The present invention relates to an apparatus for therapy with non-charged particles, preferably photons, comprising a target generating by Bremsstrahlung a therapy beam and a particle filter producing uniform dose distributions. In the apparatus the therapy beam is purged or cleaned from unwanted secondary charged particles such as secondary electrons, positrons or protons.
In radiation therapy with high energy non-charged particles, in particular high energy photons and neutrons, secondary charged particles are generated both from the rear area of a bremsstrahlung generating target such as for example a thin foil of gold and from the flattening filter itself. In case of photon therapy the fluence of photons varies across the beam cross-section. This results in a non desired uneven dose distribution across the field to be irradiated. To cure this it is known to insert conical radiation filters damping the central ray of the radiation beam to a greater extent than those at the periphery. In this way the radiation beam and therefore the dose distribution is made uniform.
Particularly in connection with deep seating tumours it is required to use radiation that has its dose maximum (maximum dose absorbed in the treated volume) as deep as possible and highest possible penetrability. To achieve said objects it is known to "harden" the beam i.e. to increase the energy of the therapy beam. Beams with particles having higher energies normally require the use of large accelerators of high energy. However, with a "hardening filter" low energy non-charged particles are instead filtered out of the useful beam resulting in an increase of the mean energy of the beam.
For low to intermediate energy photons the beam quality is also influenced mainly by the air through which the beam travels since Compton electrons will be generated in the air. Thus the air itself is the principal contamination source.
From SE-A-406 240 is previously known to harden a therapy beam of photons with a flattening filter made by low atomic number, high density ceramics.
Brahme in 1976 warned against hardening the photon beam too much on the central axis as this would make the beam uniformity depth dependent. Instead Brahme suggested the use of a low atomic number filter material only at the periphery of the beam and a high atomic number on the central axis. In doing so a perfect uniformity of the beam was achieved independent of the depth in the absorbing mass.
Increasing the particle energy inevitably increases the mean energy of the secondary charged parti- des which are generated when the beam strikes the flattening filter. Thus normally the flattening filter itself is the dominant source of unwanted secondary charged particles at the higher energies. In connection with photon therapy said secondary charged particles are secondary electrons or positrons which will contaminate the beam with the result that the dose maximum is brought closer to the skin surface. Moreover they will contribute to an increased non-desired absorbed dose to the skin.
Another disadvantage obtained when the energy of the photons is high is that the depth dose distribution will depend on the size of the radiation field. The larger the size the nearer the skin will be the dose maximum.
In order to eliminate unwanted secondary charged particles from the useful therapy beam it is known to insert metal screens in the beam and provide such screens with a thin layer of a material with a high atomic number. Said thin layer is applied in an amount of the order of 0.1-0.2 g/cm2. This thin layer will scatter secondary electrons generated in the metal screen. Nevertheless said scattering is un- sufficient and there will still be too many secondary electrons and positrons in the useful beam.
FR-A 2 295 673 relates to a conventional flattening filter for attenuation of the intensity of the central X-rays so as to obtain a flat dose curve. The filter per se generates undesirable secondary electrons disturbing the depth dose curve. The filter is located close to the X-ray target.
US-A 3 696 629 relates to an electron filter for filtering out non wanted secondary electrons from the therapy beam. The electron filter comprises magnetic means located far from the X-ray target and arranged outside the therapy beam. A substantial magnetic field strenght must be created by the magnetic means in order to subject secondary electrons generated at the photon filter or target near the photon source of the therapy beam to a Lorenz force of sufficient magnitude to drive the secondary electrons out of the therapy beam. Such a strong magnetic field over such a large field size requires the use of large and therefore also heavy magnets. By applying the magnetic fields with alternative and opposite field directions the effect of the secondary electrons is diffused, but not very effectively.
The object of the present invention is to provide a novel apparatus for use in therapy with high energy, non-charged particles, particularly photons, avoiding the drawbacks of the previously known apparatuses using flattening filters.
This a achieved by introducing in the filter itself a magnetic field through which the contaminated beam must pass before striking the surface to be irradiated. During the passage of the filter the charged, secondary particles generated by the filter itself are subjected to a Lorenzforce deflecting said secondary particles out of the useful beam generally along a helical path.
The advantages offered by the invention are that the depth of dose maximum is substantially increased, for a 20 MeV photon beam about 2 cm deeper, and that the depth of penetration at the 50% level is increased, for said 20 MeV photon beam of the order of 4 cm. Up to now such deep penetrating beams are only available from high energy accelerators generating 40 MeV photons or more. Thus, by using a small and therefore low costs accelerator which is producing a 20 MeV beam and which is provided with a novel magnetic flattening filter a beam comparable to that of a 40 MeV accelerator is achieved. In a simple operation the magnetic filter may be removed from the accelerator which then may be used for conventional therapy purposes. Thus by adding and removing the magnetic filter one and the same accelerator can be used for medium energy as well as high energy radiation purposes. Previously two different accelerators were used for this purpose.
Various embodiments of the invention will be described below with reference to the accompanying drawings wherein
In Figs. 1 and 2 a magnetic flattening filter comprises a cylindrical housing 1 serving as a means for mounting the magnetic filter close to the Bremsstrahlung target, not shown. A flange 2 is provided around the bottom ring of the cylindrical housing. The filter is shown close to natural size.
The magnetic filter comprises a conical body 4 mounted centrally on a circular base plate 5. A ring 6 of generally the same height as a conical body 4 is mounted on the base plate 5 at the periphery thereof. As shown in Fig. 3 the conical body 4 is magnetized in the axial direction. The ring 6 is also magnetized in the axial direction but with a polarity which is opposite to that of the conical body 4. The base plate 5 is in this embodiment made of magnetically conducting material thus serving as a yoke for the magnetic field lines. Thus there is a strong magnetic field between the conical body and the ring which the particles of the beam must pass. If the non-charged particles are high energy photons secondary electrons (e-) will be generated by the filter itself and said electrons will be subjected to a Lorenzforce driving the secondary electrons out of the path of the beam along a helical path as schematically shown in broken lines in Fig. 3. Should the beam 3 also include high energy positrons (e+) these will also will be subjected to said Lorenz force and move out of the beam along the path shown by dashed lines at e+ in Fig. 3 but in a direction which is opposite to that of the negatively charged electrons.
The material used for the conical body should be capable of providing a strong magnetic field and simultaneously exhibit a high density (so as to harden the beam as much as possible). Permanent magnetic materials such as Fe, Co and alloys of samarium, cobalt and other rare earth metals are preferred. If a permanent magnetic material is used the photon beam will simultaneously be differentially hardened due to the fairly low atomic number of the magnetic materials (Z-25, Fe, Co etc.) as compared to lead or tungsten which normally are used in flattening filters. The preferred samarium-cobalt-alloy is Sm-Co5. This alloy is very hard and therefore difficult to machine into conical form. A conical body of Sm-Co5 may instead be formed by cylindrical slabs 7 stacked upon each other and of successive smaller diameter as shown in Fig. 4. A non magnetic material 8 is used to fill up to a general conical form. The top portion 9 of the conical body is difficult to machine if made by said samarium-cobalt-alloy. Instead the top portion may be formed by Fe.
The conical body 4 shown in Fig. 5 is solid and made of for example ferromagnetic material. Its outer surface is provided with a thin layer 10 of a high atomic number material so as to scatter secondary, charged particle as discussed in the introductory portion of the present specification. This layer 10 may for example be gold and is applied in an amount of 0.1-0.2 g/cm2.
The ring 6 may, as shown in broken lines in Fig. 3, be formed by several individual rings cemented or clamped together into a structural unit.
In Fig. 6 a second magnetic filter embodiment is shown. Here the conical body 4 and the ring 6 are transversally magnetized, i.e. the lines of the magnetic fields are extending in a direction perpendicular to the central axis of the magnetic filter. In Fig. 6 the beam strikes the base of the conical body from a point situated below the plane of the paper and the secondary charged particles are also in this embodiment subjected to the Lorenz force moving the charged particles out of the path of the useful beam along a helix path as schematically indicated by the dashed lines in Fig. 6.
In Fig. 7 the transversal magnetization of the filter members of Fig. 6 are shown. A base plate 5 similar to that of Fig. 3 may be used for the filter shown in Fig. 6. It is however also possible to use a base plate of non-magnetic conductive material if the magnetic field is closed by way of a magnetic yoke in the form of two opposing pole shoes 11, 12 interconnected with a pole piece 13 as shown in Fig. 8. In the Fig. 8 embodiment of the magnetic filter the ring has accordingly been replaced by the pole pieces 11, 12 surrounding the conical body 4. In the Fig. 8 embodiment it is accordingly possible to mount the conical body 4 on a base plate 5 which must not be magnetically conductive.
The magnetic field in this configuration can be continously varied by adding a winding 14 supplied with direct current in order to establish the magnetic field. The purpose of this will be explained below.
In the embodiments described thus far magnetic yokes have been used in order to have a magnetic field which is as strong as possible. Theoretically, however, it is possible to refrain from a magnetic yoke and instead close the magnetic field lines at infinity. This results in a weaker magnetic field but is theroetically possible using the principles of the present invention. In this most simple form of an electron filter the filter is just a permanent magnet.
If low energy non-charged particles are used for therapy purposes and no particle intensity filtration is required in order to have a uniform beam, then it is possible to reduce the magnetic filter to a single magnetized slab of uniform thickness. The direction of the magnetization may either be transversal, like the embodiments shown in Figs. 6 and 7, or axial, as shown in Figs. 2 and 3.
The slab will subject the secondary. charged particles generated in the slab to a Lorenz force moving the secondary charged particles out of the treatment beam along helical paths.
In Fig. 9 depth dose curves are shown. Curve A has been recorded with the magnetic filter described in Figs. 1-4 and curve B has been taken with a conventional flattening filter made of lead. In both cases 20 MeV photons were used for the beam and the size of the radiated field was 20 x 20 cm2. Comparing curve A with curve B it is apparent that the dose maximum of curve A is situated 4.2 cm below the surface while with the conventional lead filter the dose maximum is situated about 2.2 cm below the surface. Thus the depth of dose maximum is about 2 cm deeper if the magnetic flattening filter in accordance with the invention is used. This has been indicated with A D. Comparing the penetration of the beam it is obvious that, for a given dose, the penetration of the beam in which the magnetic filter is used is about 4 cm deeper than that which is achieved when a conventional filter is used. This difference has been indicated as p in Fig. 9. In Fig. 9 there is a shaded area. This shaded area represents - as far as the position of the dose maximum is concerned - the non desired effect of the secondary electrons and positrons if they were present. From Fig. 9 it is also apparent that by reducing the strength of the magnetic field Ap will also reduce. Conversly, increasing the strength of the magnetic field through which the non wanted changed particles must travel will increase Ap. Accordingly by varying the magnetic field, for example by providing an electro magnet around the conical body 4, the penetrability of the beam may be varied.