterol) in a 25 mL volumetric flask followed by dilution with the diluent. The concentration of the internal standard stock solution was approximately 500 µg/mL.

[0173] An internal standard solution was prepared by placing 1.0 mL of the internal standard stock solution in a 50mL volumetric flask followed by dilution to volume with diluent. The concentration of this intermediate internal standard solution is approximately 10 µg/mL.

[0174] A reference standard stock solution was prepared by weighing approximately 50 + 5 mg of cholesterol in a 100 mL volumetric flask followed by dilution with diluent. The concentration of the cholesterol in this reference stock solution is approximately 500 µg/mL.

[0175] Working standard solutions were then made according to Table 2 by placing the appropriate amount of standard solutions into the listed 25-mL, 50-mL or 100-mL volumetric flasks. After the standard solutions were added to the volumetric flasks, the mixture was diluted to volume with diluent and swirled well.

Table B. Working Standard Solution Formulations

Working Standard Name	Volume of Internal Standard Solution (mL)	Volume of Reference Standard Stock Solution (µL)	Final Volume (mL)	Approximate Cholesterol Concentration (µg/mL)
Std 1	10	20	100	0.10
Std 2	5	25	50	0.25
Std 3	5	50	50	0.50
Std 4	5	100	50	1.00
Std 5	2.5	125	25	2.50
Std 6	2.5	250	25	5.00

[0176] The following LC-MS analysis was performed:

(1) Make 6 injections of the "Std4" to evaluate system suitability. The RSD% of the peak areas for the working standards and the internal standards must be < 5% and RSD(%) of their peak area ratios must be < 7% to pass system suitability.

(2) Inject working standards 1-6 to create a calibration curve. The square of the correlation coefficient (r²) must be > 0.99.

(3) Inject test samples followed by a bracketing standard (Std4). The peak area ratio of the bracketing standard must be within ± 10% of the averaged peak area ratio from the system suitability injections.

[0177] A calibration curve was constructed by plotting the peak area ratio (reference std/internal std) value that corresponds to the concentration of each working standard solution. The concentration of cholesterol in sample is calculated by solving a quadratic equation. Typical equipment and their settings for the LC-MS analysis are listed below and shown in Tables C and D. The values for the instrument tune parameters may change each time the mass spectrometer is tuned.

Turbovap Conditions:

[0178] 

Temperature: 45°C

Time: 30 minutes or more to dryness

Gas: nitrogen @ 5psi

HPLC Conditions:

[0179] 

HPLC: Thermo Accela HPLC Instrument or equivalent

HPLC Column: Agilent Zorbax NH₂ (4.6 mm × 150 mm; 5 µm particle size)

Mobile Phase: 70% heptane and 30% isopropanol

Column Temperature: 30 °C

Injection Volume: 25 µL

Flow Rate: 1000 µL/min

Table C. Mass Spectrometry Conditions

	Thermo Finnigan TSQ Quantum Ultra
	MS Settings		Value
	Ionization		APCI
	Polarity		Positive
	Scan type		SIM
	APCI probe position		D
	Mass (m/z) of Reference Standards		369.2
	Mass (m/z) of Internal Standards		375.3
	Mass width (m/z)		1.0
	Scan time (s)		0.10
	Data type		Centroid
	Peak Width Q3 (FWHM)		0.40
	Skimmer Offset (V)		10

Table D. Tune Parameters

	Instrument Tune Parameters		Value
	Discharge Current (arbitrary units):		20
	Capillary temperature (°C):		240
	Vaporizer Temperature (°C):		500
	Tube lens offset (V):		68
	Sheath gas pressure (arbitrary units):		20
	Auxiliary gas flow (arbitrary units):		15

[0180] The amount of lysozyme uptake by a contact lens was measured by a HPLC-UV method. Lysozyme uptake was determined as the difference of lysozyme content in phosphate-buffered saline solution (PBS) before contact lenses are immersed and the concentration in the test solution after 72 hours of lens immersion at 37°C.

[0181] A lysozyme soak solution was prepared by placing 0.215 ± 0.005 grams of lysozyme (purity = 93%) into a 100 mL volumetric flask followed by adding 50 mL of PBS to dissolve the lysozyme by swirling followed by dilution to volume with PBS. The resulting lysozyme soak solution was filtered/sterilized using a Millipore Stericup filtration device. The concentration of the lysozyme soak solution is approximately 2000 µg/mL. The mass of lysozyme may be adjusted to account for lot-to-lot purity variability so that a 2000 µg/mL concentration can be achieved.

[0182] Three contact lenses were removed from their packages and blotted with lint-free paper towel to remove excess packing solution. The lenses were placed into three separate 8 mL glass vials (one lens per vial). 1.5 mL of the lysozyme soak solution was added to each vial. The vials were capped and inspected to ensure each lens was completely immersed in the soak solution. As control samples, 1.5 mL of lysozyme soak solution were added into three separate 8 mL glass vials. The samples were then incubated on a New Brunswick Scientific incubator-shaker for 72 hours at 37°C and 100 rpm.

[0183] A diluent was prepared by mixing 900 mL water, 100 mL acetonitrile and 1 mL trifluoroacetic acid into a 1L glass bottle.

[0184] A lysozyme stock solution was prepared by placing 0.240 ± 0.010 grams of lysozyme (purity = 93%) into a 100 mL volumetric flask followed by dilution to volume with diluent. The concentration of the lysozyme stock solution is approximately 2200 µg/mL.

[0185] shown in Table E, a series of working standard solutions was prepared by mixing the appropriate amounts of lysozyme stock solution with diluent using 5 mL volumetric flasks.

Table E. Working Standards

	Working Standard Name		Volume of Stock Solution (mL)		Final Volume (mL)		Approximate Lysozyme Concentration (µg/mL)
	Std 1		1.135		5		500
	Std 2		1.815		5		800
	Std 3		2.725		5		1200
	Std 4		3.635		5		1600
	Std 5		4.540		5		2000
	Std 6 (stock)		-		-		2200

[0186] A 10% (v/v) solution was prepared by adding 1 mL of trifluoroacetic acid into a 10 mL glass volumetric flask followed by dilution with HPLC water. Samples for HPLC-UV analysis were prepared as follows: (1) by placing 1000 µL of test sample and 10 µL of the 10% TFA solution into an autosampler vial or (2) by placing 1000 µL of reference standard and 10 µL of reference standard diluent into an autosampler vial.

[0187] The analysis involved the following steps:

(1) Perform 6 injections of the "Std4" to evaluate system suitability. The RSD% of the peak areas and retention times must be < 0.5% to pass system suitability.

(2) Inject working standards 1-6 to create a calibration curve. The square of the correlation coefficient (r²) must be > 0.99.

(3) Inject test samples followed by a bracketing standard (Std4). The peak area of the bracketing standard must be ± 1% of the averaged peak areas from the system suitability injections.

[0188] A calibration curve was constructed by plotting the peak area value that corresponds to the concentration of each lysozyme working standard solution. The concentration of lysozyme in the test samples was calculated by solving a linear equation. Typical equipment and their settings are listed below or shown in Table F.

Instrument: Agilent 1200 HPLC with UV detection (or equivalent HPLC-UV)

Detection: UV @ 280 nm (5 nm bandwidth)

Column: Phenomenex Luna C5 (50 × 4.6 mm) or Agilent PLRP-S (50 × 4.6 mm)

Mobile Phase A: H₂O (0.1% TFA)

Mobile Phase B: Acetonitrile (0.1% TFA)

Column Temperature: 40 °C

Injection Volume: 10 µL

Table F. HPLC Run Conditions

	Time (minutes)		% A		%B		Flow Rate (mL/min)
	0.0		5		5		1.2
	4.0		5		95		1.2
	4.1		5		5		1.2
	6.5		5		5		1.2

[0189] Alternatively, lysozyme uptake was measured as follows. A lysozyme solution was prepared from chicken egg white (Sigma, L7651) at a concentration of 2 mg/mL in phosphate saline buffer supplemented by sodium bicarbonate at 1.37g/L and D-glucose at 0.1 g/L.

[0190] Three lenses for each test sample were tested using each protein solution, and three were tested using PBS as a control solution. The test lenses were blotted on sterile gauze to remove packing solution and aseptically transferred, using sterile forceps, into sterile 24 well cell culture plates (one lens per well) each well containing 2 mL of the lysozyme solution. Each lens was fully immersed in the solution. As controls, 2 mL of the lysozyme solution was placed in wells without a contact lens.

[0191] The plates were sealed using parafilm to prevent evaporation and dehydration and placed onto an orbital shaker and incubated at 35°C with agitation at 100 rpm for 72 hours. After the 72 hour incubation period, the lenses were rinsed 3 to 5 times by dipping lenses into 200 mL of PBS. The lenses were blotted on a paper towel to remove excess PBS and transferred into sterile conical tubes (1 lens per tube), each tube containing a volume of PBS determined based upon an estimate of lysozyme uptake expected based upon on each lens composition. The lysozyme concentration in each tube to be tested must be within the albumin standards range as described by the manufacturer (0.05 micrograms to 30 micrograms). Samples known to uptake a level of lysozyme lower than 100 µg per lens were diluted 5 times. Samples known to uptake levels of lysozyme higher than 500 µg per lens were diluted 20 times.

[0192] Lysozyme uptake was determined using on-lens bicinchoninic acid method using QP-BCA kit ( Sigma, QP-BCA) following the procedure described by the manufacturer and was calculated by subtracting the optical density measured on PBS soaked lenses from the optical density determined on lenses soaked in lysozyme solution. The optical density was measured using a Synergy II Micro-plate reader capable of reading optical density at 562 nm.

[0193] The invention is now described with reference to the following examples. Before describing several exemplary embodiments of the invention, it is to be understood that the invention is not limited to the details of construction or process steps set forth in the following description. The invention is capable of other embodiments and of being practiced or being carried out in various ways.

[0194] The following abbreviations will be used throughout the Examples and have the following meanings:

BC: back curve plastic mold

FC: front curve plastic mold

RMM: reactive monomer mixture

NVP: N-vinylpyrrolidone (Acros or Aldrich)

DMA: N, N-dimethylacrylamide (Jarchem)

HEMA: 2-hydroxyethyl methacrylate (Bimax)

HPMA: 2-hydroxypropyl methacrylate

HEAA: 2-hydroxyethyl acrylate

Bis-HEAA: N,N-bis(2-hydroxyethyl) acrylamide

GMMA: 2,3-dihydroxypropyl methacrylate

HBMA: 2-hydroxybutyl methacrylate

VMA: N-vinyl N-methyl acetamide (Aldrich)

AA: acrylic acid

MAA: methacrylic acid (Acros)

VINAL: N-[(ethenyloxy)carbonyl]-β-alanine; CAS #148969-96-4

ACA1: 3-acrylamidopropanoic acid

ACA2: 5-acrylamidopropanoic acid

Q Salt or METAC: 2-(methacryloyloxy)ethyl trimethylammonium chloride

AMPS: 2-acrylamido-2-methylpropane sulfonic acid

CBT: 1-Propanaminium, N-(2-carboxyethyl)-N,N-dimethyl-3-[(1-oxo-2-propen-1-yl)amino]-, inner salt; carboxybetaine; CAS 79704-35-1

SBT: 1-Propanaminium, N,N-dimethyl-N-[3-[(1-oxo-2-propen-1-yl)amino]propyl]-3-sulfo-, inner salt; sulfobetaine; CAS 80293-60-3

PBT: 3,5-Dioxa-8-aza-4-phosphaundec-10-en-1-aminium, 4-hydroxy-N,N,N-trimethyl-9-oxo-, inner salt, 4-oxide (9CI); phosphobetaine; CAS 163674-35-9

Blue HEMA: 1-amino-4-[3-( 4-(2-methacryloyloxy-ethoxy)-6-chlorotriazin-2-ylamino)-4-sulfophenylamino]anthraquinone-2-sulfonic acid, as described in US Patent No. 5,944,853

Styryl-TRIS: tris(trimethylsiloxy)silyl styrene (Melrob)

PVMA: poly(N-vinyl N-methyl acetamide)

PVP: poly(N-vinylpyrrolidone) (ISP Ashland)

Poly[DMA-NVP]: random or block copolymer of DMA and NVP

Poly[DMA-CBT]: random or block copolymer of DMA and CBT

EGDMA: ethylene glycol dimethacrylate (Esstech)

TEGDMA: tetraethylene glycol dimethacrylate (Esstech)

TMPTMA: trimethylolpropane trimethacrylate (Esstech)

MBA: methylene bisacrylamide (Aldrich)

TAC: Triallyl Cyanurate (Polysciences)

BMPP: 2,2-bis(4-methacryloxyphenyl)-propane (Polysciences)

BAPP: 2,2-bis[4-(2-acryloxyethoxy)phenyl]propane (Polysciences)

BHMPP: 2,2-bis[4-(2-hydroxy-3-methacryloxypropoxy)phenyl]propane (Polysciences)

Tegomer V-Si 2250: diacryloxypolydimethylsiloxane (Evonik)

Irgacure 819: bis(2,4,6-trimethylbenzoyl)-phenylphosphineoxide (BASF or Ciba Specialty Chemicals)

Irgacure 1870: blend of bis(2,6-dimethoxybenzoyl)-2,4,4-trimethyl-pentylphosphineoxide and 1-hydroxy-cyclohexyl-phenyl-ketone (BASF or Ciba Specialty Chemicals)

AIBN: azobisisobutyronitrile

Te-Bu: ethyl 2-methyl-2-(butyltellanyl)propanoate

TEMPO: 2,6-tetramethylpiperidine N-oxide

TERP: organotellurium mediated living radical polymerization

mPDMS: monomethacryloxypropyl terminated mono-n-butyl terminated polydimethylsiloxane (800-1000 MW) (Gelest)

ac-PDMS: bis-3-acryloxy-2-hydroxypropyloxypropyl polydimethylsiloxane

HO-mPDMS: mono-(2-hydroxy-3-methacryloxypropyl)-propyl ether terminated mono-n-butyl terminated polydimethylsiloxane (400-1000 MW) (Ortec or DSM-Polymer Technology Group)

TRIS: 3-methacryloxypropyl tris(trimethylsiloxy)silane

ac-TRIS: 3-acryloxypropyl tris(trimethylsiloxy)silane

SiMAA: 2-propenoic acid, 2-methyl-2-hydroxy-3-[3-[1,3,3,3-tetramethyl-1-[(trimethylsilyl)oxy]disiloxanyl]propoxy]propyl ester (Toray)

SA2: N-(2,3-dihydroxylpropyl)-N-(3-tetra(dimethylsiloxy)-dimethylbutylsilane)propyl) acrylamide

mPEG 950 : polyethylene glycol mono-methacrylate (Aldrich)

D3O: 3,7-dimethyl-3-octanol (Vigon)

TAM: t-amyl alcohol (BASF)

3E3P: 3-ethyl 3-pentanol

TPME: tripropylene glycol mono-methyl ether

DA: decanoic acid

DI water: deionized water

MeOH: methanol

IPA: isopropyl alcohol

Norbloc: 2-(2'-hydroxy-5-methacrylyloxyethylphenyl)-2H-benzotriazole (Janssen)

P2 Poly[DMA-NVP]: Copolymer of DMA-NVP, M_W = 195 kDa by SEC-MALS, made according to Preparation 2

P3 Poly[DMA-NVP]: Copolymer of DMA-NVP, M_w (MALS) = 304 kDa, made according to Preparation 3

PP: polypropylene which is the homopolymer of propylene

TT: Tuftec which is a hydrogenated styrene butadiene block copolymer (Asahi Kasei Chemicals)

Z: Zeonor which is a polycycloolefin thermoplastic polymer (Nippon Zeon Co Ltd)

EXAMPLES

Preparation 1 - Synthesis of poly(N-vinyl N-methyl acetamide) (PVMA)

[0195] 380 mL (3.48 mol) of distilled N-vinyl-N-methyl acetamide and 187 mg (1.14 mmol) of azobisisobutyronitrile were added to a 3-neck round bottom flask fitted with reflux condenser, magnetic stirring bar and thermocouple and purged of oxygen gas for 2 hours by bubbling nitrogen gas through the reaction mixture. Then, the reaction mixture was heated at 75°C for 24 hours during which time the reaction mixture solidified. The reaction product was quenched in air and isolated by work-up procedure 1 or work-up procedure 2. Work-up Procedure 1: The reaction product was dissolved in 800 mL of methylene chloride at 40°C and cooled to room temperature. The solution was poured into 2L of cold diethyl ether with manual stirring to afford a white solid after decanting off the solvents. The solid product was air dried followed by vacuum drying overnight at 50°C. The precipitated product was ground into a fine white powder and vacuum dried overnight at 50°C (85% yield). Work-up Procedure 2: The reaction product was dissolved in water and dialyzed extensively in dialysis membrane tubing (Spectra Pore MWCO 3500) and freeze dried (LABCONCO, Freezone^® Triad^™ freeze dry system, Model # 7400030) or spray dried (BUCHI mini spray dryer, Model # B-290). The molecular weight was determined by Size Exclusion Chromatography with Multi-Angle Light Scattering (SEC-MALS). The SEC-MALS setup employed methanol (with 10 mM LiBr) as the mobile phase at a flow rate of 0.6 mL/min at 50 °C. Three Tosoh Biosciences TSK-gel columns in series were used [SuperAW3000 4 um, 6.0 mm ID × 15 cm (PEO/DMF Exclusion Limit = 60,000 g/mole), SuperAW4000 6 um, 6.0 mm ID × 15 cm (PEO/DMF Exclusion Limit = 400,000 g/mole) and a SuperAW5000 7 um, 6.0 mm ID × 15 cm (PEO/DMF Exclusion Limit = 4,000,000 g/mole)] with an online Agilent 1200 UV/VIS diode array detector, a Wyatt Optilab rEX interferometric refractometer, and a Wyatt mini-DAWN Treos multiangle laser scattering (MALS) detector (λ=658nm). A dη/dc value of 0.1829 mL/g at 30 °C (λ=658 nm) was used for absolute molecular weight determination. Absolute molecular weights and polydispersity data were calculated using the Wyatt ASTRA 6.1.1.17 SEC/LS software package. The weight average molecular weight typically varied from about 500 kDa to about 700 kDa, but can be controlled by the reaction conditions and isolation procedures. The polydispersity varied from about 1.8 to about 2.8 among the samples.

Preparation 2 - TERP Synthesis of Poly[DMA-NVP], M_W = 195 kDa

[0196] 12 milligrams (0.073 mmol) AIBN were dissolved in 200 mL MeOH in a 500 mL three necked round bottom flask equipped with a reflux condenser and pressure balanced addition funnel and containing a magnetic stirring bar. 42 grams (424 mmol) DMA and 47.09 grams (424 mmol) NVP were dissolved in 100 mL MeOH and added into the addition funnel. The solutions in both the round bottom flask and the addition funnel were purged with nitrogen gas for 30 minutes. Then, 26 milligrams (0.1 mmol) of Te-Bu were added into the round bottom flask, and heating of the round bottom flask to reflux (about 65°C) commenced. Slow dropwise addition of the monomer solution also started when heating commenced. The monomer addition occurred over 7.5 hours. The reaction mixture was then allowed to cool down to room temperature. The MeOH was removed by rotary evaporation. The crude product was re-dissolved in MeOH and precipitated into hexanes three times. The copolymer was vacuum dried at 50°C.

Preparation 3: Poly[DMA-NVP], M_w (MALS) = 304 kDa

[0197] 12 milligrams (0.073 mmol) AIBN were dissolved in 200 mL MeOH in a 500 mL three necked round bottom flask equipped with a reflux condenser and pressure balanced addition funnel and containing a magnetic stirring bar. 42 grams (424 mmol) DMA and 47.09 grams (424 mmol) NVP were dissolved in 100 mL MeOH and added into the addition funnel. The solutions in both the round bottom flask and the addition funnel were purged with nitrogen gas for 60 minutes. Then, 26 milligrams (0.1 mmol) of Te-Bu were added into the round bottom flask, and heating of the round bottom flask to reflux (about 65°C) commenced. Slow dropwise addition of the monomer solution also started when heating commenced. The monomer addition occurred over 4 hours. The reaction mixture was then refluxed for 20 hours thereafter 45 milligrams (0.29 mmol) TEMPO were added and the reaction mixture refluxed for another 5 hours. The reaction mixture was then allowed to cool down to room temperature. The reaction mixture was concentrated by rotary evaporation, and the crude product isolated by precipitation into diethyl ether. After decanting off the supernatant liquid, the crude product was re-dissolved in methylene chloride and precipitated into diethyl ether three times. The copolymer was vacuum dried at 70°C.

Preparation 4 - TERP Synthesis of Poly[DMA-CBT]

[0198] 26 milligrams (0.16 mmol) AIBN, 20 grams (202 mmol) DMA and 5 grams (22 mmol) CBT were dissolved in 200 mL 50% (v/v) aqueous MeOH in a 500 mL round bottom flask equipped with a reflux condenser and containing a magnetic stirring bar. 41 milligrams (0.16 mmol) of Te-Bu were dissolved in 50 mL 50% (v/v) aqueous MeOH. Both solutions were purged with nitrogen gas for 30 minutes. Then, the Te-Bu solution was added to the round bottom flask and heated to reflux (about 62°C) for 12 hours. The reaction mixture was allowed to cool down to room temperature. The aqueous MeOH was removed by rotary evaporation. The crude product was dissolved in 500 mL acetone and precipitated by slowing adding 250 mL of hexane with stirring. After decanting off the supernatant liquid, the copolymer was vacuum dried at 62-68°C. Copolymer designated as Poly[DMA-CBT].

Comparative Examples 1-5

[0199] Each reactive mixture was formed by mixing the reactive components listed in Table 2, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 55-60°C, and the lenses were cured from the top for 20 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays. The weight ratio of OH-mPDMS, n=4 to mPDMS 1000, n=10 was 1.7. The molar ratio of OH-mPDMS, n=4 to mPDMS 1000, n=10 was 2.8.

[0200] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 50% IPA for about one or two hours, followed by washing with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 3.

TABLE 2

Component	CEx 1	CEx 2	CEx 3	CEx 4	CEx 5	CEx 6	CEx 7	CEx 8
mPDMS 1000, n=10	16.5	16.5	16.5	16.5	16.5	16.5	16.5	16.5
OH-mPDMS, n=4	27.5	27.5	27.5	27.5	27.5	27.5	27.5	27.5
NVP	46.65	44.15	41.65	39.15	35.15	23.35	11.5	0
HEMA	6.75	6.75	6.75	6.75	6.75	6.75	6.75	6.75
DMA	0	2.5	5	7.5	11.5	23.3	35.15	46.65
EGDMA	0.35	0.35	0.35	0.35	0.35	0.35	0.35	0.35
Norbloc	1.75	1.75	1.75	1.75	1.75	1.75	1.75	1.75
CGI 819	0.5	0.5	0.5	0.5	0.5	0.5	0.5	0.5
Diluent	10	10	10	10	10	10	10	10
TAM	100	100	100	100	100	100	100	100

TABLE 3

Lens	Weight %Water	%Haze	DCA (advancing)	Mechanicals		Dk
				M (psi)	%ETB
CEx 1	61 (0)	6 (1)	48 (6)	75 (10)	145 (57)	92
CEx 2	63 (0)	7 (1)	79 (9)	57 (6)	171 (36)	89
CEx 3	63 (0)	9 (1)	107 (3)	52 (4)	164 (53)	89
CEx 4	63 (0)	9 (1)	110 (4)	46 (6)	162 (45)	89
CEx 5	60 (0)	6 (1)	119 (15)	53 (6)	184 (56)	85
CEx 6	56 (0)	4 (0)	114 (13)	66 (6)	195 (44)	72
CEx 7	54 (0)	4 (1)	107 (5)	87 (10)	211 (56)	56
CEx 8	56 (0)	4 (1)	114 (19)	85 (10)	258 (58)	54

[0201] The wettability of NVP based silicone hydrogels without a polymeric wetting agent was reduced by small amounts of DMA in the reactive mixture. At 2.5 wt% DMA and above, the advancing contact angle increased to 107° (59° increase) compared to formulations without DMA (Comparative Example 6, with a DCA of 48°).

Comparative Examples 9-12

[0202] Each reactive mixture was formed by mixing the reactive components listed in Table 4, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 55-60°C, and the lenses were cured from the top for 20 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0203] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 50% IPA for about one or two hours, followed by washing with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 5.

TABLE 4

Component	CEx 9	CEx 10	CEx 11	CEx 12
mPDMS 1000	16.5	16.5	16.5	16.5
OH-mPDMS, n=4	27.5	27.5	27.5	27.5
NVP	46.55	46.05	45.55	44.05
HEMA	6.75	6.75	6.75	6.75
DMA	0	0.5	1	2.5
EGDMA	0.45	0.45	0.35	0.35
Norbloc	1.75	1.75	1.75	1.75
CGI 819	0.5	0.5	0.5	0.5
Diluent	0	0	0	0

TABLE 5

Lens	Weight % Water	%Haze	DCA (Advancing)	Mechanicals		Dk
				M (psi)	%ETB
CEx 9	54 (0)	9 (0)	50 (4)	111 (12)	148 (39)	98
CEx 10	54(0)	11 (1)	58 (9)	117 (8)	167 (36)	97
CEx 11	55 (0)	10 (1)	64 (4)	122 (9)	170 (27)	97
CEx 12	54 (0)	10 (0)	93 (11)	100 (7)	146 (31)	100

[0204] These comparative Examples confirm that as little as about 2 wt% DMA in silicone hydrogel formulations containing greater than about 40 wt% NVP degrade wettability.

Examples 1-3

[0205] Each reactive mixture was formed by mixing the reactive components listed in Table 6, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 20 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0206] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 7. The homogeneity of the reactive mixtures improved as the amount of OH-mPDMS n=4 increased. Only lenses from Example 3 were suitable for testing, and their wettability was limited (91°) despite the presence poly[DMA-NVP] in the formulation at 2wt%.

TABLE 6

Component	Ex 1	Ex 2	Ex 3
OH-mPDMS (n=15)	44.25	40.66	35
OH-mPDMS (n=4)	0	8.11	12.85
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0	0.20	0.37
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0	0.47	0.86
NVP	40.6	37.31	37
HEMA	10	9.19	10
P2:P[DMA-NVP]	2	1.84	2
MAA	0.75	0.69	0.75
TEGDMA	0.2	0.18	0.2
TAC	0.2	0.18	0.2
Norbloc	1.75	1.61	1.75
CGI 819	0.25	0.23	0.25
Diluent	15	13.95	15
TAM	100	100	100

TABLE 7

Lens	Weight % Water	% Haze	DCA (°) (adv, rec)	Mechanicals		Dk
				M (psi)	%ETB
Ex 3	53 (0)	5(1)	91 (5), 27 (11)	101 (7)	159 (44)	89

Examples 4-8

[0207] Each reactive mixture was formed by mixing the reactive components listed in Table 8, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of a 90:10 (w/w) Z:PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 20 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0208] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The lenses of Examples 4 and 5 were hazy (subjectively observed), and were not further analyzed. The physical and mechanical properties of the sterile lenses were measured and listed in Table 9.

TABLE 8

Component	Ex 4	Ex 5	Ex 6	Ex 7	Ex 8
OH-mPDMS (n=15)	25	0	25	25	30
OH-mPDMS (n=4)	30	55	30	30	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.2	-	1.2	1.2	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	2.8	-	2.8	2.8	1.94
NVP	10.35	10.35	13.35	16.35	16.35
HEMA	9.5	9.5	10.5	10.5	10.5
P2:[DMA-NVP]	17	17	15	12	12
mPEG 950	5	5	3	3	3
MAA	0.75	0.75	0.75	0.75	0.75
TEGDMA	0.2	0.2	0.2	0.2	0.2
TAC	0.2	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75	1.75
CGI 819	0.25	0.25	0.25	0.25	0.25
Diluent	23	23	20	20	20
TAM	100	100	100	100	100

TABLE 9

Lens	Weight % Water	% Haze	DCA (°) (adv, rec)	Mechanicals		Dk
				M (psi)	%ETB
Ex 6	51 (0)	38 (2)	99 (7), 15 (8)	84 (5)	158 (34)	148
Ex 7	50 (1)	19 (1)	83 (13), 2 (5)	116 (7)	178 (37)	135
Ex 8	48 (0)	12 (2)	53 (6), 47 (2)	118 (9)	163 (43)	140

[0209] Example 8 had 12 wt% DMA/NVP copolymer and displayed a very desirable contact angle (53° advancing DCA) and haze (12%). Examples 6-8 had good haze values. Comparing Example 6 to Example 7 shows that decreasing the concentration of acyclic polyamide improves both haze and contact angle, suggesting that a desirable balance of properties could be achieved by maintaining a ratio of first to second silicone-containing component of 1.2, and decreasing the concentration of acyclic polyamide. Example 8 had a ratio of first to second silicone-containing component of 0.87, and showed improved haze and contact angle compared to Example 7. Thus, properties may also be balanced by maintaining the concentration of the acyclic polyamide, and decreasing the ratio first to second silicone-containing component to within the recited ranges.

Examples 9-11

[0210] Each reactive mixture was formed by mixing the reactive components listed in Table 10, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP or a blend of 90:10 (w/w) Z:PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 20 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0211] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 11.

TABLE 10

Component	Ex 9	Ex 10	Ex 11
OH-mPDMS (n=15)	30	30	30
OH-mPDMS (n=4)	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.83	0.83	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.94	1.94	1.94
NVP	16.35	16.35	16.35
HEMA	10.5	10.5	10.5
P2:P[DMA-NVP]	12	0	0
P3:P[DMA-NVP]	0	12	12
mPEG 950	3	3	3
MAA	0.75	0.75	0.75
TEGDMA	0.2	0.2	0.2
TAC	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75
CGI 819	0.25	0.25	0.25
Diluent	20	20	20
TAM	100	100	100

TABLE 11

Lens	Weight % Water	% Haze	DCA (°) (adv, rec)	Mechanicals		Dk
				M (psi)	%ETB
Ex 9	48 (0)	12 (2)	53 (6), 47 (2)	118 (9)	163 (43)	140
Ex 10	52 (0)	16 (1)	67 (8), 28 (4)	97 (8)	194 (23)	122
Ex 11	51 (1)	24 (2)	64 (6), 27(10)	121 (9)	186 (35)	135

[0212] Copolymer P2 had a molecular weight (Mw) of 195kD and copolymer P3 had a Mw of 305 KDa. Examples 9-11 all displayed good haze and contact angle, confirming that copolymeric wetting agents having molecular weights above about 190 kDa can provide desirable wettability and haze.

Examples 12-15

[0213] Each reactive mixture was formed by mixing the reactive components listed in Table 12, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of a blend of 90:10 (w/w) Z:PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 15 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0214] The lenses were manually de-molded with most lenses adhering to the FC and released by heating about 64 lenses in about one liter of DI water at 75°C for about 30-60 minutes, followed by washing two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 13.

TABLE 12

Component	Ex 12	Ex 13	Ex 14	Ex 15
OH-mPDMS (n=15)	30	30	30	30
OH-mPDMS (n=4)	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.83	0.83	0.83	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.94	1.94	1.94	1.94
NVP	16.35	16.35	16.35	16.35
HEMA	10.5	10.5	10.5	10.5
P3:Poly [DMA-NVP]	12	0	0	0
PVMA 380 kDa	0	12	0	0
PVMA 628 kDa	0	0	12	0
PVMA 1600 kDA	0	0	0	12
mPEG 950	3	3	3	3
MAA	0.75	0.75	0.75	0.75
TEGDMA	0.2	0.2	0.2	0.2
TAC	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75
CGI 819	0.25	0.25	0.25	0.25
Diluent	20	20	20	20
TAM	100	100	100	100

TABLE 13

Lens	Weight % Water	% Haze	DCA (°) (adv, rec)	Mechanicals		Dk	RI
				M (psi)	%ETB
Ex 12	51 (1)	24 (2)	64 (6), 27(10)	121 (9)	186 (35)	135	1.4002
Ex 13	52 (0)	28 (2)	64 (16), 28 (7)	95 (6)	194 (41)	147	1.3990
Ex 14	53 (0)	36 (4)	44 (11), 36 (4)	105 (4)	195 (47)	135	1.3954
Ex 15	54 (0)	24 (2)	34 (11), 27 (4)	103 (11)	189 (56)	122	1.3949 7

[0215] Examples 12-15 all displayed desirable haze and contact angles. As the molecular weight (Mw) of the PVMA increased, the contact angle decreased, with Examples 14 (Mw of 628 kD) and 15 (Mw of 1600 kD) displaying improved wettability and decreased hysteresis compared to Example 13.

Examples 16-20

[0216] Each reactive mixture was formed by mixing the reactive components listed in Table 14, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 25 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0217] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 15.

TABLE 14

Component	Ex 16	Ex 17	Ex 18	Ex 19	Ex 20
OH-mPDMS (n=15)	30	30	30	30	30
OH-mPDMS (n=4)	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.83	0.83	0.83	0.83	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.94	1.94	1.94	1.94	1.94
NVP	16.23	16.10	16.35	16.23	16.10
HEMA	10.5	10.5	10.5	10.5	10.5
PVMA 628 kDa	6	6	12	12	12
PVMA 1600 kDa	6	6	0	0	0
mPEG 950	3	3	3	3	3
MAA	0.75	0.75	0.75	0.75	0.75
TEGDMA	0.2	0.2	0.2	0.2	0.2
TAC	0.2	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75	1.75
CGI 819	0.37	0.5	0.25	0.37	0.5
Diluent	20	20	20	20	20
TAM	100	100	100	100	100

TABLE 15

Lens	Weight % Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	RI
				M (psi)	%ETB
Ex 16	55 (0)	38 (5)	50 (7), 27 (9)	81 (8)	202 (55)	120	1.3946
Ex 17	56 (1)	38 (3)	46 (5), 23 (5)	81 (5)	157 (60)	130	1.3947
Ex 18	51 (0)	38 (4)	48 (11), 6 (6)	85 (8)	218 (23)	144	1.4015
Ex 19	53 (0)	32 (2)	71 (12), 20 (15)	84 (6)	181 (50)	129	1.3969
Ex 20	55 (1)	41 (4)	76 (7), 7 (8)	63 (5)	150 (57)	124	1.3996

[0218] Examples 16 and 17 contain a mixture of PVMA (6% 628kD and 6% 1600 kD Mw). Examples 19 and 20 were made from similar formulations, but with 12% of PVMA having a Mw of 628 kD. Examples 16 and 17, with the mixture including higher molecular weight PVMA displayed lower contact angles.

Example 21-24

[0219] Each reactive mixture was formed by mixing the reactive components listed in Table 16, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 15-25 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0220] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 17.

TABLE 16

Component	Ex 21	Ex 22	Ex 23	Ex 24
OH-mPDMS (n=15)	30	30	30	30
OH-mPDMS (n=4)	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.83	0.83	0.83	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.94	1.94	1.94	1.94
NVP	16.1	15	15	12
DMA	0	1.1	1.1	4.1
HEMA	10.5	11	11	11
PVMA 628 kDa	12	12	6	6
PVMA 1600 kDa	3	0	6	6
mPEG 950	3	3	3	3
MAA	0.75	0.75	0.75	0.75
TEGDMA	0.2	1	1	1
TAC	0.2	0	0	0
Norbloc	1.75	2	2	2
CGI 819	0.5	0.25	0.25	0.25
Cure Time (min)	25	15	28	28
Diluent	20	20	28	28
D3O	100	100	100	100

TABLE 17

Lens	Weight % Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	RI	Lipids (µg/lens)
				M (psi)	%ETB
Ex 21	56 (0)	32 (2)	56 (17), 19 (12)	69 (7)	156 (60)	126	1.3967 (006)	6.23 (0.21)
Ex 22	55 (0)	17 (1)	34 (3), 22 (9)	67 (7)	166 (58)	131	1.3979 (005)	6.2 (0.27)
Ex 23	56 (0)	16 (1)	54 (27), 21 (3)	52 (7)	195 (53)	121	1.3966 (009)	6.97 (0.70)
Ex 24	54 (0)	25 (1)	31 (28), 11 (14)	64 (5)	178 (56)	123	1.3963 (011)	6.28 (0.39)

[0221] The concentration of DMA in the reactive mixture was increased from 0 wt% (Example 21) to 4.1 wt% (Example 24), and the advancing contact angle remained below about 50°. This is in contrast to Comparative Examples 6-17, which showed that in NVP formulations without a combination of hydroxyl-substituted polydialkylsiloxanes, the inclusion of as little as about 2 wt% DMA increased contact angle above about 80°. Examples 21 -24 also show lipid uptake of about 6 µg/lens, which is desirably low. Commercially available lenses containing PVP display lipid uptake values of about 10 µg/lens.

Example 25-29

[0222] Each reactive mixture was formed by mixing the reactive components listed in Table 18, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 25 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0223] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 19.

TABLE 18

Component	Ex 25	Ex 26	Ex 27	Ex 28	Ex 29
OH-mPDMS (n=15)	30	33	33	33	33
OH-mPDMS (n=4)	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.83	0.76	0.76	0.76	0.76
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.94	1.77	1.77	1.77	1.77
NVP	7.84	6.33	6.11	5.36	4.61
DMA	7.84	6.35	6.12	5.37	4.62
HEMA	10.5	10.5	10.5	10.5	10.5
PVMA 628 kDa	9	9	12	13.5	15
PVMA 1600 kDa	3	3	0	0	0
mPEG 950	3	3	3	3	3
MAA	0.75	0.75	0.75	0.75	0.75
TEGDMA	0.75	0.75	1.2	1.2	1.2
TAC	0.2	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75	1.75
CGI 819	0.37	0.37	0.37	0.37	0.37
Diluent	20	23	23	23	23
D3O	100	100	100	100	100

TABLE 19

Lens	Weight % Water	% Haze	DCA (adv/rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
Ex 25	55 (0)	19 (1)	6 (12), 6 (12)	79 (5)	171 (44)	129	NT	NT	6.33 (0.40)
Ex 26	53 (0)	29 (1)	56 (35), 16 (17)	83 (7)	194 (65)	135	NT	NT	6.25 (0.47)
Ex 27	49(0)	20 (1)	0 (0), 2 (4)	86 (10)	177 (70)	132	81(2)	3.47 (1.42)	5.46 (0.49)
Ex 28	50 (0)	26 (1)	9 (11), 7 (12)	90(6)	179 (59)	144	49(3)	1.77 (0.88)	5.72 (0.2)
Ex 29	48(0)	33 (2)	9 (15), 8 (12)	96 (9)	165 (46)	162	19(4)	0.64 (0.55)	5.360.15)

[0224] Lenses made from PVMA 628 kDa and mixtures DMA and NVP exhibited very low lipid (less than 7 µg/lens) and PQ1 uptake (less than 5%) as well as an excellent balance of physical and mechanical properties. The concentration of DMA in the reactive mixture was varied from about 5 wt% (Example 29) to about 8% (Example 25), and the advancing contact angle remained below about 60°, and in Examples 25, 27-29, below about 10°.

Example 30-34

[0225] Each reactive mixture was formed by mixing the reactive components listed in Table 20, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC. The BC was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. Examples 30-32 used FC made of a 90:10 (w/w) blend of Z:TT and BC made of PP; examples 33-38 used FC made of Z and BC made of a 55:45 (w/w) blend of Z:PP. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 25 minutes using TLO3 lights having intensity of 4-5 mW/cm² for Examples 30-32 and 3-4 mW/cm² for Examples 33-38. The light source was about six inches above the trays.

[0226] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 21.

TABLE 20

Component	Ex 30	Ex 31	Ex 32	Ex 33	Ex 34	Ex 35	Ex 36	Ex 37	Ex 38
OH-mPDMS (n=15)	33	33	33	32	32	32	32	31	30
OH-mPDMS (n=4)	25	25	25	25	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.76	0.76	0.76	0.78	0.78	0.78	0.78	0.81	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.77	1.77	1.77	1.82	1.82	1.82	1.82	1.87	1.94
NVP	5.36	5.26	5.16	5.41	5.41	5.66	5.54	5.54	5.54
DMA	5.37	5.27	5.17	5.42	5.42	5.67	5.54	6.54	7.54
HEMA	10.5	10.5	10.5	10.73	11.33	11.33	11.33	11.33	11.33
Blue HEMA	0	0	0	0.02	0.02	0.02	0.02	0.02	0.02
PVMA 628 kDa	13.5	13.5	13.5	13.5	13.5	13.5	13.5	13.5	13.5
mPEG 950	3	3	3	3	3	3	3	3	3
MAA	0.75	0.75	0.75	1	1	1	1	1	1
TEGDMA	1.2	1.40	1.60	1.60	0	0	0	0	0
TAC	0.2	0.2	0.2	0.2	0.2	0.2	0.2	0.2	0.2
EGDMA	0	0	0	0	1	0.5	0.75	0.75	0.75
Norbloc	1.75	1.75	1.75	1.75	1.75	1.75	1.75	1.75	1.75
CGI 819	0.37	0.37	0.37	0.37	0.37	0.37	0.37	0.37	0.37
Diluent	23	23	23	23	23	23	23	23	23
D3O	100	100	100	100	100	100	100	100	100

TABLE 21

Lens	Weight % Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
Ex 30	50 (0)	24 (2)	16 (14), 16 (13)	94(7)	168 (37)	148	57 (8)	3.02 (3.39)	6.58 (0.29)
Ex 31	50 (0)	20 (1)	75 (42), 3 (5)	100 (7)	155 (43)	147	52 (8)	4.21 (1.02)	7.10 (0.53)
Ex 32	49 (1)	17 (1)	24 (26), 3 (6)	92 (8)	128 (30)	151	35 (7)	1 (1.64)	6.70 (0.53)
Ex 33	49 (0)	18 (1)	12 (13), 4 (7)	107 (14)	115 (32)	145	134 (11)	6.06 (0.29)	6.73 (0.74)
Ex 34	44 (0)	10 (1)	24 (12), 0 (0)	193 (15)	92 (26)	151	51 (6)	5.74 (0.18)	2.58 (6.36)
Ex 35	50 (0)	18 (1)	65 (11), 13 (16)	103 (8)	164 (46)	142	186 (14)	6.65 (0.27)	10.64 (1.64)
Ex 36	48 (0)	13 (1)	30 (14), 21 (17)	151 (11)	110 (31)	147	119 (8)	6.02 (0.13)	2.68 (0.33)
Ex 37	48 (0)	13 (1)	41 (9), 27 (16)	135 (11)	123 (32)	140	217 (15)	6.05 (0.12)	2.52 (7.47)
Ex 38	49 (0)	11 (1)	42 (5), 37 (5)	127 (11)	129 (27)	125	301 (14)	6.46 (0.14)	2.772.24)

[0227] Lenses made from PVMA 628 kDa and mixtures DMA and NVP exhibited surprisingly excellent biometrics, including lipid uptake of about 10 µg/lens or less and PQ1 uptake less than about 10%, and moderate lysozyme uptake, as well as an excellent balance of physical and mechanical properties.

Examples 39-43

[0228] Each reactive mixture was formed by mixing the reactive components listed in Table 22, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of 90:10 (w/w) Z:TT. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 12 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0229] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 23.

TABLE 22

Component	Ex 39	Ex 40	Ex 41	Ex 42	Ex 43
OH-mPDMS (n=15)	33	33	33	33	33
OH-mPDMS (n=4)	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.76	0.76	0.76	0.76	0.76
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.77	1.77	1.77	1.77	1.77
NVP	5.16	5.04	4.91	4.79	4.66
DMA	5.17	5.04	4.92	4.79	4.67
HEMA	10.5	10.5	10.5	10.5	10.5
PVMA 628 kDa	13.5	13.5	13.5	13.5	13.5
mPEG 950	3	3	3	3	3
MAA	0.75	1	1.25	1.5	1.75
TEGDMA	1.60	1.60	1.60	1.60	1.60
TAC	0.2	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75	1.75
CGI 819	0.37	0.37	0.37	0.37	0.37
Diluent	23	23	23	23	23
D3O	100	100	100	100	100

TABLE 23

Lens	Weight % Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
Ex 39	49 (1)	17 (1)	24 (26), 3 (6)	92 (8)	128 (30)	151	35 (7)	1 (1.64)	7.10 (0.53)
Ex 40	49 (0)	22 (1)	52 (34), 10 (14)	100 (13)	136 (31)	146	113 (9)	4.21 (0.59)	6.98 (0.35)
Ex 41	49 (0)	16 (1)	61 (27), 16 (7)	89 (12)	108 (63)	156	253 (7)	14.99 (3.58)	7.89 (0.41)
Ex 42	51 (0)	18 (1)	14 (19), 8 (10)	93 (14)	123 (47)	142	506 (29)	39.70 (2.45)	7.34 (0.37)
Ex 43	52 (0)	14 (1)	48 (36), 7 (8)	95 (10)	131 (38)	134	868 (28)	59.49 (6.05)	8.650.81)

[0230] Lysozyme uptake and PQ1 uptake increased with MAA content.

Examples 44-45

[0231] Example 41 was repeated, except that the ratio of the hydroxyl-containing silicone components was varied, as shown in Table 24. Example 44 is the same lens as Example 41, with only the lysozyme uptake test repeated. Each reactive mixture was formed by mixing the reactive components listed in Table 24, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 20 minutes using TLO3 lights having intensity of 3-4 mW/cm². The light source was about six inches above the trays.

[0232] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 25.

TABLE 24

Component	Ex 44	Ex 45	Ex 46	Ex 47	Ex 48	Ex 49	Ex 50
OH-mPDMS (n=15)	33	32.5	32	31.5	31	30.5	30
OH-mPDMS (n=4)	25	25	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.76	0.77	0.78	0.79	0.81	0.82	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.77	1.79	1.82	1.84	1.87	1.91	1.94
NVP	4.91	5.16	5.41	5.66	5.91	6.16	6.41
DMA	4.92	5.17	5.42	5.67	5.92	6.17	6.42
HEMA	10.5	10.5	10.5	10.5	10.5	10.5	10.5
PVMA 628 kDa	13.5	13.5	13.5	13.5	13.5	13.5	13.5
mPEG 950	3	3	3	3	3	3	3
MAA	1.25	1.25	1.25	1.25	1.25	1.25	1.25
TEGDMA	1.60	1.60	1.60	1.60	1.60	1.60	1.60
TAC	0.2	0.2	0.2	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75	1.75	1.75	1.75
CGI 819	0.37	0.37	0.37	0.37	0.37	0.37	0.37
Diluent	23	23	23	23	23	23	23
D3O	100	100	100	100	100	100	100

TABLE 25

Lens	Weight % Water	% Haze	DCA	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
Ex 44	49 (0)	16 (1)	61 (27), 16 (7)	89 (12)	108 (63)	156	230 (16)	14.99 (3.58)	7.89 (0.41)
Ex 45	50 (1)	16 (0)	21 (16), 14 (13)	100(11)	123 (36)	145	250 (17)	11.87 (3.26)	6.90 (0.29)
Ex 46	50 (0)	16 (0)	20 (14), 3 (6)	101 (7)	129 (30)	145	288 (36)	12.23 (2.82)	7.17 (0.26)
Ex 47	50 (0)	14 (1)	65 (21), 16 (11)	97 (12)	133 (26)	158	290 (7)	11.97 (3.07)	7.49 (0.49)
Ex 48	52 (0)	14 (1)	23 (16), 21 (18)	100 (7)	107 (38)	132	451 (39)	14.73 (3.09)	7.02 (0.12)
Ex 49	52 (0)	14 (1)	40 (32), 15 (10)	96(9)	109 (44)	131	471 (12)	14.97 (2.86)	7.74 (0.47)
Ex 50	52 (0)	11 (1)	25 (18), 17 (17)	98(8)	144 (36)	133	517(23)	15.2 (1.08)	6.520.16)

[0233] All lenses showed a desirable balance of mechanical and biometric properties.

Examples 51-52

[0234] Each reactive mixture was formed by mixing the reactive components listed in Table 26, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 25 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0235] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 27.

TABLE 26

Component	Ex 51	Ex 52
OH-mPDMS (n=15)	30	30
OH-mPDMS (n=4)	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.83	0.83
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.94	1.94
NVP	7.22	6.12
DMA	7.22	6.12
HEMA	10.5	10.5
PVMA 628 kDa	9	15
PVMA 1600 kDa	3	0
mPEG 950	3	3
MAA	0.75	0.75
Q-Salt	1.25	0
TEGDMA	0.75	1.2
TAC	0.2	0.2
Norbloc	1.75	1.75
CGI 819	0.36	0.36
Diluent	20	23
D3O	100	100

TABLE 27

Ex #	% Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
51	52 (0)	18 (1)	19 (19), 21 (19)	70 (6)	204 (49)	132	47 (5)	5.93 (0.49)	2.77 (1.39)
52	56 (0)	14 (1)	28 (6), 9 (10)	76(13)	146 (55)	121	258 (19)	5.80 (0.16)	4.05 (3.09)

[0236] Lenses containing an ammonium chloride salt (Q-Salt) displayed greatly reduced lysozyme uptake, but a good balance of mechanical properties and low PQ-1 and lipid uptake. This example shows that cationic components can be added, without negatively impacting compatibility (as shown by the 18% haze) and while maintaining a desirable balance of properties.

Examples 53-55

[0237] Each reactive mixture was formed by mixing the reactive components listed in Table 28, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 25 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0238] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 29.

TABLE 28

Component	Ex 53	Ex 54	Ex 55
OH-mPDMS (n=15)	32	32	32
OH-mPDMS (n=4)	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.78	0.78	0.78
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.82	1.82	1.82
NVP	5.41	6.91	5.45
DMA	5.42	6.92	5.46
HEMA	11.33	11.33	12.75
Blue HEMA	0.02	0.02	0.02
PVMA 628 kDa	13.5	13.5	10
Poly [DMA-co-CBT]	0	0	5
mPEG 950	3	0	0
MAA	1	1	1
EGDMA	1	1	1
TAC	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75
CGI 819	0.37	0.37	0.37
Diluent	23	23	23
D3O	100	100	100

TABLE 29

Ex.	% Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
53	44 (0)	10 (1)	24 (12), 0 (0)	193 (15)	92 (26)	151	51 (6)	2.58 (6.36)	5.74 (0.18)
54	44 (0)	14 (1)	29 (10), 6 (11)	182 (20)	93 (34)	151	57 (5)	8.46 (2.44)	5.71 (0.36)
55	44 (0)	30 (2)	18 (13), 3 (7)	164 (14)	121 (31)	132	106 (8)	21.80 (1.03)	6.020.2)

[0239] The Poly[DMA-co-CBT], is a random copolymer of DMA and 20 wt% (10 mol%) zwitterionic monomer carboxybetaine. Carboxybetaine is highly hydrophilic internal salt which is generally poorly compatible with silicone hydrogel reactive mixtures. It was surprising that 5wt% of this copolymer could be incorporated into silicone hydrogels formulations displaying only 30% haze. Lenses containing zwitterionic internal wetting agent showed increased lysozyme and PQ1 uptake.

Examples 56-63

[0240] A series of lenses were made from reactive mixtures with varying formulation components, including hydrophilic monomer, hydroxyl-containing silicone component, types and amount of crosslinker and amounts of ionic monomer. Each reactive mixture was formed by mixing the reactive components listed in Table 30, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 12 minutes using TLO3 lights having intensity of 4-5 mW/cm². The light source was about six inches above the trays.

[0241] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 31.

TABLE 30

Component	Ex 56	Ex57	Ex 58	Ex 59	Ex 60	Ex 61	Ex 62	Ex 63
OH-mPDMS (n=15)	31	31	31	31	30	31	32	33
OH-mPDMS (n=4)	25	25	25	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.81	0.81	0.81	0.81	0.83	0.81	0.78	0.76
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.87	1.87	1.87	1.87	1.94	1.87	1.82	1.77
NVP	5.54	5.54	5.54	4.54	0	0	0	0
DMA	6.54	6.54	6.54	6.04	16.03	15.03	14.03	13.03
HEMA	11.33	11.33	11.33	11.33	10.5	10.5	10.5	10.5
Blue HEMA	0.02	0.02	0.02	0.02	0.02	0.02	0.02	0.02
PVMA 628 kDa	13.5	13.5	13.5	15	13.5	13.5	13.5	13.5
mPEG 950	3	3	3	3	0	0	0	0
MAA	1	1	1	1	1.25	1.25	1.25	1.25
TEGDMA	0	0	0	0	1.6	1.6	1.6	1.6
EGDMA	0.75	0.75	0.75	0.75	0	0	0	0
TAC	0.2	0.2	0.2	0.2	0	0	0	0
Norbloc	1.75	1.75	1.75	1.75	1.75	1.75	1.75	1.75
CGI 819	0.37	0.37	0.37	0.37	0.35	0.35	0.35	0.35
Diluent	25	27.5	30	30	23	23	23	23
D3O	100	100	100	100	100	100	100	100

TABLE 31

Ex	% Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
56	49(0)	15 (1)	36 (22), 27 (17)	111(11)	160(49)	125	294 ± 25	3.81 (0.44)	NT
57	49 (0)	14 (1)	46 (15), 27 (9)	99 (11)	168 (36)	130	317 ± 27	5.61 (0.27)	NT
58	50 (0)	13 (1)	29 (9), 17 (9)	96 (6)	158 (37)	138	341 ± 12	1.98 (0.90)	NT
59	51 (0)	13 (1)	26 (5), 10 (9)	115 (11)	136 (53)	135	191 ± 25	1.10 (1.36)	NT
60	53 (0)	12 (2)	67 (30), 6 (8)	84 (8)	149 (59)	125	819 (66)	49.47 (5.05)	6.95 (1.26)
61	51 (0)	12 (1)	79 (18), 17 (14)	87 (13)	125 (52)	128	596 (47)	48.5 (2.44)	9.2 (0.78)
62	50 (0)	11 (1)	39 (2), 11 (7)	97 (13)	128 (40)	139	428 (7)	48.83 (2.54)	6.66 (0.09)
63	51 (0)	15 (1)	40 (14), 0 (0)	98 (8)	140 (44)	140	355 (17)	52.57 (1.18)	7.360.37)

[0242] All lenses showed a desirable combination of properties. Also, comparing Examples 61-63 to the lenses made in US822016, using a combination of hydroxyl-containing silicone components instead of one non-hydroxyl silicone component (mPDMS) and a hydroxyl-functional silicone-containing monomer (SiMAA), allowed for the incorporation of an anionic component (MAA), without adding thermal instability, water contents above about 50%, advancing contact angles less than 80 and Dk values of about 130 barrers or more.

Examples 64-68

[0243] Each reactive mixture was formed by mixing the reactive components listed in Table 32, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of a 55:45 (w/w) blend of Z and PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C. The lenses of Examples 64 and 66-68 were cured from the top for 20 minutes using 420 nm and 435 nm LED lights, respectively, having intensity of 4 mW/cm². Example 65 was cured using TLO3 bulbs at 5 mW/cm², for 15 minutes. The light source was about six inches above the trays.

[0244] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 33.

TABLE 32

Component	Ex 64	Ex 65	Ex 66	Ex 67	Ex 68
OH-mPDMS (n=15)	31	31	31	31	31
OH-mPDMS (n=4)	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.81	0.81	0.81	0.81	0.81
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.87	1.87	1.87	1.87	1.87
NVP	5.66	5.35	6.1	6.1	6.1
DMA	6.54	5.35	6.1	6.1	6.1
HEMA	11.33	11.33	11.33	11.33	11.33
Blue HEMA	0.02	0.02	0.02	0.02	0.02
PVMA 628 kDa	13.5	15	12	10.5	8.5
PVP K90	0	0	1.5	3	5
mPEG 950	3	3	3	3	3
MAA	1	1	1	1	1
TEGDMA	0.75	0.75	0.75	0.75	0.75
TAC	0.2	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75	1.75
CGI 819	0.25	0.25	0.25	0.25	0.25
Diluent	30	30	30	30	30
D3O	100	100	100	100	100

TABLE 33

Ex	% Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
64	49 (0)	17 (0)	33 (6), 11 (11)	99 (12)	187 (53)	133	245 ± 12	-3.04 (1.30)	NT
65	49(0)	14 (0)	33 (12,), 12 (16)	111 (7)	167 (46)	142	167 ± 8	-0.44 (2.40)	NT
66	49(0)	12 (1)	24 (9), 16 (5)	88 (13)	206 (52)	117	224 ± 14	6.13 (0.54)	2.61 (1.80)
67	49(0)	13 (1)	52 (7), 22 (8)	109 (8)	179 (29)	125	291 ± 4	6.96 (0.28)	-0.09 (3.39)
68	47(0)	15 (1)	13 (19), 10 (11)	115 (10)	165 (60)	135	200 ± 12	6.92 (0.23)	1.940.46)

[0245] Lenses prepared using mixtures of NVP and DMA together with mixtures of OH-mPDMS and mixtures of PVMA and PVP as the internal wetting agents showed an excellent balance of biometric properties including moderate lysozyme, PQ1, and lipid uptake.

Examples 69-72

[0246] Each reactive mixture was formed by mixing the reactive components listed in Table 34, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of a 55:45 (w/w) blend of Z and PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 20 minutes using 435 nm LED lights having intensity of 4 mW/cm². The light source was about six inches above the trays.

[0247] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 35.

TABLE 34

Component	Ex 69	Ex 70	Ex 71	Ex 72	Ex 73
OH-mPDMS (n=15)	31	31	31	31	31
OH-mPDMS (n=4)	25	25	25	25	25
Weight ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.80	0.80	0.80	0.80	0.80
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	1.87	1.87	1.87	1.87	1.87
NVP	5.35	5.32	5.35	5.35	5.35
DMA	5.35	5.32	5.35	5.35	5.35
HEMA	11.33	11.30	11.33	11.33	11.33
Blue HEMA	0.02	0.02	0.02	0.02	0.02
PVMA 628 kDa	10	10	7.5	5	2.5
PVP K90	5	5	7.5	10	12.5
mPEG 950	3	3	3	3	3
MAA	1	1	1	1	1
EGDMA	0.75	0.75	0.75	0.75	0.75
TAC	0.2	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75	1.75
CGI 819	0.25	0	0.25	0.25	0.25
CGI 1870	0	0.34	0	0	0
Diluent	30	30	30	30	30
D3O	100	100	100	100	100

TABLE 35

Ex	% Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)	PQ1 Uptake (%)	Lipid Uptake (µg/lens)
				M (psi)	%ETB
69	49 (0)	15 (1)	37 (9), 23 (12)	115 (8)	180 (40)	124	166 ± 9	6.96 (0.14)	2.58 (1.84)
70	47 (0)	16 (2)	43 (7), 18 (15)	118 (11)	198 (40)	134	133 ± 5	7.02 (0.42)	2.89 (2.45)
71	49(0)	13 (1)	16 (21), 16 (18)	102 (11)	192 (33)	130	185 ± 15	8.22 (0.5)	6.08 (1.37)
72	47 (0)	16 (2)	18 (11), 4 (6)	127 (14)	213 (38)	139	134 ± 19	8.29 (0.68)	2.53 (1.69)
73	46.4 (0.3)	15 (2)	15 (18), 10 (15)	134 (18)	44 (20)	136	97 ± 9	NT	2.49 (1.91)

[0248] This series of Examples shows that lenses having very low lipid uptake values (less than about 5 ug/lens, and less than 3 ug/lens) may be prepared using a combination of acyclic polyamide and PVP. All lenses had a desirable balance of both biometric, physical and mechanical properties.

Examples 74-77

[0249] Each reactive mixture was formed by mixing the reactive components listed in Table 36, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of a 55:45 (w/w) blend of Z and PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 62-65°C, and the lenses were cured from the top for 20 minutes using 435 nm LED lights having intensity of 4 mW/cm². The light source was about six inches above the trays.

[0250] The lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with 25% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted about 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 37.

TABLE 36

Component	Ex 74	Ex 75	Ex 76	Ex 77
OH-mPDMS (n=15)	31	31	26	21
mPDMS 1000 (n=10)	0	0	10	10
OH-mPDMS (n=4)	25	25	20	25
Weight ratio OH-mPDMS (n=4) to OH-mPDMS (n=15)	0.81	0.81	0.77	1.19
Molar ratio of OH-mPDMS (n=4) to OH-mPDMS (n=15)	2.37	3.33
NVP	5.35	5.32	5.35	5.35
DMA	5.35	5.32	5.35	5.35
HEMA	11.33	11.30	11.33	11.33
Blue HEMA	0.02	0.02	0.02	0.02
PVMA 628 kDa	5	5	5	5
PVP K90	10	10	10	10
mPEG 950	3	3	3	3
MAA	1	1	1	1
EGDMA	0.75	0.75	0.75	0.75
TAC	0.2	0.2	0.2	0.2
Norbloc	1.75	1.75	1.75	1.75
CGI 819	0.25	0	0.25	0.25
CGI 1870	0	0.34	0	0
Diluent	30	30	30	30
D3O	100	100	100	100

TABLE 37

Ex	% Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lysozyme (µg/Lens)
				M (psi)	%ETB
74	45.7 (0.5)	17 (1)	13 (16), 4 (9)	126 (10)	82 (18)	129	115 ± 12
75	44.8 (0.4)	19 (1)	24 (10), 8 (9)	126 (15)	73 (12)	136	101 ± 21
76	45.6 (0.5)	18 (1)	96 (6), 17 (10)	133 (12)	65 (16)	138	174 ± 54
77	46.8 (0.4)	17 (1)	91 (16), 18 (16)	136 (8)	62 (20)	135	56 ± 2

[0251] Lenses prepared using mixtures of NVP and DMA together with mixtures of OH-mPDMS and mixtures of PVMA and PVP as the internal wetting agents showed an excellent balance of biometric properties including moderate lysozyme, PQ1, and lipid uptake, except when mPDMS was also included in the reactive mixture.

Examples 78-82

[0252] Lenses were made from the formulation listed in Example 82 of Table 38, below, using the procedures described in Examples 74-77. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses of Example 82 were measured and listed in Table 39.

TABLE 38

Component	Ex 78	Ex 79	Ex 80	Ex 81	Ex 82
OH-mPDMS (n=4)	42	42	42	42	42
SiMAA	21	21	21	21	21
Weight ratio SiMMA to OH-mPDMS (n=4)	0.5	0.5	0.5	0.5	0.5
DMA	26.14	25.14	24.14	23.14	23.39
PVP K90	7	8	9	10	10
TEGDMA	1.5	1.5	1.5	1.5	1.5
Blue HEMA	0.02	0.02	0.02	0.02	0.02
Norbloc	2	2	2	2	1.75
CGI 1870	0.34	0.34	0.34	0.34	0.34
Diluent	23	23	23	23	23
D3O	100	100	100	100	100

TABLE 39

Ex	Wt % Water	% Haze	DCA (adv, rec)	Mechanicals		Dk	Lipid (µg/Lens)
				M (psi)	%ETB
82	39(0)	9(1)	21(11), 21(12)	119(9)	277(49)	98	20.49 (3)

Examples 83-93

[0253] Each reactive mixture was formed by mixing the reactive components listed in Table 40, filtering through a 3 µm filter using a heated or unheated stainless steel or glass syringe, and then degassed by applying vacuum at ambient temperature for about 10 minutes. In a glove box with a nitrogen gas atmosphere and less than 0.1 percent oxygen gas, about 75-100 µL of the reactive mixture were dosed using an Eppendorf pipet at room temperature into the FC made of Zeonor. The BC made of a 55:45 (w/w) blend of Z and PP was then placed onto the FC. The molds were equilibrated for a minimum of twelve hours in the glove box prior to dosing. The plate was transferred into an adjacent glove box maintained at 60-65°C, and the lenses were cured from the top. Examples 83 and 84 were cured for 20 minutes using 435 nm LED lights having intensity of 4 mW/cm². Examples 85-90 were cured for 15 minutes using TLO3 lights having intensity of 5 mW/cm². The light source was about six inches above the trays.

[0254] On the other hand, examples 91-93 were cured using 435 nm LED lights from the top and bottom first using an intensity of 1 mW/cm² for 2 minutes and second using an intensity of 2.5 mW/cm² for 6 minutes. Examples 91-93 also used a 90:10 (w/w) Z:TT blend FC and a 90: 10 (w/w) Z:PP blend BC. The reaction temperature was 65°C, and the oxygen gas concentration was 0.1 percent in the glove box.

[0255] For Examples 83-90, the lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 40% IPA for about one or two hours, followed by washing two times with 40% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted at least 30 minutes. For Examples 91-93, the lenses were manually de-molded with most lenses adhering to the FC and released by suspending the 64 lenses in about one liter of 70% IPA for about one or two hours, followed by washing two times with 70% IPA, two times with DI, and finally two times with borate buffered packaging solution. Each washing step lasted at least 30 minutes. A person of ordinary skill recognizes that the exact lens release process can be varied depending on the lens formulation and mold materials, regarding the concentrations of the aqueous isopropanol solutions, the number of washings with each solvent, and the duration of each step. The purpose of the lens release process is to release all of the lenses without defects and transition from diluent swollen networks to the packaging solution swollen hydrogels. The lenses were transferred into vials and subsequently sterilized by autoclaving at 122°C for 30 minutes. The physical and mechanical properties of the sterile lenses were measured and listed in Table 41.

Table 40

Component	Ex 83	Ex 84	Ex 85	Ex 86	Ex 87	Ex 88	Ex 89	Ex 90	Ex 91	Ex 92	Ex 93
OH-mPDMS n=4	30	30	25	20	15	10	10	10	25	25	25
OH-mPDMS n=15	30	30	35	40	45	50	50	50	28	28	28
Tegomer 2250	10	10	10	10	10	10	5	7.5	5	5	5
EGDMA	0	0	0	0	0	0	0	0	0.25	0.25	0.25
DMA	7	10	10	10	10	10	12.5	11.25	24	20	20
HEMA	11	11	10.98	10.98	10.98	10.98	13.48	12.23	7.89	7.89	7.89
pVMA (Mw=507KDa)	10	7	7	7	7	7	7	7	0	0	0
PVP K90	0	0	0	0	0	0	0	0	0	9	7
pVMA (Mw=570KDa)	0	0	0	0	0	0	0	0	0	0	2
PDMA (Mw=740KDa)	0	0	0	0	0	0	0	0	5	0	0
UV Absorbers	1.75	1.75	1.75	1.75	1.75	1.75	1.75	1.75	4.5	4.5	4.5
CG1 819	0.25	0.25	0.25	0.25	0.25	0.25	0.25	0.25	0	0	0
Ingacure 1870	0	0	0	0	0	0	0	0	0.34	0.34	0.34
Blue HEMA	0	0	0.02	0.02	0.02	0.02	0.02	0.02	0.02	0.02	0.02
Diluent	23	23	23	23	23	23	23	23	23	23	23
D3O	100	100	100	100	100	100	100	100	100	100	100

Table 41

Ex #	% Water	% Haze	Sessile Drop (°)	DCA Kruss (Adv °)	Dk	Lipids (µg/lens)	Mechanicals
							Modulus (psi)	Elong. (%)
Ex 83	25.5	10 (1)	NT	55 (17)	110	NT	220 (24)	158 (39)
Ex 84	25.2	6 (0)	NT	94 (10)	78	NT	180 (10)	166 (43)
Ex 85	24.5	5	NT	69	96	NT	218	124
Ex 86	23.8	4	NT	92	145	NT	182	150
Ex 87	23.1	3	NT	61	125	NT	219	135
Ex 88	24.2	5	NT	70	135	NT	178	158
Ex 89	32	18	NT	46	225	NT	118	247
Ex 90	27.7	12	NT	53	170	NT	145	126
Ex 91	38	6 (1)	39 (3)	38 (5)	128	1.74 (0.30)	109 (4)	163 (83)
Ex 92	37	4 (0)	44 (2)	40 (10)	134	2.62 (0.41)	118 (8)	252 (48)
Ex 93	37	5 (0)	43 (3)	19 (21)	124	2.17 (0.25)	143 (10)	216 (75)

NT = Not tested.

Claims

1. A silicone hydrogel formed from a reactive monomer mixture comprising:

a. between 1 and 15 wt% at least one polyamide, wherein "polyamide" refers to polymers and copolymers comprising repeating units containing amide groups;

b. at least one first mono-functional, hydroxyl substituted, linear poly(disubstituted siloxane) having 4 to 8 siloxane repeating units;

c. at least one second hydroxyl substituted, linear poly(disubstituted siloxane) selected from the group consisting of mono-functional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200 or 10-100 siloxane repeating units and multifunctional hydroxyl substituted poly(disubstituted siloxane)s having 10 to 200, or 10 to 100 siloxane repeating units, and mixtures thereof;

d. 5 to 35 wt% of at least one hydrophilic monomer;

wherein the first hydroxyl substituted, linear poly(disubstituted siloxane) and the second mono-functional hydroxyl substituted, linear poly(disubstituted siloxane) are present in concentrations to provide a ratio of wt% of all first hydroxyl substituted, linear poly(disubstituted siloxane) to wt% of all second hydroxyl substituted, linear poly(disubstituted siloxane)s of 0.4-1.3, or 0.4-1.0;

wherein "functional" means a group which can undergo free radical polymerization;

wherein concentrations of components are given in weight % of all components in the reaction mixture, excluding diluent.

2. The silicone hydrogel of claim 1, wherein the second hydroxyl substituted linear poly(disubstituted siloxane) is selected from mono-functional hydroxyl substituted linear poly(disubstituted siloxane)s having 10 to 200 or 10-100 siloxane repeating units.

3. The silicone hydrogel of claim 1 or 2, wherein:

(a) the first monofunctional hydroxyl substituted, poly(disubstituted siloxane) comprises compounds of Formula VII-1

wherein

Z is selected from O, N, S or NCH₂CH₂O, wherein when Z is O or S then R² is not present;

R¹ is independently H or methyl;

R² is H or is a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amide, ether, and combinations thereof;

R³ and R⁴ are independently a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amide, ether, and combinations thereof; R³ and R⁴ may be independently selected from methyl, ethyl or phenyl, or may be methyl;

n is 4-8; and

R⁵ is selected from straight or branched C₁ to C₈ alkyl groups, which may be optionally substituted with one or more hydroxyl, amide, ether, and combinations thereof; and/or

(b) the second hydroxyl substituted, poly(disubstituted siloxane) comprises a compound of Formula VII-2:

wherein Z is selected from O, N, S or NCH₂CH₂O, when Z is O or S R² is not present;

R¹ is independently H or methyl;

R² is H or is a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amide, ether, and combinations thereof;

R³ and R⁴ are independently a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, and which may be optionally substituted with amide, ether, and combinations thereof; R³ and R⁴ may be independently selected from methyl, ethyl or phenyl, or may be methyl;

n is the number of siloxane units and is from 10 to 200, or 10-100, or 10-50, or 10-20, or 12-18; and

R⁵ is selected from straight or branched C₁ to C₈ alkyl groups, which may be optionally substituted with one or more hydroxyl, amide, ether, and combinations thereof; and/or

(c) the second hydroxyl-substituted poly(disubstituted siloxane) further comprises a di-functional hydroxyl-substituted poly(disubstituted siloxane) of Formula XI

wherein

wherein R¹ is independently a hydrogen atom or methyl group;

R² and R³ are independently a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amido, ether, amino, carboxyl, carbonyl groups and combinations thereof; or are selected from methyl, ethyl and -(CH₂CH₂O)_xOCH₃ where x is from 1 to 20; and

n is from 1 to 200.

4. The silicone hydrogel of any of the foregoing claims, wherein the first mono-functional hydroxyl-substituted poly(disubstituted siloxane) and the second hydroxyl-substituted poly(disubstituted siloxane) are present in the reactive monomer mixture in a total concentration between 40 and 70 wt%, or 45 to 70 wt% based on all components in the reaction mixture, excluding diluent.

5. The silicone hydrogel of any of the foregoing claims, wherein:

(a) the polyamide comprises a cyclic polyamide, an acyclic polyamide, or a mixture of a cyclic polyamide and an acyclic polyamide; or

(b) the polyamide is an acyclic polyamide.

6. The silicone hydrogel of any of the foregoing claims, wherein the first or second monofunctional hydroxyl substituted, poly(disubstituted siloxane) comprises a monofunctional hydroxyl substituted, poly(dimethylsiloxane) of any of Formulae VIIa-IXb:

wherein R¹ is methyl or H; n is between 4 and 30, 4-8 or 10-20; wherein Z is selected from O, N, S or NCH₂CH₂O, when Z is O or S R² is not present;

R² is independently selected from the group consisting of a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, and which may be optionally substituted with amide, ether, and combinations thereof;

n¹ and n² are independently between 4 to 100; 4 to 50; or 4 to 25;

n³ is 1-50, 1-20, or 1-10;

R⁵ is selected from straight or branched C₁ to C₈ alkyl groups, which may be optionally substituted with one or more hydroxyl, amide, ether, polyhydroxyl groups selected from straight or branched C₁ to C₈ groups having a formula of C_fH_g(OH)_h wherein f=1-8 and g+h=2f+1 and cyclic C₁ to C₈ groups having a formula of C_fH_g(OH)_h wherein f=1-8 and g+h=2f-1, and combinations thereof; or R⁵ may be selected from methyl, butyl or hydroxyl substituted C₂-C₅ alkyl, including hydroxyl ethyl, hydroxyl propyl, hydroxyl butyl, hydroxyl pentyl and 2,3-dihydroxypropyl;

a is 4-8 for the first hydroxyl-containing silicone component and between 4-100 for the second hydroxyl-containing silicone component.

7. The silicone hydrogel of any of the foregoing claims wherein the second hydroxyl substituted, poly(disubstituted siloxane)s comprises mono-(2-hydroxy-3-methacryloxypropyl)-propyl ether terminated mono-n-butyl terminated polydimethylsiloxane (OH-mPDMS) having fifteen siloxane repeating units.

8. The silicone hydrogel of claim 1 or 2, wherein:

(a) the hydrophilic monomer comprises a reactive group selected from the group consisting of (meth)acrylates, (meth)acrylamides, styrenes, N-vinyllactams, N-vinylamides, O-vinylcarbamates, O-vinylcarbonates, vinyl ethers, vinyl esters, vinyls, allyls and combinations thereof; and/or

(b) the hydrophilic monomer is present in the reactive monomer mixture in an amount between 15 to 35 wt%.

9. The silicone hydrogel of any of the foregoing claims further comprising at least one charged component.

10. The silicone hydrogel of claim 1 or 2, wherein the second hydroxyl substituted, poly(disubstituted siloxane)s comprises at least one compound of Formula XII:

wherein R¹ is independently a hydrogen atom or methyl group; Z is selected from O, N, S or NCH₂CH₂O, wherein for Z = O and S, R² is not required;

R² is selected from the group consisting of H or a linear, branched, or cyclic alkyl group containing one to eight carbon atoms, any of which may be further substituted with at least one hydroxy group, amido, ether, amino, carboxyl, carbonyl groups and combinations; a linear or branched alkyleneoxy group, specifically ethyleneoxy groups, [CH₂CH₂O]_p wherein p is between 1 and 200, or 1 and 100, or 1 and 50, or 1 and 25, or 1 and 20, optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a C₁-C₆ linear or branched fluoroalkyl groups optionally substituted with one or more hydroxyl, amino, amido, ether, carbonyl, carboxyl, and combinations thereof; a substituted or un-substituted aryl groups, specifically phenyl groups, wherein the substituents are selected from halogen, hydroxyl, alkoxy, alkylcarbonyl, carboxy, and linear or branched or cyclic alkyl groups which may be further substituted with halogen, hydroxyl, alkoxy, alkylcarbonyl, and carboxyl groups, and combinations thereof;

n¹ and n² are independently selected from 4 to 100; 4 to 50; or 4 to 25; and

n³ is 1-50, 1-20, and 1-10.

11. The silicone hydrogel of claim 1 or 2, wherein the hydrophilic monomer is selected from hydrophilic amide monomers; optionally

(a) wherein the reactive monomer mixture comprises less than 30 wt%, or less than 25 wt% or less than 20 wt% hydrophilic amide monomers based on all components in the reaction mixture, excluding diluent; and/or

(b) wherein the hydrophilic amide monomers are included in the reactive mixture in amounts between 5 and 28 wt%, or 5 and 25 wt%, or between 8 and 20 wt% based on all components in the reaction mixture, excluding diluent.

12. The silicone hydrogel of claim 1 or 2, wherein:

(a) the hydrophilic monomer is selected from the group consisting of N,N-dimethylacrylamide, acrylamide, ethylene glycol vinyl ether (EGVE), di(ethylene glycol) vinyl ether (DEGVE), N-vinyl pyrrolidone (NVP), 1-methyl-3-methylene-2-pyrrolidone, 1-methyl-5-methylene-2-pyrrolidone, 5-methyl-3-methylene-2-pyrrolidone; 1-ethyl-5-methylene-2-pyrrolidone, N-methyl-3-methylene-2-pyrrolidone, 5-ethyl-3-methylene-2-pyrrolidone, 1-n-propyl-3-methylene-2-pyrrolidone, 1-n-propyl-5-methylene-2-pyrrolidone, 1-isopropyl-3-methylene-2-pyrrolidone, 1-isopropyl-5-methylene-2-pyrrolidone, N-vinyl-N-methyl acetamide (VMA), N-vinyl-N-ethyl acetamide, N-vinyl-N-ethyl formamide, N-vinyl formamide, N-vinyl acetamide, N-vinyl isopropylamide, allyl alcohol, N-vinyl caprolactam, N-2-hydroxyethyl vinyl carbamate, N-carboxy-β-alanine N-vinyl ester; N-carboxyvinyl-β-alanine (VINAL), N-carboxyvinyl-α-alanine and mixtures thereof; or

(b) the hydrophilic monomer is selected from N,N-dimethylacrylamide, N-vinylpyrrolidone, N-vinyl-N-methyl acetamide, N-vinyl acetamide, and 1-methyl-5-methylene-2-pyrrolidone; or

(c) the hydrophilic monomer comprises N-vinylpyrrolidone, N,N-dimethylacrylamide, or mixtures thereof.

13. The silicone hydrogel of any of the foregoing claims, wherein the silicone hydrogel has an oxygen permeability (Dk) of at least 80 barrers, or 80 to 200 barrers, 90 to 180 barrers, 100 to 160 barrers when oxygen permeability is measured using the "Oxygen permeability" testing method given in the description.

14. The silicone hydrogel of claim 9, wherein the charged monomer comprises at least one ionic moiety selected from the group consisting of anions, cations, zwitterions, betaines, and mixtures thereof.

15. The silicone hydrogel of claim 14, wherein the charged monomer comprises at least one carboxylic acid group; optionally

(a) wherein the charged monomer comprises at least one carboxylic acid monomer selected from the group consisting of (meth)acrylic acid, furmaric acid, maelic acid, itaconic acid, crotonic acid, cinnamic acid, vinylbenzoic acid, monoesters of furmaric acid, maelic acid, and itaconic acid, and mixtures thereof; or

(b) wherein the charged monomer comprises mixture of anionic and cationic monomer; or

(c) wherein the charged monomer is selected from the group consisting of (meth)acrylic acid, N-[(ethenyloxy)carbonyl]-β-alanine (VINAL), 3-acrylamidopropanoic acid (ACA1), 5-acrylamidopropanoic acid (ACA2), 3-acrylamido-3-methylbutanoic acid (AMBA), 2-(methacryloyloxy)ethyl trimethylammonium chloride (Q Salt), 2-acrylamido-2-methylpropane sulfonic acid (AMPS), 1-propanaminium, N-(2-carboxyethyl)-N,N-dimethyl-3-[(1-oxo-2-propen-1-yl)amino]-, inner salt (CBT, carboxybetaine), 1-propanaminium, N,N-dimethyl-N-[3-[(1-oxo-2-propen-1-yl)amino]propyl]-3-sulfo-, inner salt (SBT, sulfobetaine,), 3,5-Dioxa-8-aza-4-phosphaundec-10-en-1-aminium, 4-hydroxy-N,N,N-trimethyl-9-oxo-, inner salt, 4-oxide (9CI) phosphobetaine(PBT), 2-methacryloyloxyethyl phosphorylcholine, 3-(dimethyl(4-vinylbenzyl)ammonio)propane-1-sulfonate (DMVBAPS), 3-((3-acrylamidopropyl)dimethylammonio)propane-1-sulfonate (AMPDAPS), 3-((3-methacrylamidopropyl)dimethylammonio)propane-1-sulfonate (MAMPDAPS), 3-((3-(acryloyloxy)propyl)dimethylammonio)propane-1-sulfonate (APDAPS), methacryloyloxy)propyl)dimethylammonio)propane-1-sulfonate (MAPDAPS), and mixtures thereof; or

(d) wherein the charged monomer is selected from the group consisting of (meth)acrylic acid, N-[(ethenyloxy)carbonyl]-β-alanine (VINAL), 3-acrylamidopropanoic acid (ACA1), 5-acrylamidopropanoic acid (ACA2), and mixtures thereof.

16. The silicone hydrogel of any of claims 9 or 15, wherein the at least one charged monomer comprises up to 5 wt%, or between 0.5 to 5 wt.%, or between 0.5 to 3 wt.%, or between 0.5 to 2 wt.%, or between 1 to 5 wt.%, or between 1 to 3 wt, based on the total weight of the reactive monomer mixture.

17. The silicone hydrogel of any of the foregoing claims, comprising a charged monomer selected from acrylic acid, methacrylic acid, and mixtures thereof.

18. The silicone hydrogel of claim 1 or 2 wherein:

(a) the polyamide comprises an acyclic polyamide selected from the group consisting of PVMA, PNVA, and poly[N-vinyl N-alkyl acetamide]s wherein the N-alkyl group is selected from the group consisting of linear and branched alkyl groups containing between one and five carbon atoms, and copolymers and mixtures thereof; and/or

(b) wherein the polyamide comprises poly(N-vinyl-N-methyl acetamide), poly(N-vinyl acetamide), polydimethylacrylamide, or a mixture of two or more thereof; and/or

(c) wherein the polyamide comprises a copolymer; optionally

wherein the copolymer comprises repeating units selected from the group consisting of N-vinyl amides, acrylamides, hydroxyalkyl(meth)acrylates, alkyl(meth)acrylates, N-vinylpyrrolidone, N,N-dimethylacrylamide, 2-hydroxyethylmethacrylate, vinyl acetate, acrylonitrile, hydroxypropyl methacrylate, 2-hydroxyethyl acrylate, methyl methacrylate, butyl methacrylate, methacryloxypropoyl tristrimethylsiloxysilane, siloxane substituted acrylates or methacrylates, and mixtures thereof.

19. The silicone hydrogel of claim 1 or 2, wherein the polyamide comprises repeating units of Formula I or Formula II

wherein X is a direct bond, -(CO)-, or -(CO)-NHR^e-, wherein R^e is a C₁ to C₃ alkyl group;

R^a is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups;

R^b is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups, amino groups having up to two carbon atoms, amide groups having up to four carbon atoms, and alkoxy groups having up to two carbon atoms;

R^c is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups, or methyl, ethoxy, hydroxyethyl, and hydroxymethyl;

R^d is selected from H, straight or branched, substituted or unsubstituted C₁ to C₄ alkyl groups, or methyl, ethoxy, hydroxyethyl, and hydroxymethyl;

wherein the number of carbon atoms in R^a and R^b taken together is 8 or less, and wherein the number of carbon atoms in R^c and R^d taken together is 8 or less; optionally

(a) wherein the polyamide is a copolymer comprising at least 80 mole % of the repeating units from Formula I or Formula II; and/or

(b) wherein R^b is selected from straight or branch unsubstituted C₁ to C₄ alkyl groups.

20. The silicone hydrogel of claim 1 or 2, wherein the polyamide comprises between 3 and 15 wt% of the reactive monomer mixture, based upon all reactive components; or
wherein the polyamide comprises between 3 and 12 wt% of the reactive mixture based upon all reactive components.

21. The silicone hydrogel of any of the foregoing claims, wherein the polyamide comprises a cyclic polyamide; optionally
wherein the cyclic polyamide comprises polyvinylypyrrolidone (PVP) in an amount up to 15 wt.%, or an amount in the range of 2 to 15 wt. %, or an amount in the range of 5 to 15 wt.%.

22. The silicone hydrogel of claim 1 or 2, wherein the reactive monomer mixture further comprises at least one additional constituent selected from the group consisting of a diluent, a UV absorbing compound, a medicinal agent, an antimicrobial compound, a pharmaceutical compound, a nutraceutical compound, a photochromic compound, a reactive tint, a pigment, a copolymerizable dye, a nonpolymerizable dye, a release agent, a copolymer, and combinations thereof.

23. The silicone hydrogel of any of the foregoing claims further comprising at least one hydroxylalkyl (meth)acrylate monomer; optionally:

(a) wherein said hydroxyalkyl (meth)acrylate monomer is selected from the group consisting of 2-hydroxyethyl (meth)acrylate, 3-hydroxypropyl (meth)acrylate, 2-hydroxypropyl (meth)acrylate, 2,3-dihydroxypropyl (meth)acrylate, 2-hydroxybutyl (meth)acrylate, 3-hydroxybutyl (meth)acrylate, 1-hydroxypropyl-2-(meth)acrylate, 2-hydroxy-2-methyl-propyl (meth)acrylate, 3-hydroxy-2,2-dimethyl-propyl (meth)acrylate, 4-hydroxybutyl (meth)acrylate, glycerol (meth)acrylate, polyethylene glycol monomethacrylate, and mixtures thereof; or

(b) wherein said hydroxyalkyl (meth)acrylate monomer is selected from the group consisting of 2-hydroxyethyl methacrylate, glycerol methacrylate, 2-hydroxypropyl methacrylate, hydroxybutyl methacrylate, 3-hydroxy-2,2-dimethyl-propyl methacrylate, and mixtures thereof; or

(c) wherein said hydroxyalkyl (meth)acrylate monomer is selected from the group consisting of 2-hydroxyethyl methacrylate, 3-hydroxy-2,2-dimethyl-propyl methacrylate, hydroxybutyl methacrylate or glycerol methacrylate.

24. The silicone hydrogel of any of the foregoing claims, wherein the reactive monomer mixture further comprises at least one additional silicone-containing compounds without a hydroxyl group.

25. The silicone hydrogel of claim 1, wherein the second hydroxyl substituted poly(disubstituted siloxane) is selected from the group consisting of a monofunctional hydroxyl substituted, linear poly(disubstituted siloxane) having 10 to 20 siloxane repeating units and a multifunctional hydroxyl substituted, linear poly(disubstituted siloxane) having 10 to 200, or 10 to 100 siloxane repeating units; and
wherein the ratio of the first hydroxyl substituted linear poly(disubstituted siloxane) to the second hydroxyl substituted, linear poly(disubstituted siloxane) is in a range of 0.4 to 1.2, or 0.4 to 1.0.

26. The silicone hydrogel of any of the foregoing claims, wherein the polyamide has a weight average molecular weight of at least 100,000 Daltons; or greater than 150,000 Daltons; or between 150,000 to 2,000,000 Daltons, or between 300,000 to 1,800,000 Daltons when the molecular weight is determined by Size Exclusion Chromatography with Multi-Angle Light Scattering.

27. The silicone hydrogel of any of the foregoing claims, wherein the polyamide is added to the reaction mixture such that the hydrogel polymerizes around the polyamide, forming a semi-interpenetrating network.

28. A contact lens comprising the silicone hydrogel of any of the foregoing claims.

29. The contact lens of claim 28, wherein the Dk is greater than 80 barrers, wherein the lysozyme uptake is greater than 50 µg/lens, wherein the lipid uptake is less than 10 µg/lens; wherein the PQ1 uptake is less than 15%; and wherein the contact angle is less than 50° when measured using the "oxygen permeability", "lipid uptake", "PQ1 uptake", "Dynamic contact angle", and either of the "lysozyme uptake" testing methods given in the description.

Ansprüche

1. Silicon-Hydrogel, gebildet aus einem reaktiven Monomergemisch umfassend:

a. zwischen 1 und 15 Gew.-% an wenigstens einem Polyamid, wobei "Polyamid" Polymere und Copolymere bezeichnet, die Wiederholungseinheiten, die Amidgruppen enthalten, umfassen;

b. wenigstens ein erstes monofunktionelles hydroxysubstituiertes lineares Poly(disubstituiertes Siloxan) mit 4 bis 8 Siloxan-Wiederholungseinheiten;

c. wenigstens ein zweites hydroxysubstituiertes lineares Poly(disubstituiertes Siloxan) ausgewählt aus der Gruppe bestehend aus monofunktionellen hydroxysubstituierten Poly(disubstituiertes Siloxan)en mit 10 bis 200 oder 10-100 Siloxan-Wiederholungseinheiten und multifunktionellen hydroxysubstituierten Poly(disubstituiertes Siloxan)en mit 10 bis 200 oder 10 bis 100 Siloxan-Wiederholungseinheiten und Gemischen davon;

d. 5 bis 35 Gew.-% an wenigstens einem hydrophilen Monomer;

wobei das erste hydroxysubstituierte lineare Poly(disubstituiertes Siloxan) und das zweite monofunktionelle hydroxysubstituierte lineare Poly(disubstituiertes Siloxan) in Konzentrationen vorhanden sind, die ein Verhältnis der Gew.-% aller ersten hydroxysubstituierten linearen Poly(disubstituiertes Siloxan)e zu den Gew.-% aller zweiten hydroxysubstituierten linearen Poly(disubstituiertes Siloxan)e von 0,4-1,3 oder 0,4-1,0 bereitstellen;

wobei "funktionell" eine Gruppe bedeutet, die radikalische Polymerisation erfahren kann;

wobei Konzentrationen von Komponenten in Gew.-% bezogen auf alle Komponenten in dem Reaktionsgemisch mit Ausnahme von Verdünnungsmittel angegeben werden.

2. Silicon-Hydrogel gemäß Anspruch 1, wobei das zweite hydroxysubstituierte lineare Poly(disubstituiertes Siloxan) ausgewählt ist aus monofunktionellen hydroxysubstituierten linearen Poly(disubstituiertes Siloxan)en mit 10 bis 200 oder 10-100 Siloxan-Wiederholungseinheiten.

3. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei:

(a) das erste monofunktionelle hydroxysubstituierte Poly(disubstituiertes Siloxan) Verbindungen der Formel VII-1 umfasst,

wobei

Z ausgewählt ist aus O, N, S und NCH₂CH₂O, wobei, wenn Z O oder S ist, R² nicht vorhanden ist;

R¹ unabhängig H oder Methyl ist;

R² H ist oder eine lineare, verzweigte oder cyclische Alkylgruppe ist, die ein bis acht Kohlenstoffatome enthält, von denen jedes ferner mit wenigstens einer/einem Hydroxygruppe, Amid, Ether und Kombinationen davon substituiert sein kann;

R³ und R⁴ unabhängig eine lineare, verzweigte oder cyclische Alkylgruppe sind, die ein bis acht Kohlenstoffatome enthält, von denen jedes ferner mit wenigstens einer/einem Hydroxygruppe, Amid, Ether und Kombinationen davon substituiert sein kann; wobei R³ und R⁴ unabhängig ausgewählt sein können aus Methyl, Ethyl und Phenyl oder Methyl sein können;

n 4-8 ist; und

R⁵ ausgewählt ist aus geraden oder verzweigten C₁- bis C₈-Alkylgruppen, die gegebenenfalls mit einem oder mehreren Hydroxy, Amid, Ether und Kombinationen davon substituiert sein können; und/oder

(b) das zweite hydroxysubstituierte Poly(disubstituiertes Siloxan) eine Verbindung der Formel VII-2 umfasst:

wobei Z ausgewählt ist aus O, N, S und NCH₂CH₂O, wobei, wenn Z O oder S ist, R² nicht vorhanden ist;

R¹ unabhängig H oder Methyl ist;

R² H ist oder eine lineare, verzweigte oder cyclische Alkylgruppe ist, die ein bis acht Kohlenstoffatome enthält, von denen jedes ferner mit wenigstens einer/einem Hydroxygruppe, Amid, Ether und Kombinationen davon substituiert sein kann;

R³ und R⁴ unabhängig eine lineare, verzweigte oder cyclische Alkylgruppe sind, die ein bis acht Kohlenstoffatome enthält, von denen jedes ferner mit wenigstens einer Hydroxygruppe substituiert sein kann und das gegebenenfalls mit Amid, Ether und Kombinationen davon substituiert sein kann; wobei R³ und R⁴ unabhängig ausgewählt sein können aus Methyl, Ethyl und Phenyl oder Methyl sein können;

n die Anzahl von Siloxaneinheiten ist und von 10 bis 200 oder 10-100 oder 10-50 oder 10-20 oder 12-18 beträgt; und R⁵ ausgewählt ist aus geraden oder verzweigten C₁- bis C₈-Alkylgruppen, die gegebenenfalls mit einem oder mehreren Hydroxy, Amid, Ether und Kombinationen davon substituiert sein können; und/oder

(c) das zweite hydroxysubstituierte Poly(disubstituiertes Siloxan) ferner ein difunktionelles hydroxysubstituiertes Poly(disubstituiertes Siloxan) der Formel XI umfasst,

wobei

wobei R¹ unabhängig ein Wasserstoffatom oder eine Methylgruppe ist;

R² und R³ unabhängig eine lineare, verzweigte oder cyclische Alkylgruppe sind, die ein bis acht Kohlenstoffatome enthält, von denen jedes ferner mit wenigstens einer/einem Hydroxygruppe, Amido, Ether, Amino, Carboxy, Carbonylgruppen und Kombinationen davon substituiert sein kann; oder ausgewählt sind aus Methyl, Ethyl und -(CH₂CH₂O)_XOCH₃, wobei x von 1 bis 20 beträgt; und

n von 1 bis 200 beträgt.

4. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das erste monofunktionelle hydroxysubstituierte Poly(disubstituiertes Siloxan) und das zweite hydroxysubstituierte Poly(disubstituiertes Siloxan) in dem reaktiven Monomergemisch in einer Gesamtkonzentration zwischen 40 und 70 Gew.-% oder 45 bis 70 Gew.-% bezogen auf alle Komponenten in dem Reaktionsgemisch mit Ausnahme von Verdünnungsmittel vorhanden sind.

5. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei:

(a) das Polyamid ein cyclisches Polyamid, ein acyclisches Polyamid oder ein Gemisch von einem cyclischen Polyamid und einem acyclischen Polyamid umfasst; oder

(b) das Polyamid ein acyclisches Polyamid ist.

6. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das erste oder zweite monofunktionelle hydroxysubstituierte Poly(disubstituiertes Siloxan) ein monofunktionelles hydroxysubstituiertes Poly(dimethylsiloxan) gemäß einer der Formeln VIIa-IXb umfasst:

wobei R¹ Methyl oder H ist; n zwischen 4 und 30, 4-8 oder 10-20 beträgt; wobei Z ausgewählt ist aus O, N, S und NCH₂CH₂O, wobei, wenn Z O oder S ist, R² nicht vorhanden ist;

R² unabhängig ausgewählt ist aus der Gruppe bestehend aus einer linearen, verzweigten oder cyclischen Alkylgruppe, die ein bis acht Kohlenstoffatome enthält, von denen jedes ferner mit wenigstens einer Hydroxygruppe substituiert sein kann und das gegebenenfalls mit Amid, Ether und Kombinationen davon substituiert sein kann;

n¹ und n² unabhängig zwischen 4 und 100; 4 bis 50; oder 4 bis 25 betragen;

n³ 1-50, 1-20 oder 1-10 beträgt;

R⁵ ausgewählt ist aus geraden oder verzweigten C₁- bis C₈-Alkylgruppen, die gegebenenfalls mit einem oder mehreren Hydroxy, Amid, Ether, Polyhydroxygruppen ausgewählt aus geraden oder verzweigten C₁- bis C₈-Gruppen mit einer Formel von C_fH_g(OH)_h, wobei f=1-8 und g+h=2f+1, und cyclischen C₁- bis C₈-Gruppen mit einer Formel von C_fH_g(OH)_h, wobei f=1-8 und g+h=2f-1, und Kombinationen davon substituiert sein können; oder R⁵ ausgewählt sein kann aus Methyl, Butyl und hydroxysubstituiertem C₂-C₅-Alkyl, einschließlich Hydroxylethyl, Hydroxylpropyl, Hydroxybutyl, Hydroxypentyl und 2,3-Dihydroxypropyl;

a für die erste hydroxyhaltige Siliconkomponente 4-8 beträgt und für die zweite hydroxyhaltige Siliconkomponente zwischen 4 und 100 beträgt.

7. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das zweite hydroxysubstituierte Poly(disubstituiertes Siloxan) Mono(2-hydroxy-3-methacryloxypropyl)propylether-terminiertes Mono-n-butyl-terminiertes Polydimethylsiloxan (OH-mPDMS) mit fünfzehn Siloxan-Wiederholungseinheiten umfasst.

8. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei:

(a) das hydrophile Monomer eine reaktive Gruppe ausgewählt aus der Gruppe bestehend aus (Meth)acrylaten, (Meth)acrylamiden, Styrolen, N-Vinyllactamen, N-Vinylamiden, O-Vinylcarbamaten, O-Vinylcarbonaten, Vinylethern, Vinylestern, Vinylen, Allylen und Kombinationen davon umfasst; und/oder

(b) das hydrophile Monomer in dem reaktiven Monomergemisch in einer Menge zwischen 15 und 35 Gew.-% vorhanden ist.

9. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, ferner umfassend wenigstens eine geladene Komponente.

10. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei die zweiten hydroxysubstituierten Poly(disubstituiertes Siloxan)e wenigstens eine Verbindung der Formel XII umfassen:

Wobei R¹ unabhängig ein Wasserstoffatom oder eine Methylgruppe ist; Z ausgewählt ist aus O, N, S und NCH₂CH₂O, wobei für Z = O und S R² nicht erforderlich ist;

R² ausgewählt ist aus der Gruppe bestehend aus H und einer linearen, verzweigten oder cyclischen Alkylgruppe, die ein bis acht Kohlenstoffatome enthält, von denen jedes ferner mit wenigstens einer Hydroxygruppe, Amido, Ether, Amino, Carboxy, Carbonylgruppen und Kombinationensubstituiert sein kann; einer linearen oder verzweigten Alkylenoxygruppe, insbesondere Ethylenoxygruppen [CH₂CH₂O]_p, wobei p zwischen 1 und 200 oder 1 und 100 oder 1 und 50 oder 1 und 25 oder 1 und 20 beträgt, gegebenenfalls substituiert mit einem oder mehreren Hydroxy, Amino, Amido, Ether, Carbonyl, Carboxy und Kombinationen davon; einer linearen oder verzweigten C₁-C₆-Fluoralkylgruppe, gegebenenfalls substituiert mit einem oder mehreren Hydroxy, Amino, Amido, Ether, Carbonyl, Carboxy und Kombinationen davon; einer substituierten oder unsubstituierten Arylgruppe, insbesondere Phenylgruppen, wobei die Substituenten ausgewählt sind aus Halogen, Hydroxy, Alkoxy, Alkylcarbonyl, Carboxy und linearen oder verzweigten oder cyclischen Alkylgruppen, die ferner mit Halogen, Hydroxy, Alkoxy, Alkylcarbonyl und Carboxygruppen und Kombinationen davon substituiert sein können;

n¹ und n² unabhängig ausgewählt sind aus 4 bis 100; 4 bis 50; oder 4 bis 25; und

n³ 1-50, 1-20 oder 1-10 ist.

11. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei das hydrophile Monomer ausgewählt ist aus hydrophilen Amidmonomeren; gegebenenfalls

(a) wobei das reaktive Monomergemisch weniger als 30 Gew.-% oder weniger als 25 Gew.-% oder weniger als 20 Gew.-% an hydrophilen Amidmonomeren bezogen auf alle Komponenten in dem Reaktionsgemisch mit der Ausnahme von Verdünnungsmittel umfasst; und/oder

(b) wobei die hydrophilen Amidmonomere in dem reaktiven Gemisch in Mengen zwischen 5 und 28 Gew.-% oder 5 und 25 Gew.-% oder zwischen 8 und 20 Gew.-% bezogen auf alle Komponenten in dem Reaktionsgemisch mit der Ausnahme von Verdünnungsmittel enthalten sind.

12. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei:

(a) das hydrophile Monomer ausgewählt ist aus der Gruppe bestehend aus N,N-Dimethylacrylamid, Acrylamid, Ethylenglycolvinylether (EGVE), Di(ethylenglycol)vinylether (DEGVE), N-Vinylpyrrolidon (NVP), 1-Methyl-3-methylen-2-pyrrolidon, 1-Methyl-5-methylen-2-pyrrolidon, 5-Methyl-3-methylen-2-pyrrolidon; 1-Ethyl-5-methylen-2-pyrrolidon, N-Methyl-3-methylen-2-pyrrolidon, 5-Ethyl-3-methylen-2-pyrrolidon, 1-n-Propyl-3-methylen-2-pyrrolidon, 1-n-Propyl-5-methylen-2-pyrrolidon, 1-Isopropyl-3-methylen-2-pyrrolidon, 1-Isopropyl-5-methylen-2-pyrrolidon, N-Vinyl-N-methylacetamid (VMA), N-Vinyl-N-ethylacetamid, N-Vinyl-N-ethylformamid, N-Vinylformamid, N-Vinylacetamid, N-Vinylisopropylamid, Allylalkohol, N-Vinylcaprolactam, N-2-Hydroxyethylvinylcarbamat, N-Carboxy-β-alanin-N-vinylester; N-Carboxyvinyl-β-alanin (VINAL), N-Carboxyvinyl-α-alanin und Gemischen davon; oder

(b) das hydrophile Monomer ausgewählt ist aus N,N-Dimethylacrylamid, N-Vinylpyrrolidon, N-Vinyl-N-methylacetamid, N-Vinylacetamid und 1-Methyl-5-methylen-2-pyrrolidon; oder

(c) das hydrophile Monomer N-Vinylpyrrolidon, N,N-Dimethylacrylamid oder Gemische davon umfasst.

13. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das Silicon-Hydrogel eine Sauerstoffdurchlässigkeit (Dk) von wenigstens 80 Barrer oder 80 bis 200 Barrer, 90 bis 180 Barrer, 100 bis 160 Barrer aufweist, wenn Sauerstoffdurchlässigkeit unter Verwendung des in der Beschreibung gegebenen "Sauerstoffdurchlässigkeit"-Prüfverfahrens gemessen wird.

14. Silicon-Hydrogel gemäß Anspruch 9, wobei das geladene Monomer wenigstens eine ionische Einheit ausgewählt aus der Gruppe bestehend aus Anionen, Kationen, Zwitterionen, Betainen und Gemischen davon umfasst.

15. Silicon-Hydrogel gemäß Anspruch 14, wobei das geladene Monomer wenigstens eine Carbonsäuregruppe umfasst; gegebenenfalls

(a) wobei das geladene Monomer wenigstens ein Carbonsäuremonomer ausgewählt aus der Gruppe bestehend aus (Meth)acrylsäure, Fumarsäure, Maleinsäure, Itaconsäure, Crotonsäure, Zimtsäure, Vinylbenzoesäure, Monoestern von Fumarsäure, Maleinsäure und Itaconsäure und Gemischen davon umfasst; oder

(b) wobei das geladene Monomer ein Gemisch von anionischem und kationischem Monomer umfasst; oder

(c) wobei das geladene Monomer ausgewählt ist aus der Gruppe bestehend aus (Meth)acrylsäure, N-[(Ethenyloxy)carbonyl]-P-alanin (VINAL), 3-Acrylamidopropansäure (ACA1), 5-Acrylamidopropansäure (ACA2), 3-Acrylamido-3-methylbutansäure (AMBA), 2-(Methacryloyloxy)ethyltrimethylammoniumchlorid (Q-Salz), 2-Acrylamido-2-methylpropansulfonsäure (AMPS), inneres 1-Propanaminium-N-(2-Carboxyethyl)-N,N-dimethyl-3-[(1-oxo-2-propen-1-yl)amino]-Salz (CBT, Carboxybetain), inneres 1-Propanaminium-N,N-dimethyl-N-[3-[(1-oxo-2-propen-1-yl)amino]propyl]-3-sulfo-Salz (SBT, Sulfobetain), inneres 3,5-Dioxa-8-aza-4-phosphaundec-10-en-1-aminium-4-hydroxy-N,N,N-trimethyl-9-oxo-Salz, 4-Oxid(9CI)phosphobetain (PBT), 2-Methacryloyloxyethylphosphorylcholin, 3-(Dimethyl(4-vinylbenzyl)ammonio)propan-1-sulfonat (DMVBAPS), 3-((3-Acrylamidopropyl)dimethylammonio)propan-1-sulfonat (AMPDAPS), 3-((3-Methacrylamidopropyl)dimethylammonio)propan-1-sulfonat (MAMPDAPS), 3-((3-(Acryloyloxy)propyl)dimethylammonio)propan-1-sulfonat (APDAPS), Methacryloyloxy)propyl)dimethylammonio)propan-1-sulfonat (MAPDAPS) und Gemischen davon; oder

(d) wobei das geladene Monomer ausgewählt ist aus der Gruppe bestehend aus (Meth)acrylsäure, N-[(Ethenyloxy)carbonyl]-P-alanin (VINAL), 3-Acrylamidopropansäure (ACA1), 5-Acrylamidopropansäure (ACA2) und Gemischen davon.

16. Silicon-Hydrogel gemäß einem der Ansprüche 9 und 15, wobei das wenigstens eine geladene Monomer bis zu 5 Gew.-% oder zwischen 0,5 und 5 Gew.-% oder zwischen 0,5 und 3 Gew.-% oder zwischen 0,5 und 2 Gew.-% oder zwischen 1 und 5 Gew.-% oder zwischen 1 und 3 Gew.-% bezogen auf das Gesamtgewicht des reaktiven Monomergemischs umfasst.

17. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, umfassend ein geladenes Monomer ausgewählt aus Acrylsäure, Methacrylsäure und Gemischen davon.

18. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei:

(a) das Polyamid ein acyclisches Polyamid ausgewählt aus der Gruppe bestehend aus PVMA, PNVA und Poly[N-vinyl-N-alkylacetamid]en umfasst, wobei die N-Alkylgruppe ausgewählt ist aus der Gruppe bestehend aus linearen und verzweigten Alkylgruppen, die zwischen einem und fünf Kohlenstoffatomen enthalten, und Copolymeren und Gemischen davon; und/oder

(b) wobei das Polyamid Poly(N-vinyl-N-methylacetamid), Poly(N-vinylacetamid), Polydimethylacrylamid oder ein Gemisch von zwei oder mehr davon umfasst; und/oder

(c) wobei das Polyamid ein Copolymer umfasst; gegebenenfalls

wobei das Copolymer Wiederholungseinheiten ausgewählt aus der Gruppe bestehend aus N-Vinylamiden, Acrylamiden, Hydroxyalkyl(meth)acrylaten, Alkyl(meth)acrylaten, N-Vinylpyrrolidon, N,N-Dimethylacrylamid, 2-Hydroxyethylmethacrylat, Vinylacetat, Acrylnitril, Hydroxypropylmethacrylat, 2-Hydroxyethylacrylat, Methylmethacrylat, Butylmethacrylat, Methacryloxypropoyltristrimethylsiloxysilan, siloxansubstituierten Acrylaten oder Methacrylaten und Gemischen davon umfasst.

19. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei das Polyamid Wiederholungseinheiten der Formel I oder Formel II umfasst,

wobei X eine direkte Bindung, - (CO) - oder - (CO) -NHR^e-ist, wobei R^e eine C₁- bis C₃-Alkylgruppe ist;

R^a ausgewählt ist aus H, geraden oder verzweigten, substituierten oder unsubstituierten C₁- bis C₄-Alkylgruppen;

R^b ausgewählt ist aus H, geraden oder verzweigten, substituierten oder unsubstituierten C₁- bis C₄-Alkylgruppen, Aminogruppen mit bis zu zwei Kohlenstoffatomen, Amidgruppen mit bis zu vier Kohlenstoffatomen und Alkoxygruppen mit bis zu zwei Kohlenstoffatomen;

R^c ausgewählt ist aus H, geraden oder verzweigten, substituierten oder unsubstituierten C₁- bis C₄-Alkylgruppen und Methyl, Ethoxy, Hydroxyethyl und Hydroxymethyl;

R^d ausgewählt ist aus H, geraden oder verzweigten, substituierten oder unsubstituierten C₁- bis C₄-Alkylgruppen und Methyl, Ethoxy, Hydroxyethyl und Hydroxymethyl;

wobei die Anzahl von Kohlenstoffatomen in R^a und R^b zusammengenommen 8 oder weniger beträgt und wobei die Anzahl von Kohlenstoffatomen in R^c und R^d zusammengenommen 8 oder weniger beträgt; gegebenenfalls

(a) wobei das Polyamid ein Copolymer ist, das wenigstens 80 mol-% an den Wiederholungseinheiten der Formel I oder Formel II umfasst; und/oder

(b) wobei R^b ausgewählt ist aus geraden oder verzweigten unsubstituierten C₁- bis C₄-Alkylgruppen.

20. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei das Polyamid zwischen 3 und 15 Gew.-% des reaktiven Monomergemischs bezogen auf alle reaktiven Komponenten umfasst; oder
wobei das Polyamid zwischen 3 und 12 Gew.-% des reaktiven Monomergemischs bezogen auf alle reaktiven Komponenten umfasst.

21. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das Polyamid ein cyclisches Polyamid umfasst; gegebenenfalls
Wobei das cyclische Polyamid Polyvinylypyrrolidon (PVP) in einer Menge bis zu 15 Gew.-% oder in einer Menge in dem Bereich von 2 bis 15 Gew.-% oder in einer Menge in dem Bereich von 5 bis 15 Gew.-% umfasst.

22. Silicon-Hydrogel gemäß Anspruch 1 oder 2, wobei das reaktive Monomergemisch ferner wenigstens einen zusätzlichen Bestandteil ausgewählt aus der Gruppe bestehend aus einem Verdünnungsmittel, einer UV-absorbierenden Verbindung, einem medizinischen Mittel, einer antimikrobiellen Verbindung, einer pharmazeutischen Verbindung, einer nutrazeutischen Verbindung, einer photochromen Verbindung, einer reaktiven Farbe, einem Pigment, einem copolymerisierbaren Farbstoff, einem nichtpolymerisierbaren Farbstoff, einem Trennmittel, einem Copolymer und Kombinationen davon umfasst.

23. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, ferner umfassend wenigstens ein Hydroxylalkyl(meth)acrylatmonomer; gegebenenfalls:

(a) wobei das Hydroxyalkyl(meth)acrylatmonomer ausgewählt ist aus der Gruppe bestehend aus 2-Hydroxyethyl(meth)acrylat, 3-Hydroxypropyl(meth)acrylat, 2-Hydroxypropyl(meth)acrylat, 2,3-Dihydroxypropyl(meth)acrylat, 2-Hydroxybutyl(meth)acrylat, 3-Hydroxybutyl(meth)acrylat, 1-Hydroxypropyl-2-(meth)acrylat, 2-Hydroxy-2-methylpropyl(meth)acrylat, 3-Hydroxy-2,2-dimethylpropyl(meth)acrylat, 4-Hydroxybutyl(meth)acrylat, Glycerol(meth)acrylat, Polyethylenglycolmonomethacrylat und Gemischen davon; oder

(b) wobei das Hydroxyalkyl(meth)acrylatmonomer ausgewählt ist aus der Gruppe bestehend aus 2-Hydroxyethylmethacrylat, Glycerolmethacrylat, 2-Hydroxypropylmethacrylat, Hydroxybutylmethacrylat, 3-Hydroxy-2,2-dimethylpropylmethacrylat und Gemischen davon; oder

(c) wobei das Hydroxyalkyl(meth)acrylatmonomer ausgewählt ist aus der Gruppe bestehend aus 2-Hydroxyethylmethacrylat, 3-Hydroxy-2,2-dimethylpropylmethacrylat, Hydroxybutylmethacrylat und Glycerolmethacrylat.

24. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das reaktive Monomergemisch ferner wenigstens eine zusätzliche siliconhaltige Verbindung ohne eine Hydroxygruppe umfasst.

25. Silicon-Hydrogel gemäß Anspruch 1, wobei das zweite hydroxysubstituierte Poly(disubstituiertes Siloxan) ausgewählt aus der Gruppe bestehend aus einem monofunktionellen hydroxysubstituierten linearen Poly(disubstituiertes Siloxan) mit 10 bis 20 Siloxan-Wiederholungseinheiten und einem multifunktionellen hydroxysubstituierten linearen Poly(disubstituiertes Siloxan) mit 10 bis 200 oder 10 bis 100 Siloxan-Wiederholungseinheiten; und
wobei das Verhältnis des ersten hydroxysubstituierten linearen Poly(disubstituiertes Siloxan)s zu dem zweiten hydroxysubstituierten linearen Poly(disubstituiertes Siloxan) in einem Bereich von 0,4 bis 1,2 oder 0,4 bis 1,0 liegt.

26. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das Polyamid ein gewichtsgemitteltes Molekulargewicht von wenigstens 100.000 Dalton; oder höher als 150.000 Dalton; oder zwischen 150.000 und 2.000.000 Dalton oder zwischen 300.000 und 1.800.000 Dalton aufweist, wenn das Molekulargewicht durch Größenausschlusschromatographie mit Mehrwinkel-Lichtstreuung bestimmt wird.

27. Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche, wobei das Polyamid so zu dem Reaktionsgemisch zugegeben wird, dass das Hydrogel um das Polyamid polymerisiert, um ein semi-interpenetrierendes Netzwerk zu bilden.

28. Kontaktlinse umfassend das Silicon-Hydrogel gemäß einem der vorstehenden Ansprüche.

29. Kontaktlinse gemäß Anspruch 28, wobei die Dk größer als 80 Barrer ist, wobei die Lysozymaufnahme größer als 50 µg/Linse ist, wobei die Lipidaufnahme kleiner als 10 µg/Linse ist; wobei die PQ1-Aufnahme kleiner als 15 % ist; und wobei der Kontaktwinkel kleiner als 50° ist, wenn gemessen unter Verwendung der in der Beschreibung gegebenen "Sauerstoffdurchlässigkeit-", "Lipidaufnahme-", "PQ1-Aufnahme-", "dynamischer Kontaktwinkel-" und einem der "Lysozymaufnahme"-Prüfverfahren.

Revendications

1. Hydrogel de silicone formé à partir d'un mélange de monomères réactifs comprenant :

a. entre 1 et 15 % en poids d'au moins un polyamide, le terme « polyamide » faisant référence à des polymères et des copolymères comprenant des motifs répétitifs contenant des groupes amide ;

b. au moins un premier poly(siloxane disubstitué) monofonctionnel, substitué par hydroxyle, linéaire ayant 4 à 8 motifs répétitifs de siloxane ;

c. au moins un deuxième poly(siloxane disubstitué) substitué par hydroxyle, linéaire choisi dans le groupe constitué par des poly(siloxane disubstitué) substitués par hydroxyle monofonctionnels ayant 10 à 200 ou 10 à 100 motifs répétitifs de siloxane et des poly(siloxane disubstitué) substitués par hydroxyle multifonctionnels ayant 10 à 200 ou 10 à 100 motifs répétitifs de siloxane et des mélanges correspondants ;

d. 5 à 35 % en poids d'au moins un monomère hydrophile ;

le premier poly(siloxane disubstitué) substitué par hydroxyle, linéaire et le deuxième poly(siloxane disubstitué) substitué par hydroxyle monofonctionnel, linéaire étant présents en des cconcentrations pour fournir un rapport de % en poids de tous les premiers poly(siloxane disubstitué) substitués par hydroxyle, linéaires sur tous les deuxièmes poly(siloxane disubstitué) substitués par hydroxyle, linéaires de 0,4-1,3, ou 0,4-1,0 ;

le terme « fonctionnel » signifiant un groupe qui peut subir une polymérisation par des radicaux libres ;

les concentrations de composants étant données en % en poids de tous les composants dans le mélange réactionnel, à l'exclusion d'un diluant.

2. Hydrogel de silicone selon la revendication 1, le deuxième poly(siloxane disubstitué) substitué par hydroxyle, linéaire étant choisi parmi des poly(siloxane disubstitué) linéaires substitués par hydroxyle monofonctionnels ayant 10 à 200 ou 10 à 100 motifs répétitifs de siloxane.

3. Hydrogel de silicone selon la revendication 1 ou 2,

(a) le premier poly(siloxane disubstitué) substitué par hydroxyle, monofonctionnel comprenant des composés de formule VII-1

Z étant choisi parmi O, N, S ou NCH₂CH₂O, lorsque Z est O ou S alors R² n'étant pas présent ;

R¹ étant indépendamment H ou méthyle ;

R² étant H ou étant un groupe alkyle linéaire, ramifié ou cyclique contenant un à huit atomes de carbone, l'un quelconque desquels pouvant en outre être substitué par au moins un groupe hydroxy, amide, éther et des combinaisons correspondantes ;

R³ et R⁴ étant indépendamment un groupe alkyle linéaire, ramifié ou cyclique contenant un à huit atomes de carbone, l'un quelconque desquels pouvant en outre être substitué par au moins un groupe hydroxy, amide, éther et des combinaisons correspondantes ; R³ et R⁴ pouvant être indépendamment choisis parmi méthyle, éthyle ou phényle ou pouvant être méthyle ;

n étant 4-8 ; et

R⁵ étant choisi parmi des groupes C₁ à C₈ alkyle linéaires ou ramifiés, qui peuvent être éventuellement substitués par un ou plusieurs hydroxyle, amide, éther et des combinaisons correspondantes ; et/ou

(b) le deuxième poly(siloxane disubstitué) substitués par hydroxyle comprenant un Composé de formule VII-2 :

Z étant choisi parmi O, N, S ou NCH₂CH₂O, lorsque Z est O ou S, R² n'étant pas présent ;

R¹ étant indépendamment H ou méthyle ;

R² étant H ou étant un groupe alkyle linéaire, ramifié ou cyclique contenant un à huit atomes de carbone, l'un quelconque desquels pouvant en outre être substitué par au moins un groupe hydroxy, amide, éther et des combinaisons correspondantes ;

R³ et R⁴ étant indépendamment un groupe alkyle linéaire, ramifié ou cyclique contenant un à huit atomes de carbone, l'un quelconque desquels pouvant en outre être substitué par au moins un groupe hydroxy, et qui peut être éventuellement substitué par amide, éther et des combinaisons correspondantes ; R³ et R⁴ pouvant être indépendamment choisis parmi méthyle, éthyle ou phényle ou pouvant être méthyle ;

n étant le nombre de motifs de siloxane et étant de 10 à 200, ou 10-100, ou 10-50, ou 10-20, ou 12-18 ; et

R⁵ étant choisi parmi des groupes C₁ à C₈ alkyle linéaires ou ramifiés, qui peuvent être éventuellement substitués par un ou plusieurs hydroxyle, amide, éther et des combinaisons correspondantes ; et/ou

(c) le deuxième poly(siloxane disubstitué) substitué par hydroxyle comprenant en outre un poly(siloxane disubstitué) substitué par hydroxyle difonctionnel de formule XI

R¹ étant indépendamment un atome d'hydrogène ou un groupe méthyle ;

R² et R³ étant indépendamment un groupe alkyle linéaire, ramifié ou cyclique contenant un à huit atomes de carbone, l'un quelconque desquels pouvant en outre être substitué par au moins un groupe hydroxy, amido, éther, amino, carboxyle, des groupes carbonyle et des combinaisons correspondantes ; ou étant choisis parmi méthyle, éthyle et - (CH₂CH₂O)_XOCH₃, où x est de 1 à 20 ; et

n étant de 1 à 200.

4. Hydrogel de silicone selon l'une quelconque des revendications précédentes, le premier poly(siloxane disubstitué) substitué par hydroxyle monofonctionnel et le deuxième poly(siloxane disubstitué) substitué par hydroxyle étant présents dans le mélange de monomères réactifs en une concentration totale comprise entre 40 et 70 % en poids, ou 45 à 70 % en poids sur la base de tous les composants dans le mélange réactionnel, à l'exclusion d'un diluant.

5. Hydrogel de silicone selon l'une quelconque des revendications précédentes,

(a) le polyamide comprenant un polyamide cyclique, un polyamide acyclique ou un mélange d'un polyamide cyclique et d'un polyamide acyclique ; ou

(b) le polyamide étant un polyamide acyclique.

6. Hydrogel de silicone selon l'une quelconque des revendications précédentes, le premier ou le deuxième poly(siloxane disubstitué) substitué par hydroxyle monofonctionnel comprenant un polydiméthylsiloxane monofonctionnel substitué par hydroxyle de l'une quelconque des formules VIIa-IXb :

R¹ étant méthyle ou H ; n étant compris entre 4 et 30, 4-8 ou 10-20 ; Z étant choisi parmi O, N, S ou NCH₂CH₂O, lorsque Z est O ou S, R² n'est pas présent ;

R² étant indépendamment choisi dans le groupe constitué par un groupe alkyle linéaire, ramifié ou cyclique contenant un à huit atomes de carbone, l'un quelconque desquels pouvant en outre être substitué par au moins un groupe hydroxy, et qui peut être éventuellement substitué par amide, éther et des combinaisons correspondantes ; n¹ et n² étant indépendamment compris entre 4 et 100 ; 4 et 50 ; ou 4 et 25 ;

n³ étant 1-50, 1-20, ou 1-10 ;

R⁵ étant choisi parmi des groupes C₁ à C₈ alkyle linéaires ou ramifiés, qui peuvent être éventuellement substitués par un ou plusieurs hydroxyle, amide, éther, des groupes polyhydroxyle choisis parmi des groupes C₁ à C₈ linéaires ou ramifiés ayant une formule de C_fH_g(OH)_h, f = 1 - 8 et g + h = 2f + 1 et des groupes C₁ à C₈ cycliques ayant une formule de C_fH_g(OH)_h, f = 1 - 8 et g + h = 2f - 1 et des combinaisons correspondantes ; ou R⁵ pouvant être choisi parmi méthyle, butyle ou C₂-C₅ alkyle substitué par hydroxyle, y compris hydroxyléthyle, hydroxylpropyle, hydroxylbutyle, hydroxylpentyle et 2,3-dihydroxypropyle ;

a étant 4-8 pour le premier composant de type silicone contenant hydroxyle et entre 4-100 pour le deuxième composant de type silicone contenant hydroxyle.

7. Hydrogel de silicone selon l'une quelconque des revendications précédentes, les deuxièmes poly(siloxane disubstitué) substitués par hydroxyle comprenant polydiméthylsiloxane à terminaison éther de mono-(2-hydroxy-3-méthacryloxypropyl)-propyle à terminaison mono-n-butyle (OH-mPDMS) ayant quinze motifs répétitifs de siloxane.

8. Hydrogel de silicone selon la revendication 1 ou 2,

(a) le monomère hydrophile comprenant un groupe réactif choisi dans le groupe constitué par (méth)acrylates, (méth)acrylamides, styrènes, N-vinyllactames, N-vinylamides, O-vinylcarbamates, O-vinylcarbonates, éthers de vinyle, esters de vinyle, vinyles, allyles et des combinaisons correspondantes ; et/ou

(b) le monomère hydrophile étant présent dans le mélange de monomères réactifs en une quantité comprise entre 15 et 35 % en poids.

9. Hydrogel de silicone selon l'une quelconque des revendications précédentes comprenant en outre au moins un composant chargé.

10. Hydrogel de silicone selon la revendication 1 ou 2, les deuxièmes poly(siloxane disubstitué) substitués par hydroxyle comprenant au moins un composé de formule XII

R¹ étant indépendamment un atome d'hydrogène ou un groupe méthyle ; Z étant choisi parmi O, N, S ou NCH₂CH₂O, pour Z = O et S, R² n'étant pas requis ;

R² étant choisi dans le groupe constitué par H ou un groupe alkyle linéaire, ramifié ou cyclique contenant un à huit atomes de carbone, l'un quelconque desquels pouvant en outre être substitué par au moins un groupe hydroxy, amido, éther, amino, carboxyle, des groupes carbonyle et des combinaisons ; un groupe alkylèneoxy linéaire ou ramifié, spécifiquement des groupes éthylèneoxy, [CH₂CH₂O]_p, p étant compris entre 1 et 200, ou 1 et 100, ou 1 et 50, ou 1 et 25, ou 1 et 20, éventuellement substitués par un ou plusieurs hydroxyle, amino, amido, éther, carbonyle, carboxyle et des combinaisons correspondantes ; un groupe fluoroalkyle linéaire ou ramifié en C₁-C₆ éventuellement substitué par un ou plusieurs hydroxyle, amino, amido, éther, carbonyle, carboxyle et des combinaisons correspondantes ; un groupe aryle substitué ou non substitué, spécifiquement des groupes phényle, les substituants étant choisis parmi halogène, hydroxyle, alcoxy, alkylcarbonyle, carboxy, et des groupes alkyle linéaires ou ramifiés ou cycliques qui peuvent en outre être substitués par des groupes halogène, hydroxyle, alcoxy, alkylcarbonyle et carboxyle et des combinaisons correspondantes ;

n¹ et n² étant indépendamment choisis parmi 4 à 100 ; 4 à 50 ; ou 4 à 25 ; et

n³ étant 1-50, 1-20 et 1-10.

11. Hydrogel de silicone selon la revendication 1 ou 2, le monomère hydrophile étant choisi parmi des monomères hydrophiles de type amide ; éventuellement

(a) le mélange de monomères réactifs comprenant moins de 30 % en poids, ou moins de 25 % en poids ou moins de 20 % en poids de monomères hydrophiles de type amide sur la base de tous les composants dans le mélange réactionnel, à l'exclusion d'un diluant ; et/ou

(b) les monomères hydrophiles de type amide étant compris dans le mélange réactif en des quantités comprises entre 5 et 28 % en poids, ou 5 et 25 % en poids, ou entre 8 et 20 % en poids sur la base de tous les composants dans le mélange réactionnel, à l'exclusion d'un diluant.

12. Hydrogel de silicone selon la revendication 1 ou 2,

(a) le monomère hydrophile étant choisi dans le groupe constitué par N,N-diméthylacrylamide, acrylamide, éther vinylique de l'éthylène glycol (EGVE), éther vinylique du di(éthylène glycol) (DEGVE), N-vinyle pyrrolidone (NVP), 1-méthyl-3-méthylène-2-pyrrolidone, 1-méthyl-5-méthylène-2-pyrrolidone, 5-méthyl-3-méthylène-2-pyrrolidone ; 1-éthyl-5-méthylène-2-pyrrolidone, N-méthyl-3-méthylène-2-pyrrolidone, 5-éthyl-3-méthylène-2-pyrrolidone, 1-n-propyl-3-méthylène-2-pyrrolidone, 1-n-propyl-5-méthylène-2-pyrrolidone, 1-isopropyl-3-méthylène-2-pyrrolidone, 1-isopropyl-5-méthylène-2-pyrrolidone, N-vinyl-N-méthylacétamide (VMA), N-vinyl-N-éthylacétamide, N-vinyl-N-éthylformamide, N-vinylformamide, N-vinylacétamide, N-vinylisopropylamide, alcool allylique, N-vinylcaprolactame, N-2-hydroxyéthylcarbamate de vinyle, ester de N-vinyle de N-carboxy-β-alanine ; N-carboxyvinyl-β-alanine (VINAL), N-carboxyvinyl-α-alanine et des mélanges correspondants ; ou

(b) le monomère hydrophile étant choisi parmi N,N-diméthylacrylamide, N-vinylpyrrolidone, N-vinyl-N-méthylacétamide, N-vinylacétamide et 1-méthyl-5-méthylène-2-pyrrolidone ; ou

(c) le monomère hydrophile comprenant N-vinylpyrrolidone, N,N-diméthylacrylamide ou des mélanges correspondants.

13. Hydrogel de silicone selon l'une quelconque des revendications précédentes, l'hydrogel de silicone ayant une perméabilité à l'oxygène (Dk) d'au moins 80 barrers, ou 80 à 200 barrers, 90 à 180 barrers, 100 à 160 barrers, lorsque la perméabilité à l'oxygène est mesurée en utilisant le procédé de test « perméabilité à l'oxygène » donné dans la description.

14. Hydrogel de silicone selon la revendication 9, le monomère chargé comprenant au moins un groupement ionique choisi dans le groupe constitué par des anions, des cations, des zwitterions, des bétaïnes et des mélanges correspondants.

15. Hydrogel de silicone selon la revendication 14, le monomère chargé comprenant au moins un groupe acide carboxylique ; éventuellement

(a) le monomère chargé comprenant au moins un monomère d'acide carboxylique choisi dans le groupe constitué par l'acide (méth)acrylique, l'acide fumarique, l'acide maléique, l'acide itaconique, l'acide crotonique, l'acide cinnamique, l'acide vinylbenzoïque, les monoesters de l'acide fumarique, de l'acide maléique et de l'acide itaconique et des mélanges correspondants ; ou

(b) le monomère chargé comprenant un mélange de monomère anionique et cationique ; ou

(c) le monomère chargé étant choisi dans le groupe constitué par acide(méth)acrylique, N-[(éthényloxy)carbonyl]-P-alanine (VINAL), acide 3-acrylamidopropanoïque (ACA1), acide 5-acrylamidopropanoïque (ACA2), acide 3-acrylamido-3-méthylbutanoïque (AMBA), chlorure de 2-(méthacryloyloxy)éthyltriméthylammonium (sel Q), acide 2-acrylamido-2-méthylpropane sulfonique (AMPS), 1-propanaminium, N-(2-carboxyéthyl)-N,N-diméthyl-3-[(1-oxo-2-propène-1-yl)amino]-, sel interne (CBT, carboxybétaïne), 1-propanaminium, N,N-diméthyl-N-[3-(1-oxo-2-prop-1-yl)amino]propyl]-3-sulfo-, sel interne (SBT, sulfobetaïne,), 3,5-Dioxa-8-aza-4-phosphaundéc-10-en-1-aminium, 4-hydroxy-N,N,N-triméthyl-9-oxo-, sel interne, 4-oxyde (9CI) phosphobétaïne (PBT), 2-méthacryloyloxyéthylphosphorylcholine, 3-(diméthyl(4-vinylbenzyl)ammonio)propane-1-sulfonate (DMVBAPS), 3-(3-acrylamidopropyl)diméthyllammonio)propane-1-sulfonate (AMPDAPS), 3-((3-méthacrylamidopropyl)diméthylammonium)propane-1-sulfonate (MAMPDAPS), 3-((3-(acryloyloxy)propyl)diméthylammonium)propane-1-sulfonate (APDAPS), méthacryloyloxy)propyl)diméthylammonium)propane-1-sulfonate (MAPDAPS) et des mélanges correspondants ; ou

(d) le monomère chargé étant choisi dans le groupe constitué par l'acide (méth)acrylique, la N-[(éthenyloxy)carbonyl]-P-alanine (VINAL), l'acide 3-acrylamidopropanoïque (ACA1), l'acide 5-acrylamidopropanoïque (ACA2) et des mélanges correspondants.

16. Hydrogel de silicone selon l'une quelconque des revendications 9 ou 15, l'au moins un monomère chargé représentant jusqu'à 5 % en poids, ou entre 0,5 et 5 % en poids, ou entre 0,5 et 3 % en poids, ou entre 0,5 et 2 % en poids, ou entre 1 et 5 % en poids ou entre 1 et 3 % en poids, sur la base du poids total du mélange de monomères réactifs.

17. Hydrogel de silicone selon l'une quelconque des revendications précédentes, comprenant un monomère chargé choisi parmi l'acide acrylique, l'acide méthacrylique et des mélanges correspondants.

18. Hydrogel de silicone selon la revendication 1 ou 2,

(a) le polyamide comprenant un polyamide acyclique choisi dans le groupe constitué par PVMA, PNVA et des poly[N-vinyl-N-alkyl-acétamide], le groupe N-alkyle étant choisi dans le groupe constitué par des groupes alkyle linéaires et ramifiés contenant entre un et cinq atomes de carbone et des copolymères et des mélanges correspondants ; et/ou

(b) le polyamide comprenant un poly(N-vinyl-N-méthylacetamide), un poly(N-vinylacétamide), un polydiméthylacrylamide ou un mélange de deux ou plus de ceux-ci ; et/ou

(c) le polyamide comprenant un copolymère ; éventuellement

le copolymère comprenant des motifs répétitifs choisis dans le groupe constitué par N-vinylamides, acrylamides, (méth)acrylates d'hydroxyalkyle, (méth)acrylates d'alkyle, N-vinylpyrrolidone, N,N-diméthylacrylamide, 2-hydroxyéthylméthacrylate, acétate de vinyle, acrylonitrile, méthacrylate d'hydroxypropyle, acrylate de 2-hydroxyéthyle, méthacrylate de méthyle, méthacrylate de butyle, méthacryloxypropoyl-tristriméthylsiloxysilane, acrylates ou méthacrylates substitués par des siloxanes et des mélanges correspondants.

19. Hydrogel de silicone selon la revendication 1 ou 2, le polyamide comprenant des motifs répétitifs de formule I ou de formule II

X étant une liaison directe, - (CO) - ou - (CO) -NHR^e-, R^e étant un groupe C₁ à C₃ alkyle ;

R^a étant choisi parmi H, des groupes C₁ à C₄ alkyle linéaires ou ramifiés, substitués ou non substitués ;

R^b étant choisi parmi H, des groupes C₁ à C₄ alkyle linéaires ou ramifiés, substitués ou non substitués, des groupes amino ayant jusqu'à deux atomes de carbone, des groupes amide ayant jusqu'à quatre atomes de carbone et des groupes alcoxy ayant jusqu'à deux atomes de carbone ;

R^c étant choisi parmi H, des groupes C₁ à C₄ alkyle linéaires ou ramifiés, substitués ou non substitués, ou méthyle, éthoxy, hydroxyéthyle et hydroxyméthyle ;

R^d étant choisi parmi H, des groupes C₁ à C₄ alkyle linéaires ou ramifiés, substitués ou non substitués, ou méthyle, éthoxy, hydroxyéthyle et hydroxyméthyle ;

le nombre d'atomes de carbone dans R^a et R^b pris ensemble étant 8 ou moins, et le nombre d'atomes de carbone dans R^c et R^d pris ensemble étant 8 ou moins ; éventuellement

(a) le polyamide étant un copolymère comprenant au moins 80 % en moles des motifs répétitifs de formule I ou de formule II ; et/ou

(b) R^b étant choisi parmi des groupes C₁ à C₄ alkyle non substitués linéaires ou ramifiés.

20. Hydrogel de silicone selon la revendication 1 ou 2, le polyamide comprenant entre 3 et 15 % en poids du mélange de monomères réactifs, sur la base de tous les composants réactifs ; ou
le polyamide comprenant entre 3 et 12 % en poids du mélange réactif sur la base de tous les composants réactifs.

21. Hydrogel de silicone selon l'une quelconque des revendications précédentes, le polyamide comprenant un polyamide cyclique ; éventuellement
le polyamide cyclique comprenant une polyvinylpyrrolidone (PVP) en une quantité allant jusqu'à 15 % en poids, ou une quantité dans la plage de 2 à 15 % en poids, ou une quantité dans la plage de 5 à 15 % en poids.

22. Hydrogel de silicone selon la revendication 1 ou 2,le mélange de monomères réactifs comprenant en outre au moins un constituant supplémentaire choisi dans le groupe constitué par un diluant, un composé absorbant des UV, un agent médicinal, un composé antimicrobien, un composé pharmaceutique, un composé nutraceutique, un composé photochromique, une teinture réactive, un pigment, un colorant copolymérisable, un colorant non polymérisable, un agent de libération, un copolymère et des combinaisons correspondantes.

23. Hydrogel de silicone selon l'une quelconque des revendications précédentes comprenant en outre au moins un monomère de (méth)acrylate d'hydroxyalkyle ; éventuellement ;

(a) ledit monomère de (méth)acrylate d'hydroxyalkyle étant choisi dans le groupe constitué par (méth)acrylate de 2-hydroxyéthyle, (méth)acrylate de 3-hydroxypropyle, (méth)acrylate de 2-hydroxypropyle, (méth)acrylate de 2,3-dihydroxypropyle, (méth)acrylate de 2-hydroxybutyle, (méth)acrylate de 3-hydroxybutyle, 2-(méth)acrylate de 1-hydroxypropyle, (méth)acrylate de 2-hydroxy-2-méthyl-propyle, (méth)acrylate de 3-hydroxy-2,2-diméthyl-propyle, (méth)acrylate de 4-hydroxybutyle, (méth)acrylate de glycérol, monométhacrylate de polyéthylène glycol et des mélanges correspondants ; ou

(b) ledit monomère de (méth)acrylate d'hydroxyalkyle étant choisi dans le groupe constitué par méthacrylate de 2-hydroxyéthyle, méthacrylate de glycérol, méthacrylate de 2-hydroxypropyle, méthacrylate d'hydroxybutyle, méthacrylate de 3-hydroxy-2,2-diméthyl-propyle et des mélanges correspondants ; ou

(c) ledit monomère de (méth)acrylate d'hydroxyalkyle étant choisi dans le groupe constitué par méthacrylate de 2-hydroxyéthyle, méthacrylate de 3-hydroxy-2,2-diméthyl-propyle, méthacrylate d'hydroxybutyle ou méthacrylate de glycérol.

24. Hydrogel de silicone selon l'une quelconque des revendications précédentes, le mélange de monomères réactifs comprenant en outre au moins un composé contenant une silicone supplémentaire sans un groupe hydroxyle.

25. Hydrogel de silicone selon la revendication 1, le deuxième poly(siloxane disubstitué) substitué par hydroxyle étant choisi dans le groupe constitué par un poly(siloxane disubstitué) linéaire, substitué par hydroxyle monofonctionnel ayant 10 à 20 motifs répétitifs de siloxane et un poly(siloxane disubstitué) linéaire, substitué par hydroxyle multifonctionnel ayant 10 à 200, ou 10 à 100 motifs répétitifs de siloxane ; et
le rapport du premier poly(siloxane disubstitué) linéaire substitué par hydroxyle sur le deuxième poly(siloxane disubstitué) linéaire, substitué par hydroxyle étant dans une plage de 0,4 à 1,2, ou de 0,4 à 1,0.

26. Hydrogel de silicone selon l'une quelconque des revendications précédentes, le polyamide ayant un poids moléculaire moyen en poids d'au moins 100 000 Daltons ; ou supérieur à 150 000 Daltons ; ou compris entre 150 000 et 2 000 000 Daltons, ou compris entre 300 000 et 1 800 000 Daltons lorsque le poids moléculaire est déterminé par chromatographie d'exclusion stérique avec diffusion de lumière multi-angle.

27. Hydrogel de silicone selon l'une quelconque des revendications précédentes, le polyamide étant ajouté au mélange réactionnel de sorte que l'hydrogel polymérise autour du polyamide, formant un réseau semi-interpénétrant.

28. Lentille de contact comprenant l'hydrogel de silicone selon l'une quelconque des revendications précédentes.

29. Lentille de contact selon la revendication 28, le Dk étant supérieur à 80 barrers, l'absorption de lysozyme étant supérieure à 50 µg/lentille, l'absorption de lipides étant inférieure à 10 µg/lentille ; l'absorption de PQ1 étant inférieure à 15 % ; et l'angle de contact étant inférieur à 50° lorsqu'ils sont mesurés en utilisant les procédés de test « perméabilité à l'oxygène », « absorption de lipides », « absorption de PQ1 », « angle de contact dynamique », et l'un ou l'autre des procédés de test « absorption de lysozyme » donnés dans la description.