(19)
(11)EP 2 710 396 B1

(12)EUROPEAN PATENT SPECIFICATION

(45)Mention of the grant of the patent:
29.07.2020 Bulletin 2020/31

(21)Application number: 12724729.4

(22)Date of filing:  09.05.2012
(51)International Patent Classification (IPC): 
G01R 33/34(2006.01)
(86)International application number:
PCT/IB2012/052309
(87)International publication number:
WO 2012/156866 (22.11.2012 Gazette  2012/47)

(54)

PERSONALIZED RF COIL ARRAY FOR MR IMAGING GUIDED INTERVENTIONS

PERSONALISIERTES RF-SPULENARRAY FÜR MR-BILDGEBUNGS-GEFÜHRTE INTERVENTIONEN

RÉSEAU DE BOBINES RF PERSONNALISÉ POUR INTERVENTIONS GUIDÉES PAR IMAGERIE PAR RÉSONANCE MAGNÉTIQUE


(84)Designated Contracting States:
AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

(30)Priority: 16.05.2011 EP 11166210

(43)Date of publication of application:
26.03.2014 Bulletin 2014/13

(73)Proprietors:
  • Koninklijke Philips N.V.
    5656 AG Eindhoven (NL)
    Designated Contracting States:
    AL AT BE BG CH CY CZ DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR 
  • Philips Intellectual Property & Standards GmbH
    20099 Hamburg (DE)
    Designated Contracting States:
    DE 

(72)Inventors:
  • MARTENS, Hubert, Cécile, François
    NL-5656 AE Eindhoven (NL)
  • MOORE, Elizabeth, Anne
    NL-5656 AE Eindhoven (NL)
  • POSSANZINI, Cecilia
    NL-5656 AE Eindhoven (NL)
  • NIJENHUIS, Marco, Hubertus, Johannes
    NL-5656 AE Eindhoven (NL)
  • PARDOEL, Michel, Gerardus
    NL-5656 AE Eindhoven (NL)
  • BOS, Clemens
    NL-5656 AE Eindhoven (NL)
  • ELEVELT, Aaldert, Jan
    NL-5656 AE Eindhoven (NL)
  • WIRTZ, Daniel
    NL-5656 AE Eindhoven (NL)

(74)Representative: Philips Intellectual Property & Standards 
High Tech Campus 5
5656 AE Eindhoven
5656 AE Eindhoven (NL)


(56)References cited: : 
JP-A- 2 200 243
US-A- 5 905 378
US-A1- 2007 016 003
JP-A- 6 181 907
US-A1- 2005 080 333
  
  • ARTEMOV D ET AL: "Switchable Multicoil Array for MR Micro-Imaging of Breast Lesions", 19990101; 19990000, vol. 41, 1 January 1999 (1999-01-01), pages 569-574, XP002329115,
  • VOGAN J ET AL: "Manipulation in mri devices using electrostrictive polymer actuators: with an application to reconfigurable imaging coils", ROBOTICS AND AUTOMATION, 2004. PROCEEDINGS. ICRA '04. 2004 IEEE INTERN ATIONAL CONFERENCE ON NEW ORLEANS, LA, USA APRIL 26-MAY 1, 2004, PISCATAWAY, NJ, USA,IEEE, US, vol. 3, 26 April 2004 (2004-04-26), pages 2498-2504, XP010768492, DOI: 10.1109/ROBOT.2004.1307436 ISBN: 978-0-7803-8232-9
  • ULI GOTSHAL ET AL: "Transmit-Receive Phased Array for MR Guided Spine Interventional Procedures", PROC.INTL.SOC.MAG.RESON.MED. 10, 1 January 2002 (2002-01-01), page 327, XP55036741,
  • B.M. KAUFMAN ET AL: "Coil System for Optimal MR Mammography and MR-Guided Intervention", PROC.INTL.SOC.MAG.RESON.MED. 17, 1 January 2009 (2009-01-01), page 4740, XP55036742,
  • H. LIU ET AL: "MR Monitored Neurosurgical Procedures at 1.5 Tesla", PROC.INTL.SOC.MAG.RESON.MED., 1 January 1998 (1998-01-01), page 1977, XP55036743,
  • ANDERSON N. NNEWIHE ET AL: "Custom-fitted 16-channel bilateral breast coil for bidirectional parallel imaging", MAGNETIC RESONANCE IN MEDICINE, vol. 66, no. 1, 1 February 2011 (2011-02-01), pages 281-289, XP55036744, ISSN: 0740-3194, DOI: 10.1002/mrm.22771
  • F. LIU ET AL: "Debye Potential based Method for the Analysis of Electromagnetic Fields inside a Lossy, Multilayered Spherical Head Phantom Excited by MRI Coils", PROC.INTL.SOC.MAG.RESON.MED. 11, 1 January 2004 (2004-01-01), page 1648, XP55036745,
  • B. KEIL ET AL: "Age-Optimized 32-Channel Brain Arrays for 3T Pediatric Imaging", PROC.INTL.SOC.MAG.RESON.MED., 1 January 2010 (2010-01-01), page 643, XP55036747,
  • B. KEIL ET AL: "A 64-Channel Array Coil for 3T Head/Neck/C-spine Imaging", PROC.INTL.SOC.MAG.RESON.MED., 23 April 2011 (2011-04-23), page 160, XP55036748,
  
Note: Within nine months from the publication of the mention of the grant of the European patent, any person may give notice to the European Patent Office of opposition to the European patent granted. Notice of opposition shall be filed in a written reasoned statement. It shall not be deemed to have been filed until the opposition fee has been paid. (Art. 99(1) European Patent Convention).


Description

FIELD OF THE INVENTION



[0001] The invention relates to the field of magnetic resonance (MR) imaging. It concerns a method of manufacturing a personalized RF coil array for MR imaging guided interventions.

[0002] Image-forming MR methods which utilize the interaction between magnetic fields and nuclear spins in order to form two-dimensional or three-dimensional images are widely used nowadays, notably in the field of medical diagnostics, because for the imaging of soft tissue they are superior to other imaging methods in many respects, do not require ionizing radiation and are usually not invasive.

BACKGROUND OF THE INVENTION



[0003] According to the MR method in general, the body of the patient to be examined is arranged in a strong, uniform magnetic field whose direction at the same time defines an axis (normally the z-axis) of the co-ordinate system on which the measurement is based. The magnetic field produces different energy levels for the individual nuclear spins in dependence on the magnetic field strength which can be excited (spin resonance) by application of an electromagnetic alternating field (RF field) of defined frequency (so-called Larmor frequency, or MR frequency). From a macroscopic point of view, the distribution of the individual nuclear spins produces an overall magnetization which can be deflected out of the state of equilibrium by application of an electromagnetic pulse of appropriate frequency (RF pulse) while the magnetic field of the RF pulse extends perpendicular to the z-axis, so that the magnetization performs a precession about the z-axis. This motion of the magnetization describes a surface of a cone whose angle of aperture is referred to as flip angle. The magnitude of the flip angle is dependent on the strength and the duration of the applied electromagnetic pulse. In the case of a so-called 90° pulse, the spins are deflected from the z axis to the transverse plane (flip angle 90°). The RF pulse is radiated toward the body of the patient via a RF coil arrangement of the MR device. The RF coil arrangement typically surrounds the examination volume in which the body of the patient is placed.

[0004] After termination of the RF pulse, the magnetization relaxes back to the original state of equilibrium, in which the magnetization in the z direction is built up again with a first time constant T1 (spin lattice or longitudinal relaxation time), and the magnetization in the direction perpendicular to the z direction relaxes with a second time constant T2 (spin-spin or transverse relaxation time). The variation of the magnetization can be detected by means of receiving RF coils which are arranged and oriented within the examination volume of the MR device in such a manner that the variation of the magnetization is measured in the direction perpendicular to the z-axis. The decay of the transverse magnetization is accompanied, after application of, for example, a 90° pulse, by a transition of the nuclear spins (induced by local magnetic field inhomogeneities) from an ordered state with the same phase to a state in which all phase angles are uniformly distributed (dephasing). The dephasing can be compensated by means of a refocusing pulse (for example a 180° pulse). This produces an echo signal (spin echo) in the receiving coils.

[0005] In order to realize spatial resolution in the body, linear magnetic field gradients extending along the three main axes are superposed on the uniform magnetic field, leading to a linear spatial dependency of the spin resonance frequency. The signal picked up in the receiving coils then contains components of different frequencies which can be associated with different locations in the body. The signal data obtained via the receiving coils corresponds to the spatial frequency domain and is called k-space data. The k-space data usually includes multiple lines acquired with different phase encoding. Each line is digitized by collecting a number of samples. A set of k-space data is converted to a MR image by means of Fourier transformation or other suitable algorithms.

[0006] The lack of harmful effects on the examined patient and the operator make MR imaging well-suited for "interventional radiology", wherein the acquired and reconstructed MR images are used to guide invasive procedures. The general goal of imaged guidance is to apply imaged-based information to the processes of diagnosis and therapy. Known MR imaging-guided therapy systems use pre-operatively acquired MR images to create anatomic models, which provide localization, targeting, and visualization of the 3D anatomy. These models support pre-operative planning to define and optimize access strategies and to simulate planned interventions. These models connect image coordinates with the actual position defined by an instrument's location in the surgical field. Thus, they enable a surgeon to navigate and execute procedures with full knowledge of the surrounding anatomy.

[0007] In a plurality of practical applications, shifts and deformations of soft tissues occur during surgery because of mechanical factors, physiological motion, swelling, or hemorrhage. These changes may displace organs or their tissue components to such a degree that pre-operatively acquired MR imaging-based 3D models cannot be registered with the patient's actual anatomy. In this situation the ultimate solution for accurate MR imaging-guided surgery is real-time intra-operative MR imaging or at least frequent updating of the volumetric MR images during interventional procedures. This results in methods that can continuously detect changes of the position of various tissue components and locate the targets of the interventions and their environments in order to define trajectories to the lesion to be treated. Hence, the justification of intra-operative MR imaging is the change in anatomy during surgeries or the change of tissue integrity during therapy. The goal is to allow MR imaging-guided therapy to make full use of the anatomic and functional information accessible by current MR imaging methods. By providing the physician with current MR image information, safety and efficiency of surgical or interventional procedures is significantly improved.

[0008] A publication titled "Switchable Multicoul Array for MR Micro-Imaging of Breast Lesions" by D. Artemov et al describes a switchable coil area which enables remote selection of the coil pair closest to the position of the lesion in the breast, thereby permitting coverage of the whole breast without changing the position of the coils. The position of the lesion/lesions was defined from mammographic films, and the matching boxes were connected to the coils closest to the estimated position of the breast lesions.

[0009] US 2007/016003 A1 describes a MRI coil system. It is said that, in a preferred embodiment, multiple coils are selected on the basis of being sized appropriately to the patient anatomy, with each coil imaging substantially independent sub-volumes of the total imaging volume. It is said that in this way, the combined signal to noise ratio from all the coils can be maximized.

[0010] US 2005/0080333 A1 describes that different coil configurations may be used for different purposes (bilateral, unilateral) and to accommodate various patient breast sizes, which is said to be critical to acquire optimal images.

[0011] A publication titled "Manipulation in MRI Devices using Electrostrictive Polymer Actuators: With an Application to Reconfigurable Imaging Coils" by J. Vogan et al describes a method for remotely changing the size and location of the coil with EPAM actuators while the patient remains in MRI. It is said that optimal image quality results when the sensitivity profile of the coil is matched to the volume of interest within the patient.

[0012] A publication titled "Transmit-Receive Phased Array for MR Guided Spine Interventional Procedures" by U. Gotshal et al describes a phased array coil for enhancing spine image quality. The design of the phased array coil is said to address the lack of SNR and resolution with general-purpose coils in the area of spine surgery.

[0013] A publication titled "Coil System for Optimal MR Mammography and MR-Guided Intervention" by B.M. Kaufman et al describes a breast coil system having two coil modules that are diagnostic and interventional. It is said that the use of two different RF coils dedicated to these two imaging protocols maximizes the benefit of MRI breast imaging in that the diagnostic coil is dedicated to provide high SNR in diagnostic imaging and time resolution in dynamic imaging.

[0014] A problem is that it remains difficult in a surgical setting to optimally place the RF coils required for MR signal acquisition around the respective body portion in such a fashion that (i) a good signal-to-noise ratio (SNR) is obtained and (ii) a good access to the interventional field is assured for the physician.

SUMMARY OF THE INVENTION



[0015] From the foregoing it is readily appreciated that there is a need for an improved RF coil arrangement for MR imaging guided interventions that enables high-quality intra-operative MR imaging as well as good access to the patient.

[0016] In accordance with the invention, a method of manufacturing a personalized RF coil array for MR imaging guided interventions is disclosed. The method comprises the steps of:
  • acquiring diagnostic image data reflecting the anatomy of a portion of a patient's body, the diagnostic image data comprising X-ray, CT and/or MR images; determining an interventional field within the portion of the patient's body by planning the surgical intervention on the basis of the diagnostic image data; providing a substrate for accommodating RF antennae, the substrate being adapted to the shape of the patient's body, so that the RF antennae are placed firmly, in close proximity, and in a well-defined position on the patient's body during the surgical intervention; simulating, on the basis of the diagnostic image data, a RF electromagnetic field distribution during the MR imaging guided surgical intervention to compute sizes, shapes and positions of the RF antenna on the substrate which optimize the signal-to-noise ratio of MR signal acquisition from the interventional field, and arranging the RF antennae on the substrate in accordance with the computed sizes, shapes and positions to establish the personalized RF coil array.


[0017] The invention proposes a personalized design of a RF coil array for MR imaging-guided surgical procedures. The design of the RF coil array, i.e. the sizes, shapes, and positions of the RF antennae, is based on the anatomy of the portion of the patient's body to be treated and on the surgery plan. The diagnostic image data, which comprise X-ray images, CT images, and/or MR images, is acquired pre-operatively in a first step. Anatomic models may be created on the basis of this diagnostic image data, which enable localization, targeting, and visualization of the 3D anatomy of the patient's body portion. In a second step, pre-operative planning is performed on the basis of the acquired diagnostic image data in order to define the interventional field and to optimize the access strategies. Finally, the design of the RF coil array is derived from the results of the surgery planning. The sizes, shapes and/or positions of one or more RF antennae on the substrate is automatically computed, thereby optimizing the signal-to-noise ratio of the MR signals acquired intra-operatively from the interventional field.

[0018] The substrate, on which the one or more RF antennae are arranged, is adapted to the shape of the patient's body, so that the RF coil array can be placed firmly, in close proximity, and in a well-defined position on the patient's body during the surgical invention. Preferably, both the shape of the substrate and the position of the substrate on the patient's body are derived from the previously acquired diagnostic image data and from the planning results.

[0019] According to a preferred embodiment of the invention, an access path to the interventional field is further determined during the step of planning the intervention, wherein the one or more RF antennae are arranged on the substrate in such a manner that the signal-to-noise ratio of MR signal acquisition from the interventional field and from the access path is optimized. In this embodiment, the optimization criteria determining the design of the RF coil array are extended so as to ensure the acquisition of high-quality MR images not only from the interventional field itself, i.e. the target region of the intervention, but also from the access path, which the surgeon takes to reach the lesion to be treated. Acquisition of high-quality MR images throughout the complete intervention is thus achieved.

[0020] According to a further preferred embodiment of the invention, one or more apertures are provided on the substrate in such a manner that the access path is kept clear when the substrate is attached to the patient's body. The size, the shape, and the locations of apertures in the substrate, via which the surgeon accesses the patient's body portion, are derived from the pre-operatively acquired diagnostic image data and from the results of the surgery plan according to this embodiment of the invention. Preferably, the RF antennae are arranged on the substrate at a pre-determined minimum distance from the interventional field and/or from the access path. This ensures that the interventional field is freely accessible for the surgeon. Furthermore, interferences between the RF antennae and the surgical instruments are avoided.

[0021] This means that a RF electromagnetic field simulation is performed in order to automatically determine the optimum sizes, shapes, and positions of the RF antennae in order to optimize the signal-to-noise ratio for MR signals acquired from the interventional field and/or from the access path. As explained above, this optimization may be constrained by the provision of one or more apertures on the substrate, which have to be kept clear from the RF antennae in order to enable access to the patient's body during surgery.

[0022] In yet another preferred embodiment of the invention, the final design of the personalized RF coil array is transferred to a rapid prototyping facility, where the personalized RF coil array is fabricated. After the fabrication step the RF coil array is ready to be used for the planned surgical intervention.

[0023] The method of the invention may further comprise the step of arranging electronic components for RF signal transmission and/or reception via the RF antennae on the substrate. Such electronic components may be, for example, RF connectors for connecting RF cables to the individual antennae, RF tuning and/or matching networks, or RF pre-amplifiers directly connected to the RF antennae. Also these electronic components may be fabricated (at least in part) by means of rapid prototyping. Per se known techniques for generating printed circuit boards and associated components by means of rapid prototyping can be used for this purpose. Further discrete electronic components, which cannot be manufactured by rapid prototyping methods, can be assembled and integrated into the personalized RF coil array in a separate manufacturing step.

[0024] In a possible embodiment of the invention, the RF antennae, which are arranged on the substrate of the personalized RF coil array, are standardized RF coil modules. The use of standardized and pre-fabricated RF coil modules in the personalized RF coil array of the invention facilitates the manufacturing process. The individual standardized RF coil modules are positioned on the substrate and/or interconnected such that the signal-to-noise ratio for MR signals acquired from the interventional field and/or from the access path is optimized.

BRIEF DESCRIPTION OF THE DRAWINGS



[0025] The enclosed drawings disclose preferred embodiments of the present invention. It should be understood, however, that the drawings are designed for the purpose of illustration only and not as a definition of the limits of the invention. In the drawings:
Fig. 1
schematically shows a MR device including a personalized RF coil array according to the invention;
Fig. 2
shows the RF coil array of Figure 1 in more detail.;
Fig. 3
shows another embodiment of the personalized RF coil array according to the invention.

DETAILED DESCRIPTION OF EMBODIMENTS



[0026] With reference to Figure 1, a MR device 1 is shown. The device comprises superconducting or resistive main magnet coils 2 such that a substantially uniform, temporally constant main magnetic field Bo is created along a z-axis through an examination volume. The device further comprises a set of (1st, 2nd, and - where applicable - 3rd order) shimming coils 2', wherein the current flow through the individual shimming coils of the set 2' is controllable for the purpose of minimizing Bo deviations within the examination volume.

[0027] A magnetic resonance generation and manipulation system applies a series of RF pulses and switched magnetic field gradients to invert or excite nuclear magnetic spins, induce magnetic resonance, refocus magnetic resonance, manipulate magnetic resonance, spatially and otherwise encode the magnetic resonance, saturate spins, and the like to perform MR imaging.

[0028] Most specifically, a gradient pulse amplifier 3 applies current pulses to selected ones of whole-body gradient coils 4, 5 and 6 along x, y and z-axes of the examination volume. A digital RF frequency transmitter 7 transmits RF pulses or pulse packets, via a send-/receive switch 8, to a -body RF coil 9 to transmit RF pulses into the examination volume. A typical MR imaging sequence is composed of a packet of RF pulse segments of short duration which taken together with each other and any applied magnetic field gradients achieve a selected manipulation of nuclear magnetic resonance. The RF pulses are used to saturate, excite resonance, invert magnetization, refocus resonance, or manipulate resonance and select a portion of a body 10 positioned in the examination volume. The MR signals are also picked up by the body RF coil 9.

[0029] For intra-operative generation of MR images of the head region of the body 10, for example by means of parallel imaging, a set of local array RF antennae (coils) 11, 12, 13 are placed on a mask 19, which constitutes a substrate adapted to the patient's head anatomy within the meaning of the invention. The RF coils 11, 12, 13 are positioned contiguous to the head region selected for imaging. Hence, high-quality MR images can be acquired, for example, during brain surgery. The array coils 11, 12, 13 can be used to receive MR signals induced by body-coil RF transmissions.

[0030] The resultant MR signals are picked up by the body RF coil 9 and/or by the array RF coils 11, 12, 13 and demodulated by a receiver 14, preferably including a pre-amplifier (not shown). The receiver 14 is connected to the RF coils 9, 11, 12 and 13 via send-/receive switch 8.

[0031] A host computer 15 controls the current flow through the shimming coils 2' as well as the gradient pulse amplifier 3 and the transmitter 7 to generate any of a plurality of MR imaging sequences, such as echo planar imaging (EPI), echo volume imaging, gradient and spin echo imaging, fast spin echo imaging, and the like. For the selected sequence, the receiver 14 receives a single or a plurality of MR data lines in rapid succession following each RF excitation pulse. A data acquisition system 16 performs analog-to-digital conversion of the received signals and converts each MR data line to a digital format suitable for further processing. In modern MR devices the data acquisition system 16 is a separate computer which is specialized in acquisition of raw image data.

[0032] Ultimately, the digital raw image data is reconstructed into an image representation by a reconstruction processor 17 which applies a Fourier transform or other appropriate reconstruction algorithms, such like SENSE or GRAPPA. The MR image may represent a planar slice through the patient, an array of parallel planar slices, a three-dimensional volume, or the like. The image is then stored in an image memory where it may be accessed for converting slices, projections, or other portions of the image representation into appropriate format for visualization, for example via a video monitor 18 which provides a human-readable display of the resultant MR image.

[0033] Figure 2 shows the personalized RF coil array of the invention in more detail. As can be seen in Figure 2, the substrate 19 is a mask (fabricated, for example, from a suitable plastic material) which is adapted to the shape of the patient's head. The mask 19 comprises apertures for the patient's eyes, mouth and nose. RF coils 11, 12, 13 are arranged on the mask 19 in such a manner that the signal-to-noise ratio of MR signals acquired via the RF coils 11, 12, 13 from an interventional field within the patient's brain is optimized. The personalized RF coil array shown in Figure 2 further comprises an aperture at the planned site for craniotomy to allow the surgeon to access the skull and brain. The corresponding access path is indicated by arrow 20 in Figure 2. The personalized RF coil array is designed and manufactured in an automated fashion by means of rapid prototyping. Therein, the sizes, shapes, and positions of the RF coils 11, 12, and 13 are computed by means of simulation of electromagnetic field distributions in order to optimize the signal-to-noise ratio taking into account the interventional field and access path resulting from the planning of the intervention. The necessary apertures of the mask 19 are used as constraints in the optimization procedure.

[0034] Figure 3 illustrates an embodiment of the invention, in which standardized and interconnectible RF coil modules are used. The coil modules 21 are arranged on the mask 19 in accordance with the above-described optimization criteria. The interconnected RF coil modules 21 are connected via cable connections to a RF unit 22 comprising, for example, a RF pre-amplifier.


Claims

1. Method of establishing a personalized RF coil array for use in a MR imaging guided surgical intervention on a portion of a patient's body, the method comprising:

- acquiring diagnostic image data reflecting the anatomy of the portion of the patient's body (10), the diagnostic image data comprising X-ray, CT and/or MR images;

- determining an interventional field within the portion of the patient's body (10) by planning the surgical intervention on the basis of the diagnostic image data;

- providing a substrate (19) for accommodating RF antennae (11, 12, 13), the substrate being adapted to the shape of the patient's body (10), so that the RF antennae (11, 12, 13) are placed firmly, in close proximity, and in a well-defined position on the patient's body (10) during the surgical intervention;

characterized by the method further comprising:

- simulating, on the basis of the diagnostic image data, a RF electromagnetic field distribution during the MR imaging guided surgical intervention to compute sizes, shapes and positions of the RF antennae (11, 12, 13) on the substrate (19) which optimize the signal-to-noise ratio of MR signal acquisition from the interventional field; and

- arranging the RF antennae (11, 12, 13) on the substrate (19) in accordance with the computed sizes, shapes and positions to establish the personalized RF coil array.


 
2. Method of claim 1, wherein planning the surgical intervention further comprises determining an access path (20) to the interventional field, wherein the sizes, shapes and/or positions of the RF antennae (11, 12, 13) are computed to optimize the signal-to-noise ratio of MR signal acquisition from the interventional field and from the access path (20).
 
3. Method of claim 2, further comprising providing one or more apertures on the substrate (19) to keep the access path (20) clear when the substrate (19) is attached to the patient's body (10) during the surgical intervention.
 
4. Method of claim 2 or 3, wherein the RF antennae (11, 12, 13) are arranged on the substrate (19) at a pre-determined minimum distance from the interventional field and/or the access path (20).
 
5. Method of any one of claims 1-4, wherein the MR imaging guided surgical intervention is perfonned on a head region of the patient's body (10), wherein the substrate is constituted by a mask (19) adapted to a shape of the patient's head.
 
6. Method of any one of claims 1-5, wherein the personalized RF coil array, which comprises the substrate (19) and the RF antennae (11, 12, 13) arranged on the substrate (19), is manufactured by means of rapid prototyping.
 
7. Method of any one of claims 1-6, further comprising arranging electronic components for RF signal transmission and/or reception via the RF antennae (11, 12, 13) on the substrate (19).
 
8. Method of any one of claims 1-7, wherein the RF antennae (11, 12, 13) are standardized RF coil modules (21).
 


Ansprüche

1. Verfahren zum Festlegen eines personalisierten RF-Spulenarrays zur Verwendung in einer MR-bildgebungsgeführten chirurgischen Intervention an einem Abschnitt des Körpers eines Patienten, wobei das Verfahren umfasst:

- Erfassen von Diagnosebilddaten, die die Anatomie des Körperabschnitts des Patienten (10) widerspiegeln, wobei die Diagnosebilddaten X-Strahlen-, CT- und/oder MR-Bilder umfassen;

- Bestimmen eines Interventionsfeldes innerhalb des Körperabschnitts des Patienten (10) durch Planen der chirurgischen Intervention auf der Grundlage der Diagnosebilddaten;

- Bereitstellen eines Substrats (19) zur Aufnahme von RF-Antennen (11, 12, 13), wobei das Substrat an die Form des Körpers des Patienten (10) angepasst ist, so dass die RF-Antennen (11, 12, 13) fest, in unmittelbarer Nähe und in einer genau definierten Position am Körper des Patienten (10) während der chirurgischen Intervention platziert sind;

dadurch gekennzeichnet, dass das Verfahren zudem umfasst:

- Simulieren einer Verteilung des elektromagnetischen RF-Feldes während der MR-bildgebungsgeführten chirurgischen Intervention auf der Grundlage der Diagnosebilddaten, um Größen, Formen und Positionen der RF-Antennen (11, 12, 13) auf dem Substrat (19) zu berechnen, die das Signal-Rausch-Verhältnis der MR-Signalerfassung aus dem Interventionsfeld optimieren; und

- Anordnen der RF-Antennen (11, 12, 13) auf dem Substrat (19) gemäß den berechneten Größen, Formen und Positionen, um das personalisierte RF-Spulenarray festzulegen.


 
2. Verfahren nach Anspruch 1, wobei die Planung der chirurgischen Intervention zudem das Bestimmen eines Zugangspfades (20) zu dem Interventionsfeld umfasst, wobei die Größen, Formen und/oder Positionen der RF-Antennen (11, 12, 13) berechnet werden, um das Signal-Rausch-Verhältnis der MR-Signalerfassung aus dem Interventionsfeld und aus dem Zugangspfad (20) zu optimieren.
 
3. Verfahren nach Anspruch 2, zudem umfassend das Bereitstellen einer oder mehrerer Öffnungen auf dem Substrat (19), um den Zugangspfad (20) frei zu halten, wenn das Substrat (19) während der chirurgischen Intervention am Körper des Patienten (10) befestigt ist.
 
4. Verfahren nach Anspruch 2 oder 3, wobei die RF-Antennen (11, 12, 13) auf dem Substrat (19) in einem vorbestimmten Mindestabstand vom Interventionsfeld und/oder dem Zugangspfad (20) angeordnet sind.
 
5. Verfahren nach einem der Ansprüche 1-4, wobei die MR-bildgebungsgeführte chirurgische Intervention an einem Kopfbereich des Körpers des Patienten (10) durchgeführt wird, wobei das Substrat aus einer Maske (19) besteht, die an eine Form des Kopfes des Patienten angepasst ist.
 
6. Verfahren nach einem der Ansprüche 1-5, wobei das personalisierte RF-Spulenarray, das das Substrat (19) und die auf dem Substrat (19) angeordneten RF-Antennen (11, 12, 13) umfasst, mittels Rapid Prototyping hergestellt wird.
 
7. Verfahren nach einem der Ansprüche 1-6, zudem umfassend das Anordnen elektronischer Komponenten zum Senden und/oder Empfangen von RF-Signalen über die RF-Antennen (11, 12, 13) auf dem Substrat (19).
 
8. Verfahren nach einem der Ansprüche 1-7, wobei die RF-Antennen (11, 12, 13) standardisierte RF-Spulenmodule (21) sind.
 


Revendications

1. Procédé d'établissement d'un réseau de bobines RF personnalisé destiné à être utilisé dans une intervention chirurgicale guidée par imagerie par résonance magnétique sur une partie du corps d'un patient, le procédé comprenant :

- acquérir des données d'images de diagnostic reflétant l'anatomie de la partie du corps du patient (10), les données d'images de diagnostic comprenant des images par rayons X, par tomodensitométrie et/ou par résonance magnétique ;

- déterminer un champ d'intervention à l'intérieur de la partie du corps du patient (10) en planifiant l'intervention chirurgicale sur la base des données d'images de diagnostic ;

- fournir un substrat (19) pour accueillir des antennes RF (11, 12, 13), le substrat étant adapté à la forme du corps du patient (10), de sorte que les antennes RF (11, 12, 13) soient placées fermement, à proximité immédiate et dans une position bien définie sur le corps du patient (10) pendant l'intervention chirurgicale ;

caractérisé en ce que le procédé comprend de plus :

- simuler, sur la base des données d'images de diagnostic, une distribution de champ électromagnétique RF pendant l'intervention chirurgicale guidée par imagerie par résonance magnétique pour calculer les dimensions, les formes et les positions des antennes RF (11, 12, 13) sur le substrat (19) qui optimisent le rapport signal/bruit de l'acquisition du signal de résonance magnétique à partir du champ d'intervention ; et

- disposer les antennes RF (11, 12, 13) sur le substrat (19) en fonction des dimensions, des formes et des positions calculées pour établir le réseau de bobines RF personnalisé.


 
2. Procédé selon la revendication 1, dans lequel la planification de l'intervention chirurgicale comprend de plus la détermination d'un chemin d'accès (20) au champ d'intervention, dans lequel les dimensions, les formes et/ou les positions des antennes RF (11, 12, 13) sont calculées pour optimiser le rapport signal/bruit de l'acquisition du signal de résonance magnétique à partir du champ d'intervention et du chemin d'accès (20).
 
3. Procédé selon la revendication 2, comprenant de plus le fait de prévoir une ou plusieurs ouvertures sur le substrat (19) pour maintenir le chemin d'accès (20) dégagé lorsque le substrat (19) est fixé au corps du patient (10) pendant l'intervention chirurgicale.
 
4. Procédé selon la revendication 2 ou 3, dans lequel les antennes RF (11, 12, 13) sont disposées sur le substrat (19) à une distance minimale prédéterminée du champ d'intervention et/ou du chemin d'accès (20).
 
5. Procédé selon l'une quelconque des revendications 1-4, dans lequel l'intervention chirurgicale guidée par imagerie par résonance magnétique est effectuée sur une région de la tête du corps du patient (10), dans lequel le substrat est constitué par un masque (19) adapté à une forme de la tête du patient.
 
6. Procédé selon l'une quelconque des revendications 1-5, dans lequel le réseau de bobines RF personnalisé, comprenant le substrat (19) et les antennes RF (11, 12, 13) disposées sur le substrat (19), est fabriqué au moyen d'un prototypage rapide.
 
7. Procédé selon l'une quelconque des revendications 1-6, comprenant de plus la disposition de composants électroniques pour la transmission et/ou la réception de signaux RF par l'intermédiaire des antennes RF (11, 12, 13) sur le substrat (19).
 
8. Procédé selon l'une quelconque des revendications 1-7, dans lequel les antennes RF (11, 12, 13) sont des modules de bobines RF standardisés (21).
 




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Cited references

REFERENCES CITED IN THE DESCRIPTION



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Patent documents cited in the description




Non-patent literature cited in the description