EP3468665A1 - Système de libération pour thérapie par particules - Google Patents

Système de libération pour thérapie par particules

Info

Publication number
EP3468665A1
EP3468665A1 EP17730556.2A EP17730556A EP3468665A1 EP 3468665 A1 EP3468665 A1 EP 3468665A1 EP 17730556 A EP17730556 A EP 17730556A EP 3468665 A1 EP3468665 A1 EP 3468665A1
Authority
EP
European Patent Office
Prior art keywords
particle
support structure
delivery system
therapy delivery
particle therapy
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP17730556.2A
Other languages
German (de)
English (en)
Inventor
Graeme Burt
Robert APSIMON
Hywel OWEN
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Lancaster University Business Enterprises Ltd
Original Assignee
Lancaster University Business Enterprises Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Lancaster University Business Enterprises Ltd filed Critical Lancaster University Business Enterprises Ltd
Publication of EP3468665A1 publication Critical patent/EP3468665A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1077—Beam delivery systems
    • A61N5/1081—Rotating beam systems with a specific mechanical construction, e.g. gantries
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1077—Beam delivery systems
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H13/00—Magnetic resonance accelerators; Cyclotrons
    • H05H13/10—Accelerators comprising one or more linear accelerating sections and bending magnets or the like to return the charged particles in a trajectory parallel to the first accelerating section, e.g. microtrons or rhodotrons
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H7/00—Details of devices of the types covered by groups H05H9/00, H05H11/00, H05H13/00
    • H05H7/001—Arrangements for beam delivery or irradiation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
    • A61N2005/1087—Ions; Protons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1092—Details
    • A61N2005/1094—Shielding, protecting against radiation
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H7/00—Details of devices of the types covered by groups H05H9/00, H05H11/00, H05H13/00
    • H05H7/001—Arrangements for beam delivery or irradiation
    • H05H2007/002—Arrangements for beam delivery or irradiation for modifying beam trajectory, e.g. gantries
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H2277/00—Applications of particle accelerators
    • H05H2277/10—Medical devices
    • H05H2277/11—Radiotherapy

Definitions

  • the present invention relates to a particle therapy delivery system for delivering particles to a patient.
  • Radiotherapy is one of the common forms of modern cancer treatment, where a tumour is irradiated by photons or charged particles in order to kill cancer cells.
  • Proton and ion beams deposit most of their energy in tissue over a small depth range known as the Bragg peak. This makes proton and ion therapy
  • Proton therapy is typically performed with beam currents of the order of nano- amperes (nA) with beam energies in the range of 60 to 250 MeV.
  • protons may be used for imaging because the Bragg peak occurs after the protons pass through the patient.
  • proton beams for imaging require beam currents of the order of pico-amperes (pA) and energies around 350 MeV.
  • pA pico-amperes
  • other ion species may be used with lower currents and higher energies than protons. For example, for carbon ions, beam energies of 1 .5 to 5 GeV (125 to 420 MeV/u) and currents below 1 nA are suitable.
  • WO2015/071430 A1 outlines a design for a single room ion therapy gantry. This design has a synchrotron mounted on a rotating gantry in order to produce a bunched ion beam at variable energy which can irradiate the target from all directions around the patient. However, this design is still relatively large and expensive. Synchrotrons require pulsed magnets for injection and extraction, each of which typically comprise at least one kicker magnet that turns on and off rapidly to perform the injection or extraction. Septum magnets may also be employed. The minimum diameter of synchrotrons is determined in part by the limitations on these pulsed magnets; hence a gantry incorporating a synchrotron has a minimum diameter of around 7 metres.
  • a particle therapy delivery system comprising a support structure defining at least a partial enclosure within which a patient is positioned in use, and a particle delivery line for delivering particles to a patient, wherein the particle delivery line comprises at least one linear particle accelerator mounted to the support structure such that particles travelling along the particle delivery line, in use, complete at least one revolution about an axis of the support structure.
  • the particle therapy system according to the first aspect of the present invention is advantageous principally as the at least one linear particle accelerator is mounted to the support structure such that particles travelling along the particle delivery line, in use, complete at least one revolution about an axis of the support structure.
  • this arrangement may enable a more compact arrangement than known arrangements in which linear particle accelerators are mounted to gantries, without the use of an expensive synchrotron.
  • the present invention may not require pulsed magnets such as those required in a synchrotron, and instead the present invention may utilise static magnetic fields.
  • the static magnetic fields employed in the present invention may be made stronger than is possible for pulsed magnets.
  • the radius of curvature of static magnets may therefore be smaller, and hence the diameter of the support structure may be reduced relative to prior art disclosures which utilise
  • linear particle accelerator may allow the energy of particles to be delivered to a patient to be varied pulse-to-pulse within about 1 millisecond for a pulse width typically up to 5 microseconds and a repetition rate of typically up to 500 Hz.
  • circular accelerators typically require 10s of milliseconds to adjust energy because bending magnets or mechanical degraders must be adjusted accordingly.
  • the relatively high rate at which the particle energy can be varied may allow for combined treatment and imaging within a single system.
  • Use of a linear particle accelerator relative to a circular accelerator for example a synchrotron, may also provide a relatively higher dose rate, which may allow for a higher patient throughput.
  • Linear particle accelerators are commonly referred to as "linacs", and it will be understood that the two terms are used interchangeably herein.
  • the portion of the particle delivery line which comprises the at least one linac may be referred to as a mounted portion of the beam delivery line.
  • the at least one linear particle accelerator mounted to the support structure such that particles travelling along the particle delivery line, in use, complete a partial revolution, one revolution, or a plurality of revolutions about an axis of the support structure.
  • the axis of the support structure may comprise an axis which passes through a patient when a patient is positioned in the at least a partial enclosure in use.
  • the axis of the support structure may comprise a central axis of the support structure, for example a central longitudinal axis of the support structure.
  • the support structure may be rotatable about a patient in use, and the axis of the support structure may comprise an axis of rotation of the support structure, for example an axis about which the support structure is rotatable.
  • the support structure may comprise at least one bearing for facilitating rotation of the support structure in use.
  • the support structure may comprise a gantry, for example a rotatable gantry.
  • the support structure may have a substantially cylindrical global form, and may have a hollow interior within which a patient is positioned in use.
  • the support structure may comprise a substantially circular or annular cross-section.
  • the support structure may be substantially circular or annular in form when viewed along the direction of a central longitudinal axis of the support structure.
  • the support structure may comprise a curved outer surface, for example a continuously curved outer surface such that the outer surface defines a cylinder, or other surface of revolution.
  • the support structure may have a diameter of at most 1 m, at most 2m, at most 3m, at most 4m, or at most 5m.
  • the minimum achievable diameter for the support structure of the present invention may be approximately one metre, however clinical specifications typically require the beam nozzle at the end of the final bending section to be at least two metres away from the patient. Therefore the diameter of the support structure of the present invention would likely be limited by clinical specifications rather than physical limitations.
  • the mounted portion of the particle delivery line may be mounted to the support structure such that particles travelling along the particle delivery line in use travel at least 180 degrees about an axis of the support structure.
  • the mounted portion of the particle delivery line may be mounted to the support structure such that particles travelling along the particle delivery line in use complete at least one revolution about the support structure, for example about the outer surface of the support structure.
  • the mounted portion of the particle delivery line may be mounted to the support structure such that particles travelling along the particle delivery line in use pass around at least one circumference of the support structure.
  • the particles may comprise charged particles, for example ions or protons.
  • the particles may comprise an ion beam or proton beam, or other charged particle.
  • the particle delivery line may comprise at least one guiding device for altering the path of particles travelling along the particle delivery line in use.
  • the at least one guiding device may be configured to produce an electromagnetic field which alters the path of particles travelling along the particle delivery line in use, for example an electromagnetic field which bends the path of particles travelling along the particle delivery line in use.
  • the at least one guiding device may be configured to produce an electromagnetic field which causes particles travelling along the particle delivery line in use to complete at least one revolution about an axis of the support structure.
  • the at least one guiding device may be configured to produce a constant electromagnetic field in use, for example a fixed strength and/or time dependent electromagnetic field.
  • the electromagnetic field produced by the at least one guiding device may be alterable when the particle therapy delivery system is not in operation and/or between pulses of particles delivered by the particle therapy delivery system.
  • the at least one guiding device may be configured to produce a constant electromagnetic field for a pre-determined period of time, for example a period of time corresponding to the period of time between pulses of particles delivered to a patient in use.
  • the at least one guiding device may comprise a magnet, for example an electromagnet.
  • the at least one guiding device may comprise a superconducting magnet, for example a superconducting electromagnet.
  • the at least one guiding device may comprise a magnet of fixed field strength, or may comprise a magnet of variable field strength.
  • the at least one guiding device may comprise an achromatic magnetic system, for example a magnetic system configured to bend particles to produce a particle beam comprising particles with a plurality of kinetic energies but with substantially the same direction..
  • the at least one guiding device may be configured to receive particles from and/or transmit particles to the at least one linac in use.
  • the at least one guiding device may be mounted to the support structure, for example mounted to the support structure upstream and/or downstream of the linac in the particle delivery line.
  • the mounted portion of the particle delivery line may be mounted to the support structure in a substantially helical manner.
  • at least a portion of the particle delivery line may be mounted to the support structure such that particles travelling along the particle delivery line in use travel along a substantially helical path.
  • the mounted portion of the particle delivery line may be mounted to the support structure in a substantially helical manner.
  • At least a portion of the particle delivery line may be wrapped around the support structure in a substantially helical manner.
  • At least a portion of the particle delivery line may be mounted to the support structure in a substantially axial manner.
  • at least a portion of the particle delivery line may be mounted to the support structure such that particles travelling along the particle delivery line in use travel along a path substantially parallel to a longitudinal axis of the support structure.
  • the mounted portion of the particle delivery line may be mounted to the support structure in a substantially axial manner.
  • the at least one linac may be mounted substantially parallel relative to an outer surface of the support structure.
  • the at least one linac may be mounted to the support structure such that a longitudinal axis of the at least one linac extends in a direction having a component along a longitudinal axis and a transverse axis of the support structure.
  • the at least one linac may be mounted to the support structure such that the at least one linac is at most 10cm, 20cm, 30cm, 40cm, or 50cm away from an outer surface of the support structure.
  • the at least one guiding device may be mounted substantially parallel relative to an outer surface of the support structure.
  • the at least one guiding device may be mounted to the support structure such that the at least one guiding device is at most 10cm, 20cm, 30cm, 40cm, or 50cm away from an outer surface of the support structure.
  • the at least one guiding device may be shaped to conform substantially to the shape of the support structure, for example an outer surface of the support structure. Where the support structure comprises a curved outer surface, the at least one guiding device may be curved in form. For example, at least a portion of the at least one guiding device may be curved in form. The curvature of the at least one guiding device may correspond substantially to the curvature of the outer surface of the support structure.
  • the particle delivery line may comprise a plurality of linacs, for example a plurality of linacs spaced apart from one another along the length of the particle delivery line. At least one guiding device may be located between adjacent linacs.
  • the plurality of linacs may be mounted to the support structure such that particles travelling along the particle delivery line in use complete at least one revolution about an axis of the support structure.
  • the plurality of linacs may be mounted to the support structure such that the plurality of linacs extend substantially about the support structure, for example substantially about the circumference of the support structure.
  • the combination of the plurality of linacs and a plurality of guiding devices may extend about substantially the entirety of the support structure, for example substantially the entirety of the circumference of the support structure.
  • the plurality of linacs may be mounted to the support structure in a substantially helical manner, for example such that particles travelling along the particle delivery line in use travel along a substantially helical path.
  • the combination of the plurality of linacs and a plurality of guiding devices may be mounted to the support structure in a substantially helical manner, for example such that the particles travelling along the particle delivery line in use travel along a substantially helical path.
  • the particle therapy delivery system may comprise a particle delivery device for delivering particles from the particle delivery line to a patient.
  • the particle delivery device may be located at an end of the particle delivery line, for example a point along the particle delivery line where particles travelling along the particle delivery line have reached a pre-determined desired energy for delivery to a patient.
  • the particle delivery device may be mounted to the support structure such that the particle delivery device extends between the particle delivery line and the at least a partial enclosure.
  • the particle delivery device may comprise a guiding device, for example a waveguide, or plurality of guiding devices, mounted to the particle delivery line.
  • the particle therapy delivery system may comprise a pre-accelerator for providing pre-accelerated particles to the particle delivery line.
  • the pre-accelerator may be mounted to the support structure, or may be spaced apart from the support structure and connected to the particle delivery line by a pre-accelerator transfer line.
  • the pre-accelerator may comprise a circular particle accelerator or a linear particle accelerator.
  • the pre-accelerator may comprise a cyclotron or synchrotron.
  • the particle therapy delivery system may comprise a bypass particle line for bypassing the particle delivery line.
  • the bypass particle line may comprise a different structure to the particle delivery line, such that particles travelling along the bypass particle line in use have a different energy to particles travelling along the particle delivery line in use. This may be beneficial as an operator of the particle therapy delivery system can choose which energy of particle to deliver to a patient, and thus the operator may switch rapidly between imaging and treatment of a patient within a single system.
  • the pre-accelerator may comprise a plurality of outlet ports for extraction of pre- accelerated particles. At least one of the plurality of outlet ports may be in communication with the particle delivery line. At least one of the plurality of outlet ports may be in communication with the particle bypass line. The particle delivery line and the particle bypass line may be in communication with different outlet ports of the pre-accelerator.
  • the particle therapy delivery system may comprise at least one radiation shield for shielding a patient from radiation during acceleration of particles by the at least one linac and/or during acceleration of particles by the pre-accelerator. The at least one radiation shield may be located in a region of the at least one linac and/or the pre-accelerator.
  • the at least one radiation shield may be mounted to the support structure, for example in a region of the at least one linac and/or the pre-accelerator.
  • the at least one radiation shield may be mounted within the at least a partial enclosure.
  • Figure 1 is a schematic perspective view of a first embodiment of a particle therapy delivery system according to the present invention
  • Figure 2 is a schematic left side view of the particle therapy delivery system of Figure 1 ;
  • Figure 3 is a schematic front view of the particle therapy delivery system of Figure 1 ;
  • Figure 4 is a schematic aerial view of the particle therapy delivery system of Figure 1 ;
  • Figure 5 is a schematic rear view of the particle therapy delivery system of Figure 1 ;
  • Figure 6 is a schematic sectional view of a second embodiment of a particle therapy delivery system according to the present invention.
  • Figure 7 is a schematic perspective view of a third embodiment of a particle therapy delivery system according to the present invention.
  • Figure 8 is a schematic rear view of the particle therapy delivery system of Figure 7;
  • Figure 9 is a schematic right side view of the particle therapy delivery system of Figure 7.
  • a particle therapy delivery system according to a first embodiment of the present invention, generally designated 10, is shown schematically in Figures 1 to 5.
  • the particle therapy delivery system 10 comprises a rotatable gantry 12, a plurality of linear particle accelerators (linacs) 14, a plurality of achromatic bending magnet devices 16, a pre-accelerator 18, an injection line 20, and a delivery line 22.
  • linacs linear particle accelerators
  • achromatic bending magnet devices 16
  • pre-accelerator 18 an injection line 20
  • delivery line 22 a delivery line 22.
  • the rotatable gantry 12 is substantially cylindrical in form, and is hollow such that a patient 24 can be located within the interior of the rotatable gantry 1 2 in use.
  • the rotatable gantry 12 has front 26 and rear 28 legs which are attached to bearings 30 about which the rotatable gantry 12 rotates in use.
  • the rear of the rotatable gantry 12 has a support structure 32 which connects to a rear bearing 30.
  • Each of the plurality of linacs 14 is substantially the same, and in the present case each is formed of a number of radio frequency (RF) cavities, although it will be recognised that other types of linear acceleration device, for example based on dielectric or laser acceleration, may be used.
  • RF radio frequency
  • the RF cavities are typically 10 cm to 50 cm in length and can produce accelerating gradients ranging from 15 MV per metre to 60 MV per metre for medical proton linacs.
  • a linac 14 consists of more than one RF cavity
  • the region between cavities is typically 10 cm to 30 cm in length and may comprise one or more focussing magnets and/or other devices.
  • the focussing magnets are typically 1 cm to 5 cm in length and typically have an inner bore radius of 2 mm to 10 mm.
  • the achromatic bending magnet devices 16 may be similar to those disclosed in US 201 1 /0101236, which are superconducting bending magnets with focussing magnets integrated into the design to produce an achromatic bending section with an average bending radius of 60 cm.
  • the achromatic bending magnets 16 may be realised with normal conducting (resistive) magnet technology, however superconducting technology may allow for a more compact and lighter system. If superconducting magnets are used then cryogenic cooling may need to be provided to the achromatic bending magnet devices 16. This may be achieved either by mounting the cooling systems, pumps and other required components to the rotatable gantry 12 or by mounting them remotely via suitable cooling pipes.
  • the plurality of linacs 14 and the plurality of achromatic bending magnet devices 16 are mounted to the rotatable gantry 12 to form a helical particle delivery path, such that particles travel in a helical fashion in use.
  • the pre-accelerator 18 is mounted to a rear section of the rotatable gantry 12, and comprises a cyclotron.
  • the pre-accelerator 18 is connected to a first achromatic bending magnet device 16 via the injection line 20.
  • a last achromatic bending magnet device 16 is connected to the delivery line 22, which comprises a waveguide or other appropriate device for extracting and delivering particles to a patient in use.
  • a patient 24 is positioned inside the rotatable gantry 12 on a moveable table 34 which is operated by a control system and user interface.
  • the position of the patient 24 and of the rotatable gantry 12 is determined by a treatment plan.
  • the table 34 may move the patient 24 in all 3 dimensions within the rotating gantry 12 and may rotate the patient 24 to any orientation.
  • the pre-accelerator 18 produces an ion beam with energy 3 MeV or higher and beam current up to 1 imA or higher. From the pre-accelerator 18 the beam is directed into the entrance of the linac(s) 14 by the injection line 20, and the beam is accelerated to the required energy in the range of 65 MeV to 350 MeV. The beam is directed from each linac 14 into the next linac 14 using an achromatic bending magnet device 16. From the linacs 14, the beam is directed towards the patient 24 by the delivery line 22.
  • the delivery line 22 consists of two bendingmagnets, which may utilise achromatic bending devices such as DBAs (double-bend achromats).
  • the final deflecting region may also contain an energy selection system. Energy selection may also or alternatively be performed by collimation within the achromatic bending sections 16.
  • the beam delivery line 22 may comprise devices such as moveable collimators, to manipulate the beam profile to match the shape of the target. Furthermore, the beam delivery line 22 may include scanning magnets and/or focusing magnets to allow the beam to be scanned or the beam size to be varied during operation in accordance to the treatment plan.
  • the particle therapy delivery system 10 may be operated in accordance to a treatment plan for directing a proton or ion beam at a target region within a patient 24.
  • the aforementioned treatment plan is typically determined by a treatment planning system where information such as tumour type and/or size and/or location is used to determine beam parameters such as beam current, energy, size as well as the direction of beam incidence to the tumour. This information is then transferred to the gantry control system in order to determine the operational parameters of the particle therapy delivery system 10.
  • the beam current of the accelerated beam is typically of the order of nano-amps for treatment.
  • the final energy of the accelerated beam may be altered by shifting the
  • the desired energy may be set by an input device such as a user-operated control system and may be changed during operation of the system. Changes to the desired energy of the accelerated beam may also be achieved by changing the energy of the pre-accelerated beam by changing the settings of the pre-accelerator 18.
  • the particle therapy delivery system 10 provides all the benefits of a linac-driven ion delivery facility in a compact system, with no detriment to performance.
  • the rotating gantry 12 allows the target region of the patient to be imaged and/or treated from any azimuthal angle by the accelerated and/or a bypassed beam travelling radially or otherwise towards the centre of the gantry 12.
  • the target e.g. tumour
  • the target may be maintained in a fixed position during treatment and/or imaging and is irradiated from different directions to minimise damage to surrounding healthy tissue.
  • the target is typically positioned at the point where the accelerated and bypassed beams intersect with the gantry's axis of rotation; this point is defined as the isocentre and the gantry 12 is conventionally known as an isocentric gantry.
  • the directions from which the beam irradiates the target are determined as part of a treatment plan.
  • the rotating gantry 12 is rotatable through at least 360 degrees and may be rotated to any angle required.
  • the second embodiment of the particle therapy delivery system 100 is substantially the same as the first embodiment of the particle therapy delivery system 10, and differs only in the addition of a radiation shield 36.
  • the radiation shield 36 is mounted in the interior of the rotatable gantry 12, and is positioned to protect the patient 24 from radiation from particles accelerated by either the pre- accelerator 18 or the plurality of linacs 14 in use.
  • the third embodiment 200 is substantially the same as the first embodiment 10, and differs only in that the pre-accelerator has first 38 and second 40 outlet ports, the first outlet port 38 being connected to the injection line 20, and the second outlet port 40 being connected to the bypass line 42.
  • the bypass line 42 allows ions to be delivered to the patient 24, for example in two different energy ranges. This allows the operator to switch rapidly between imaging and treatment of a patient with a single system. Further ports may also be employed.

Abstract

Système de libération pour thérapie par particules (10) comprenant une structure de support (12) définissant au moins une enceinte partielle à l'intérieur de laquelle un patient est positionné en cours d'utilisation, et une conduite de libération de particules pour administrer des particules à un patient, où la structure de support (12) peut tourner autour d'un patient, lors de l'utilisation, et la conduite de libération de particules comprend au moins un accélérateur de particules linéaire (14) fixé sur la structure de support de sorte que les particules se déplaçant le long de la conduite de libération de particules, lors de l'utilisation, fassent au moins un tour complet autour d'un axe de la structure de support (12).
EP17730556.2A 2016-06-10 2017-06-09 Système de libération pour thérapie par particules Withdrawn EP3468665A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
GB1610146.1A GB2551330A (en) 2016-06-10 2016-06-10 Particle therapy delivery system
PCT/GB2017/051688 WO2017212290A1 (fr) 2016-06-10 2017-06-09 Système de libération pour thérapie par particules

Publications (1)

Publication Number Publication Date
EP3468665A1 true EP3468665A1 (fr) 2019-04-17

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EP17730556.2A Withdrawn EP3468665A1 (fr) 2016-06-10 2017-06-09 Système de libération pour thérapie par particules

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EP (1) EP3468665A1 (fr)
GB (1) GB2551330A (fr)
WO (1) WO2017212290A1 (fr)

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Publication number Priority date Publication date Assignee Title
US10880983B2 (en) 2017-05-03 2020-12-29 The General Hospital Corporation System and method for gantry-less particle therapy
JP7319846B2 (ja) * 2019-07-01 2023-08-02 株式会社日立製作所 粒子線治療システム
JP2021041005A (ja) * 2019-09-12 2021-03-18 株式会社日立製作所 粒子線照射システム及び粒子線照射施設

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US5382914A (en) * 1992-05-05 1995-01-17 Accsys Technology, Inc. Proton-beam therapy linac
FR2702663B1 (fr) * 1993-03-18 1995-04-28 Gen Electric Cgr Installation de protonthérapie.
DE4411171A1 (de) * 1994-03-30 1995-10-05 Siemens Ag Vorrichtung zur Bereitstellung eines Strahls aus geladenen Teilchen, der eine Achse auf einer diese schneidenden Zielgeraden anfliegt, sowie ihre Verwendung
IT1277909B1 (it) * 1995-08-09 1997-11-12 Enea Ente Nuove Tec Acceleratore lineare compatto per protoni da 5 e 200 mev per adroterapia
US9446263B2 (en) * 2013-03-15 2016-09-20 Viewray Technologies, Inc. Systems and methods for linear accelerator radiotherapy with magnetic resonance imaging
WO2015070865A1 (fr) * 2013-11-14 2015-05-21 Danfysik A/S Système de thérapie à particules

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GB2551330A (en) 2017-12-20
WO2017212290A1 (fr) 2017-12-14

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