CN109464752B - Neutron capture therapy system - Google Patents
Neutron capture therapy system Download PDFInfo
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- CN109464752B CN109464752B CN201710800921.XA CN201710800921A CN109464752B CN 109464752 B CN109464752 B CN 109464752B CN 201710800921 A CN201710800921 A CN 201710800921A CN 109464752 B CN109464752 B CN 109464752B
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N5/1028—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy using radiation sources applied onto the body
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
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- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1042—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head
- A61N5/1045—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head using a multi-leaf collimator, e.g. for intensity modulated radiation therapy or IMRT
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
- A61N5/1064—Monitoring, verifying, controlling systems and methods for adjusting radiation treatment in response to monitoring
- A61N5/1065—Beam adjustment
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- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N2005/1019—Sources therefor
- A61N2005/1022—Generators, e.g. X-ray tubes
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- 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
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- A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
- A61N2005/109—Neutrons
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
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- A61N2005/1092—Details
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- A—HUMAN NECESSITIES
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- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N2005/1092—Details
- A61N2005/1097—Means for immobilizing the patient
Abstract
The neutron capture treatment system comprises an accelerator, a beam transmission part and a neutron beam generation part, wherein the accelerator accelerates charged particles to generate a charged particle beam, the beam transmission part transmits the charged particle beam generated by the accelerator to the neutron beam generation part, the neutron beam generation part generates a neutron beam for treatment, and the beam transmission part comprises a shielding body for preventing neutrons and other radiation rays from leaking from the beam transmission part.
Description
Technical Field
The present invention relates to a radiation irradiation system, and more particularly, to a neutron capture therapy system.
Background
With the development of atomic science, radiation therapy such as cobalt sixty, linac, electron beam, etc. has become one of the main means for cancer therapy. However, the traditional photon or electron treatment is limited by the physical condition of the radioactive rays, and a large amount of normal tissues on the beam path can be damaged while killing tumor cells; in addition, due to the different sensitivity of tumor cells to radiation, traditional radiotherapy often has poor therapeutic effects on malignant tumors with relatively high radiation resistance (such as glioblastoma multiforme (glioblastoma multiforme) and melanoma (melanoma)).
In order to reduce radiation damage to normal tissue surrounding a tumor, the concept of target treatment in chemotherapy (chemotherapy) has been applied to radiotherapy; for tumor cells with high radiation resistance, radiation sources with high relative biological effects (relative biological effectiveness, RBE) such as proton therapy, heavy particle therapy, neutron capture therapy, etc. are also actively developed. The neutron capture treatment combines the two concepts, such as boron neutron capture treatment, and provides better cancer treatment selection than the traditional radioactive rays by means of the specific aggregation of boron-containing medicaments in tumor cells and the accurate neutron beam regulation.
Various radioactive rays, such as neutrons and photons with low to high energy, are generated in the radiotherapy process, and may cause different degrees of damage to normal tissues of a human body. Therefore, in the field of radiotherapy, it is an extremely important task to reduce radiation pollution to the external environment, medical staff or normal tissues of a patient while achieving effective treatment. Meanwhile, in the existing accelerator boron neutron capture treatment, a plurality of patients cannot be treated at the same time, or a plurality of irradiation chambers are unreasonably distributed, and the transmission path of the charged particle beam is long, so that loss is generated.
Therefore, a new solution is needed to solve the above-mentioned problems.
Disclosure of Invention
In order to solve the above-described problems, an aspect of the present invention provides a neutron capture therapy system including an accelerator that accelerates charged particles to generate a charged particle beam, a beam transmission section that transmits the charged particle beam generated by the accelerator to the neutron beam generation section that generates a therapeutic neutron beam, and a neutron beam generation section that includes a shield to prevent neutrons and other radiation from leaking from the beam transmission section.
Preferably, the neutron capture treatment system further comprises a treatment table, the neutron beam generating part comprises a target material, a beam shaping body and a collimator, the target material is arranged between the beam transmission part and the beam shaping body, the charged particle beam generated by the accelerator irradiates the target material through the beam transmission part and acts with the target material to generate neutrons, and the generated neutrons sequentially pass through the beam shaping body and the collimator to form a therapeutic neutron beam and irradiate to a patient on the treatment table.
Further, the beam shaper comprises a reflector, a retarder, a thermal neutron absorber, a radiation shield and a beam outlet, wherein the retarder retards neutrons generated by the target to an epithermal neutron energy region, the reflector surrounds the retarder and guides the deviated neutrons back to the retarder so as to improve the epithermal neutron beam intensity, the thermal neutron absorber is used for absorbing thermal neutrons so as to avoid excessive dose caused by shallow normal tissues during treatment, the radiation shield is arranged at the rear part of the reflector around the beam outlet and is used for shielding the leaked neutrons and photons so as to reduce the normal tissue dose of a non-irradiation region, the collimator is arranged at the rear part of the beam outlet and is used for converging neutron beams, and a radiation shielding device is arranged between a patient and the beam outlet and is used for shielding radiation of the beam coming from the beam outlet to normal tissues of the patient.
Further, the beam transmission part is provided with a vacuum tube for accelerating or transmitting the charged particle beam, the vacuum tube stretches into the beam shaping body along the charged particle beam direction and sequentially passes through the reflector and the retarder, and the target is arranged in the retarder and is positioned at the end part of the vacuum tube.
As another preferred aspect, the beam transfer unit includes a first transfer unit connected to the accelerator, a beam direction switch for switching a traveling direction of the charged particle beam, and a second transfer unit for transferring the charged particle beam to the neutron beam generating unit, and the shield is a shield case surrounding the beam direction switch.
Further, the beam direction switch comprises a first beam direction switch and a second beam direction switch, the beam transmission part further comprises a third transmission part connected with the first beam direction switch and the second beam direction switch, and the shielding cover is 2 cover bodies respectively surrounding the first beam direction switch and the second beam direction switch.
Still further, the first and second beam direction switches include a deflection electromagnet for deflecting a charged particle beam direction and a switching electromagnet for controlling a traveling direction of the charged particle beam, the boron neutron capture therapy system further includes a beam collector for performing output confirmation of the charged particle beam before therapy, the first or second beam direction switch is directed to the beam collector, the first, second, and third transfer sections include a beam adjustment section for the charged particle beam, and the second transfer section includes a current monitor and a charged particle beam scanning section. The number of the neutron beam generating parts is 3, the second transmission part comprises a fourth transmission part, a fifth transmission part and a sixth transmission part which respectively transmit the charged particle beams to the 3 neutron beam generating parts, the first transmission part is branched into the third transmission part and the fourth transmission part in the first beam direction switcher, and the third transmission part is branched into the fifth transmission part and the sixth transmission part in the second beam direction switcher.
Further, the boron neutron capture therapy system further includes a charged particle beam generation chamber housing the accelerator and at least a portion of the beam transport section, and an irradiation chamber in which the patient is undergoing therapy with neutron beam irradiation, at least a portion of the neutron beam generation section being embedded in a partition wall of the irradiation chamber and the charged particle beam generation chamber.
Still further, the charged particle beam generating chamber includes an accelerator chamber and a beam transport chamber, the first transport portion extending from the accelerator chamber to the beam transport chamber, the second transport portion extending from the beam transport chamber to the neutron beam generating portion, the beam direction switch and the shield being housed within the beam transport chamber.
The neutron capture therapy system of the present invention can prevent neutrons and other radiation from leaking from the beam transport section.
Drawings
FIG. 1 is a schematic diagram of a neutron capture therapy system according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a neutron capture treatment system layout in the XY plane according to an embodiment of the present invention;
fig. 3 is a schematic view of fig. 2 taken along the section A-A.
Detailed Description
Embodiments of the invention will be described in further detail below with reference to the drawings to enable those skilled in the art to practice the invention by reference to the description. An XYZ coordinate system (see fig. 2 and 3) in which the X axis is the direction of the charged particle beam P emitted from the accelerator, the Y axis is the direction perpendicular to the direction of the charged particle beam P emitted from the accelerator, and the Z axis is the direction perpendicular to the ground is set, and X, Y, Z is used for explaining the positional relationship of the components.
As shown in fig. 1, the neutron capture therapy system in the present embodiment is preferably a boron neutron capture therapy system 100, and the boron neutron capture therapy system 100 is a device for cancer treatment using boron neutron capture therapy. Boron neutron capture therapy treatment of cancer by irradiating a patient 200 injected with boron (B-10) with a neutron beam N, after the patient 200 takes or injects the boron (B-10) containing drug, the boron containing drug is selectively accumulated in tumor cells M, and then the boron (B-10) containing drug is utilized to have a characteristic of high capture cross section for thermal neutrons by 10 B(n,α) 7 Li neutron capture and nuclearCleavage reaction production 4 He (He) 7 Li two heavy charged particles. The average energy of the two charged particles is about 2.33MeV, the particles have high linear transfer (Linear Energy Transfer, LET) and short range characteristics, and the linear energy transfer and range of the alpha short particles are 150keV/μm and 8 μm respectively 7 The Li heavy-load particles are 175 keV/mum and 5 μm, and the total range of the two particles is approximately equal to one cell size, so that the radiation injury to organisms can be limited at the cell level, and the aim of killing tumor cells locally can be fulfilled on the premise of not causing too great injury to normal tissues.
The boron neutron capture therapy system 100 includes an accelerator 10, a beam transport section 20, a neutron beam generation section 30, and a therapy table 40. The accelerator 10 accelerates charged particles (e.g., protons, deuterons, etc.) to produce a charged particle beam P, such as a proton beam; a beam transmission unit 20 that transmits the charged particle beam P generated by the accelerator 10 to a neutron beam generation unit 30; the neutron beam generator 30 generates a therapeutic neutron beam N and irradiates the patient 200 on the treatment table 40.
The neutron beam generating section 30 includes a target T, a beam shaping body 31, and a collimator 32, and the charged particle beam P generated by the accelerator 10 is irradiated to the target T via the beam transmitting section 20 and reacts with the target T to generate neutrons, and the generated neutrons sequentially pass through the beam shaping body 31 and the collimator 32 to form a therapeutic neutron beam N and irradiate the therapeutic neutron beam N to the patient 200 on the therapeutic table 40. The target T is preferably a metal target. Suitable nuclear reactions are selected according to the required neutron yield and energy, the available energy and current of the accelerated charged particles, the physicochemical properties of the metal target, etc., and are usually discussed as 7 Li(p,n) 7 Be and Be 9 Be(p,n) 9 And B, performing an endothermic reaction. The energy threshold values of the two nuclear reactions are respectively 1.881MeV and 2.055MeV, because the ideal neutron source for boron neutron capture treatment is epithermal neutrons with the energy level of keV, theoretically if protons with the energy only slightly higher than the threshold value are used for bombarding a metal lithium target material, relatively low-energy neutrons can Be generated, the clinical treatment can Be realized without too much retarding treatment, however, the proton action cross section of the two targets of lithium metal (Li) and beryllium metal (Be) and the threshold energy is not high, so as to generate enough neutron flux, and the method is effectiveHigher energy protons are often selected to initiate nuclear reactions. The ideal target should have high neutron yield, a neutron energy distribution close to that of the epithermal neutron energy region (described in detail below), no too much intense penetrating radiation, safety, low cost, easy operation, and high temperature resistance, but practically no nuclear reaction meeting all the requirements can be found. The target T may also Be made of a metallic material other than Li, be, such as Ta or W, an alloy thereof, or the like, as is well known to those skilled in the art. The accelerator 10 may be a linear accelerator, a cyclotron, a synchrotron.
The beam shaping body 31 can adjust the beam quality of the neutron beam N generated by the action of the charged particle beam P and the target T, and the collimator 32 is used for converging the neutron beam N, so that the neutron beam N has high targeting property in the treatment process. The beam shaping body 31 further comprises a reflector 311, a retarder 312, a thermal neutron absorber 313, a radiation shielding 314 and a beam outlet 315, neutrons generated by the action of the charged particle beam P and the target T are made of a material with a large cross section for acting with fast neutrons and a small cross section for acting with fast neutrons, in this embodiment, the retarder 312 is made of a material with a large cross section for acting with fast neutrons, and the retarder 312 is made of a material with a small cross section for acting with fast neutrons, in addition to the therapeutic requirement for the ultrathermal neutrons, and the neutrons coming out of the target T need to be adjusted to the fast neutron energy region (0.5 eV-40 keV) via the retarder 312, because the fast neutron energy (> 40 keV) is reduced to the ultrathermal neutron energy region (0.5 eV-40 keV) and the thermal neutrons are reduced as much as possible, in order to avoid harm to operators or patients, in this embodiment, the retarder 312 is made of a material with a large cross section for acting with fast neutrons 2 O、AlF 3 、Fluental、CaF 2 、Li 2 CO 3 、MgF 2 And Al 2 O 3 At least one of them; the reflector 311 surrounds the retarder 312 and reflects neutrons diffused around through the retarder 312 back to the neutron beam N to improve the neutron utilization rate, and is made of a material having strong neutron reflection capability, in this embodiment, the reflector 311 is made of at least one of Pb or Ni; the rear part of the retarder 312 is provided with a thermal neutron absorber 313 made of a material having a large cross section for reacting with thermal neutrons, in this embodiment the thermal neutron absorber 313 is made of Li-6, and the thermal neutron absorber 313 is used for absorbing thermal neutrons passing through the retarder 312 toThe content of thermal neutrons in the neutron beam N is reduced, and excessive dose caused by the treatment and the shallow normal tissue is avoided; a radiation shield 314 is disposed at the rear of the reflector around the beam outlet 315 for shielding neutrons and photons leaking from portions outside the beam outlet 315, the material of the radiation shield 314 comprising at least one of a photon shielding material and a neutron shielding material, in this embodiment the material of the radiation shield 314 comprising a photon shielding material lead (Pb) and a neutron shielding material Polyethylene (PE). It will be appreciated that other configurations of beam shaping body 31 are possible, provided that the epithermal neutron beam required for treatment is obtained. The collimator 32 is disposed at the rear of the beam outlet 315, and the epithermal neutron beam exiting the collimator 32 irradiates the patient 200, is retarded to thermal neutrons after passing through the shallow normal tissue, and reaches the tumor cells M, it will be appreciated that the collimator 32 may be omitted or replaced by other structures, and the neutron beam exits from the beam outlet 315 to directly irradiate the patient 200. In this embodiment, the radiation shielding device 50 is further disposed between the patient 200 and the beam outlet 315 to shield the normal tissue of the patient from the radiation from the beam outlet 315, and it is understood that the radiation shielding device 50 may be omitted. The target T is disposed between the beam transmitting portion 20 and the beam shaping body 31, the beam transmitting portion 20 has a vacuum tube C for accelerating or transmitting the charged particle beam P, in this embodiment, the vacuum tube C extends into the beam shaping body 31 along the direction of the charged particle beam P and sequentially passes through the reflector 311 and the retarder 312, and the target T is disposed in the retarder 312 and at the end of the vacuum tube C, so as to obtain better neutron beam quality. It will be appreciated that the target may be arranged in other ways and may be movable relative to the accelerator or beam shaping body to facilitate changing targets or to allow the charged particle beam to act uniformly with the target.
Referring to fig. 2 and 3, the boron neutron capture therapy system 100 is disposed entirely in the space of the two floors L1 and L2, and the boron neutron capture therapy system 100 further includes an irradiation chamber 101 (101A, 101B, 101C) and a charged particle beam generation chamber 102, and the patient 200 on the treatment table 40 is subjected to the treatment irradiated with the neutron beam N in the irradiation chamber 101 (101A, 101B, 101C), and the charged particle beam generation chamber 102 accommodates the accelerator 10 and at least a part of the beam transmission section 20. The neutron beam generating sections 30 may have one or more to generate one or more therapeutic neutron beams N, and the beam transmitting section 20 may selectively transmit the charged particle beams P to one or more of the neutron beam generating sections 30 or simultaneously transmit the charged particle beams P to a plurality of the neutron beam generating sections 30, each of the neutron beam generating sections 30 corresponding to one of the irradiation chambers 101. In this embodiment, the number of neutron beam generating sections and irradiation chambers is 3, and the number of neutron beam generating sections 30A, 30B, and 30C and the number of irradiation chambers 101A, 101B, and 101C are respectively. The beam transmission unit 20 includes: a first transmission unit 21 connected to the accelerator 10; first and second beam direction switches 22, 23 for switching the traveling direction of the charged particle beam P; a second transmission unit 24 connected to the first and second beam direction switches 22 and 23; the third, fourth, and fifth transfer units 25A, 25B, and 25C transfer the charged particle beams P from the first beam direction switch 22 or the second beam direction switch 23 to the neutron beam generating units 30A, 30B, and 30C, respectively, and irradiate the generated neutron beams N to the patients in the irradiation chambers 101A, 101B, and 101C, respectively. The third transfer unit 25A is connected to the first beam direction switch 22 and the neutron beam generating unit 30A, the fourth transfer unit 25B is connected to the second beam direction switch 23 and the neutron beam generating unit 30B, and the fifth transfer unit 25C is connected to the second beam direction switch 23 and the neutron beam generating unit 30C. That is, the first transmission unit 21 branches into the second transmission unit 24 and the third transmission unit 25A in the first beam direction switch 22, and the second transmission unit 24 branches into the fourth transmission unit 25B and the fifth transmission unit 25C in the second beam direction switch 23. The first and second transfer units 21, 24 transfer in the X-axis direction, the third transfer unit 25A transfers in the Z-axis direction, the fourth and fifth transfer units 25B, 25C transfer in the XY plane and in the Y-shape with respect to the transfer directions of the first and second transfer units 21, 24, the neutron beam generating units 30A, 30B, 30C and the corresponding irradiation chambers 101A, 101B, 101C are disposed in the transfer directions of the third, fourth and fifth transfer units 25A, 25B, 25C, respectively, and the direction of the generated neutron beam N is the same as the transfer directions of the third, fourth and fifth transfer units 25A, 25B, 25C, respectively, so that the neutron beam directions generated by the neutron beam generating units 30B, 30C are in the same plane, and the neutron beam directions generated by the neutron beam generating unit 30A are perpendicular to the plane. By adopting the arrangement mode, the space can be effectively utilized, a plurality of patients can be treated at the same time, the transmission line of the beam is not prolonged too much, and the loss is small. It is understood that the direction of the neutron beam N generated by the neutron beam generating section 30A (30B, 30C) may be different from the direction of the third (fourth, fifth) transmission section 25A (25B, 25C); the first and second transmission units 21, 24 may have different transmission directions, and the second transmission unit 24 may be omitted, and may have only one beam direction switch for branching the beam into 2 or more transmission sections; the transmission directions of the fourth and fifth transmission parts 25B and 25C and the transmission direction of the first transmission part 21 may be a "Y" shape, or may be a deformation of "Y", for example, the transmission direction of the fourth transmission part 25B or the fifth transmission part 25C is the same as the transmission direction of the first transmission part 21, and the transmission directions of the fourth and fifth transmission parts 25B and 25C and the transmission direction of the first transmission part 21 may be other shapes, such as "T" shape or arrow shape, as long as the transmission directions of the fourth and fifth transmission parts 25B and 25C form an included angle greater than 0 degree on the XY plane; the conveyance direction of the fourth and fifth conveyance sections 25B, 25C is not limited to the XY plane, and the conveyance direction of the third conveyance section 25A may not be along the Z axis, as long as two of the conveyance direction of the fourth conveyance section 25B, the conveyance direction of the fifth conveyance section 25C, and the conveyance direction of the first conveyance section 21 are in the same plane (first plane), the conveyance direction of the first conveyance section 21 and the conveyance direction of the third conveyance section 25A are also in the same plane (second plane), and the first plane and the second plane are different; the third transmission unit 25A, the neutron beam generating unit 30A, and the irradiation chamber 101A may be omitted, and thus only beam transmission in the XY plane may be provided.
The first and second beam direction switches 22 and 23 include a deflection electromagnet for deflecting the charged particle beam P and a switching electromagnet for controlling the traveling direction of the charged particle beam P, and the boron neutron capture therapy system 100 may further include a beam collector (not shown) for confirming the output of the charged particle beam P before therapy or the like, and the first or second beam direction switches 22 and 23 can guide the charged particle beam P to the beam collector while deviating from a normal trajectory.
The first transmission part 21, the second transmission part 24, and the third, fourth and fifth transmission parts 25A, 25B and 25C are each constructed by a vacuum tube C, and may be formed by connecting a plurality of sub-transmission parts, and the transmission directions of the plurality of sub-transmission parts may be the same or different, for example, the transmission directions of the first, second, third, fourth and fifth transmission parts 21, 24, 25A, 25B and 25C may be the transmission directions of any sub-transmission part thereof by deflecting the beam transmission directions by an electromagnet, and the first plane and the second plane formed as described above are planes formed between the sub-transmission parts directly connected to the beam direction switcher; the apparatus may further include a beam adjustment unit (not shown) for the charged particle beam P, the beam adjustment unit including a horizontal diverter and a horizontal-vertical diverter for adjusting the axis of the charged particle beam P, a quadrupole electromagnet for suppressing the divergence of the charged particle beam P, a four-way cutter for shaping the charged particle beam P, and the like. The third, fourth, and fifth transfer units 25A, 25B, and 25C may include a current monitor (not shown) and a charged particle beam scanning unit (not shown) as needed. The current monitor measures in real time the current value (i.e., charge, irradiation dose rate) of the charged particle beam P irradiated to the target T. The charged particle beam scanning unit scans the charged particle beam P, and performs irradiation control of the charged particle beam P with respect to the target T, for example, control of the irradiation position of the charged particle beam P with respect to the target T.
The charged particle beam generating chamber 102 may include an accelerator chamber 1021 and a beam transport chamber 1022, the accelerator chamber 1021 being two-layered, and the accelerator 10 extending from L2 to L1. The beam transfer chamber 1022 is located at L2, and the first transfer portion 21 extends from the accelerator chamber 1021 to the beam transfer chamber 1022. The irradiation chambers 101B and 101C are located at L2, and the irradiation chamber 101A is located at L1. In this embodiment, L1 is below L2, that is, the floor of L2 is the ceiling of L1, and it is understood that the configuration may be reversed. The material of the floor (ceiling) S may be concrete or boron-containing barite concrete having a thickness of 0.5m or more. The irradiation chambers 101A, 101B, 101C and the beam transfer chamber 1022 are provided with a shielding space surrounded by a shielding wall W1, and the shielding wall W1 may be a wall made of boron-containing barite concrete having a thickness of 1m or more and a density of 3g/c.c., and includes a first partition shielding wall W2 partitioning the beam transfer chamber 1022 from the irradiation chambers 101B, 101C, a second partition shielding wall W3 partitioning the accelerator chamber 1021 and the beam transfer chamber 1022 at L1, and a third partition shielding wall W4 partitioning the accelerator chamber 1021 and the irradiation chamber 101A at L2. The accelerator chamber 1021 is surrounded by a concrete wall W having a thickness of 1m or more, a second partition wall W3, and a third partition wall W4. At least a part of the neutron beam generating sections 30B, 30C is buried in the first partition shielding wall W2, and the fourth and fifth transmission sections 25B, 25C extend from the beam transmission chamber 1022 to the neutron beam generating sections 30B, 30C; the neutron beam generating section 30A is located in the irradiation chamber 101A, and the third transmission section 25A extends from the beam transmission chamber 1022 to the irradiation chamber 101A through the floor S. The irradiation chambers 101A, 101B, and 101C have shielding doors D1, D2, and D3 for the treatment table 40 and the doctor to enter and exit, respectively, the accelerator chamber 1021 has shielding doors D4 and D5 for the accelerator chamber 1021 to maintain the accelerator 10 at L1 and L2, the beam transfer chamber 1022 has a shielding door D6 for the accelerator chamber 1021 to enter and exit the beam transfer chamber 1022 to maintain the beam transfer unit 20, and the shielding door D6 is provided on the second partition shielding wall W3. The inner shield wall W5 is further provided in the irradiation chambers 101A, 101B, 101C to form a labyrinth passage from the shield doors D1, D2, D3 to the beam outlet, to prevent direct irradiation of the radiation rays when the shield doors D1, D2, D3 are accidentally opened, the inner shield wall W5 may be provided at different positions according to different layouts of the irradiation chambers, and a shield door D7 inside the irradiation chamber may be provided between the inner shield wall W5 and the shield wall W1 or the third partition shield wall W4 to form secondary protection when the sub-beam irradiation treatment is underway. The inner shielding wall W5 can be made of boron-containing barite concrete with the thickness of more than 0.5m and the density of 3 g/c.c.; the shielding doors D1, D2, D3, D4, D5, D6, D7 may be composed of two independent layers of the main shielding door D and the sub shielding door D ', or only the main shielding door D or the sub shielding door D ', may be determined according to practical situations, the main shielding door D may be a boron-containing PE or barite concrete or lead having a thickness of 0.5m or more and a density of 6g/c.c. of the same material, and the sub shielding door D ' may be a boron-containing PE or barite concrete or lead having a thickness of 0.2m or more and a density of 6g/c.c. of the same material. In this embodiment, the shielding doors D1, D4, D5, D6 are composed of a main shielding door D and a sub-shielding door D ', the shielding doors D1, D2, D3 include only the main shielding door D, and the shielding door D7 includes only the sub-shielding door D'. The shielding walls and the shielding doors form a shielding space, and prevent radiation from entering the inside of the irradiation chambers 101A, 101B, and 101C and the outside of the beam transmission chamber 1022, and radiation from being emitted from the inside to the outside. In the present embodiment, the second partition shielding wall W3 that partitions the accelerator chamber 1021 and the beam transfer chamber 1022 is provided between the accelerator 10 and the first beam direction switcher 22, that is, the first transfer portion 21 passes through the second partition shielding wall W3, it is understood that the second partition shielding wall W3 and the shielding door D6 may be omitted, or may be provided at other positions, such as between the first and second beam direction switchers 22, 23 or between the second beam direction switcher 23 and the neutron beam generating portions 30B, 30C; or an additional partition shielding wall and shielding door are provided between the second partition shielding wall W3 and the first partition shielding wall W2. That is, a shielding wall is provided between the neutron beam generating section and the accelerator, and an operator is prevented from being irradiated with neutrons and other radiation leaking from the neutron beam generating section during inspection and maintenance of the accelerator, while reducing the reaction of the accelerator activated by neutrons.
Where the shielding wall or floor is penetrated by the assembly or element to easily cause leakage of neutrons and other radiation rays, as in the present embodiment, the neutron beam generating sections 30B, 30C penetrate the first partition shielding wall W2, the first transmission section 21 penetrates the second partition shielding wall W3, the third transmission section 25A penetrates the floor S, and the first shielding body 60, the second shielding body 70, and the third shielding body 80 may be provided at the positions penetrated by the neutron beam generating sections 30B, 30C, the first transmission section 21, the third transmission section 25A on the side of the first partition shielding wall W2, the second partition shielding wall W3, the floor S toward the upstream in the beam transmission direction, respectively. The first shielding body 60 covers the end portions of the neutron beam generating sections 30B, 30C facing the accelerator and contacts the first partition shielding wall W2 around the neutron beam generating sections 30B, 30C, prevents neutrons overflowing or reflecting from the beam shaping bodies of the neutron beam generating sections 30B, 30C from entering the accelerator chamber 1021 and the beam transfer chamber 1022, and the fourth and fifth transfer sections 25B, 25C pass through the first shielding body 60 to reach the targets T of the neutron beam generating sections 30B, 30C. The second shielding 70 contacts the second partition shielding wall W3 around the first transmission part 21, preventing neutrons overflowing or reflected from the beam transmission part 20 from entering the accelerator chamber 1021, and the first transmission part 21 passes through the second shielding 70 and the second partition shielding wall W3 to reach the first beam direction switcher 22. The third shielding 80 contacts the floor S around the third transmission portion 25A, preventing neutrons overflowing or reflected from the irradiation chamber 101A from entering the beam transmission chamber 1022, and the third transmission portion 25A passes through the third shielding 80 and the floor S to reach the neutron beam generating portion 30A. The materials of the first, second and third shields 60, 70, 80 may be PE or barite concrete or lead containing boron.
The first and second beam direction switches 22, 23 are each surrounded by a shielding 26, the shielding 26 being of a material such as PE or barite concrete or lead containing boron, to prevent leakage of neutrons and other radiation from the beam direction switches. It will be appreciated that the first and second beam direction switches 22, 23 may also be entirely surrounded by a shield 26; other parts of the beam transport section, such as the vacuum tube, may also be surrounded by a shielding to prevent neutrons and other radiation from leaking from the beam transport section.
The boron neutron capture therapy system 100 may also include a preparation room, a control room, and other space for assisting in therapy, each irradiation room may be configured with a preparation room for performing preparation work such as fixing a patient to a treatment table, injecting boron medicine, simulating a therapy plan, and the like before irradiation therapy, a connection channel is provided between the preparation room and the irradiation room, the patient is directly pushed into the irradiation room after the preparation work is completed or automatically enters the irradiation room through a track controlled by the control mechanism, the preparation room and the connection channel are also closed by a shielding wall, and the preparation room is also provided with a shielding door. The control room is used for controlling the accelerator, the beam transmission part, the treatment table and the like, controlling and managing the whole irradiation process, and a manager can monitor a plurality of irradiation rooms at the same time in the control room.
It will be appreciated that the shield walls (including concrete wall W), shield doors, shields, and shields in this embodiment may all have other thicknesses or densities or be replaced with other materials.
While the foregoing describes illustrative embodiments of the present invention to facilitate an understanding of the present invention by those skilled in the art, it should be understood that the present invention is not limited to the scope of the embodiments, but rather that various changes can be made within the spirit and scope of the present invention as defined and defined by the appended claims as would be apparent to those skilled in the art.
Claims (10)
1. A neutron capture therapy system, comprising an accelerator, a beam transmission portion and a neutron beam generation portion, wherein the accelerator accelerates charged particles to generate a charged particle beam, the beam transmission portion transmits the charged particle beam generated by the accelerator to the neutron beam generation portion, and the neutron beam generation portion generates a therapeutic neutron beam.
2. The neutron capture therapy system of claim 1, wherein the neutron beam generating device further comprises a therapy table, the neutron beam generating device comprises a target, a beam shaping body and a collimator, the target is disposed between the beam transmitting device and the beam shaping body, the charged particle beam generated by the accelerator irradiates the target via the beam transmitting device and acts with the target to generate neutrons, and the generated neutrons sequentially pass through the beam shaping body and the collimator to form a therapeutic neutron beam and irradiate to a patient on the therapy table.
3. The neutron capture therapy system of claim 2, wherein the beam shaper body includes a reflector body, a moderator body, a thermal neutron absorber, a radiation shield body and a beam exit port, the moderator body moderates neutrons generated from the target material to an epithermal neutron energy region, the reflector body surrounds the moderator body and directs stray neutrons back to the moderator body to increase the epithermal neutron beam intensity, the thermal neutron absorber is used for absorbing thermal neutrons to avoid excessive doses with shallow normal tissue during therapy, the radiation shield body is disposed behind the reflector body around the beam exit port for shielding leaking neutrons and photons to reduce normal tissue doses in non-irradiated regions, the collimator is disposed behind the beam exit port to focus neutron beams, and a radiation shielding device is disposed between the patient and the beam exit port to shield radiation from the beam exiting the beam exit port to normal tissue of the patient.
4. The neutron capture therapy system of claim 3, wherein the beam transport section has a vacuum tube for accelerating or transporting the charged particle beam, the vacuum tube extending into the beam shaping body in the direction of the charged particle beam and passing sequentially through the reflector and the buffer body, the target being disposed within the buffer body at an end of the vacuum tube.
5. The neutron capture therapy system of claim 1, wherein the beam transport section includes a first transport section connected to the accelerator, a beam direction switch to switch the direction of travel of the charged particle beam, and a second transport section to transport the charged particle beam to the neutron beam generating section, the shield being a shield surrounding the beam direction switch.
6. The neutron capture therapy system of claim 5, wherein the beam direction switch comprises first and second beam direction switches, the beam transport section further comprising a third transport section connecting the first and second beam direction switches, the shielding enclosure being 2 enclosures surrounding the first and second beam direction switches, respectively.
7. The neutron capture therapy system of claim 6, wherein the first and second beam direction switches include deflection electromagnets for deflecting the charged particle beam and switching electromagnets for controlling the traveling direction of the charged particle beam, the neutron capture therapy system further includes a beam collector for output confirmation of the charged particle beam before the therapy, the first or second beam direction switches are directed to the beam collector, the first, second and third transmission sections include beam adjustment sections for the charged particle beam, and the second transmission section includes a current monitor and a charged particle beam scanning section.
8. The neutron capture therapy system of claim 6, wherein the neutron beam generating sections are 3, the second transfer sections include fourth, fifth and sixth transfer sections which transfer charged particle beams to the 3 neutron beam generating sections respectively, the first transfer section branching into the third transfer section and fourth transfer section in the first beam direction switcher, and the third transfer section branching into the fifth transfer section and sixth transfer section in the second beam direction switcher.
9. The neutron capture therapy system of claim 5, further comprising a charged particle beam generation chamber and an irradiation chamber, the charged particle beam generation chamber housing the accelerator and at least a portion of the beam transport section, the patient undergoing treatment with neutron beam irradiation in the irradiation chamber, at least a portion of the neutron beam generation section being embedded in a dividing wall of the irradiation chamber and the charged particle beam generation chamber.
10. The neutron capture therapy system of claim 9, wherein the charged particle beam generation chamber includes an accelerator chamber and a beam transport chamber, the first transport portion extending from the accelerator chamber to the beam transport chamber, the second transport portion extending from the beam transport chamber to the neutron beam generation portion, the beam direction switch and shielding housing being housed within the beam transport chamber.
Priority Applications (9)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710800921.XA CN109464752B (en) | 2017-09-07 | 2017-09-07 | Neutron capture therapy system |
| RU2020109210A RU2745081C1 (en) | 2017-09-07 | 2018-08-16 | Neutron capture therapy system |
| JP2020513396A JP2020519420A (en) | 2017-09-07 | 2018-08-16 | Neutron capture therapy system |
| PCT/CN2018/100753 WO2019047697A1 (en) | 2017-09-07 | 2018-08-16 | Neutron capture therapy system |
| EP18852829.3A EP3666337B1 (en) | 2017-09-07 | 2018-08-16 | Neutron capture therapy system |
| EP21178910.2A EP3922307A1 (en) | 2017-09-07 | 2018-08-16 | Neutron capture therapy system |
| US16/745,565 US11058898B2 (en) | 2017-09-07 | 2020-01-17 | Neutron capture therapy system |
| US17/243,998 US11583702B2 (en) | 2017-09-07 | 2021-04-29 | Neutron capture therapy system |
| JP2023057086A JP2023078466A (en) | 2017-09-07 | 2023-03-31 | Neutron capture therapy system |
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| CN201710800921.XA CN109464752B (en) | 2017-09-07 | 2017-09-07 | Neutron capture therapy system |
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| EP4183448A1 (en) * | 2020-07-20 | 2023-05-24 | Neuboron Therapy System Ltd. | Radiotherapy system and safety interlock control method therefor |
| JP2022150626A (en) * | 2021-03-26 | 2022-10-07 | 住友重機械工業株式会社 | Treatment preparation device and treatment facility |
| WO2023284780A1 (en) * | 2021-07-16 | 2023-01-19 | 中硼(厦门)医疗器械有限公司 | Neutron capture therapy system |
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