TW202342137A - Neutron capture treatment system - Google Patents

Abstract

The utility model provides a neutron capture treatment system, which can avoid or reduce the leakage of neutrons and other radiation rays at a shielding wall or floor where components or elements pass through, and the arrangement of a neutron shielding structure can reduce secondary radiation generated after an installation mechanism or a driving mechanism is irradiated by the neutrons. The neutron capture treatment system comprises an accelerator, a beam transmission part, a neutron beam generation part and a shielding wall for accommodating the accelerator, the beam transmission part and the neutron beam generation part, and a shielding body is arranged on one side, facing the upstream of the beam transmission direction, of the shielding wall and penetrates through the beam transmission part or the neutron beam generation part. The neutron capture therapy system further comprises a mounting mechanism or a driving mechanism of the shielding body, the mounting mechanism is used for movably mounting the shielding body on the side, facing the upstream of the beam transmission direction, of the shielding wall, the driving mechanism is used for driving the shielding body to move, and the mounting mechanism or the driving mechanism is provided with a neutron shielding structure.

Description

Neutron capture therapy system

The present invention relates to a radiation irradiation system, and in particular to a neutron capture therapy system.

With the development of atomic science, radiation therapy such as cobalt 60, linear accelerator, and electron beam has become one of the main means of cancer treatment. However, traditional photon or electron therapy is limited by the physical conditions of radiation itself. While killing tumor cells, it will also cause damage to a large number of normal tissues in the path of the beam. In addition, due to the different sensitivity of tumor cells to radiation, traditional radiation therapy The treatment results for malignant tumors that are more resistant to radiation (such as glioblastoma multiforme and melanoma) are often poor.

In order to reduce radiation damage to normal tissues surrounding tumors, the concept of targeted therapy in chemotherapy has been applied to radiation therapy. For tumor cells with high radiation resistance, we are currently actively developing therapies with high relative biological effects. biological effectiveness (RBE) radiation sources, such as proton therapy, heavy particle therapy, neutron capture therapy, etc. Among them, neutron capture therapy combines the above two concepts. For example, boron neutron capture therapy uses boron-containing drugs to treat tumor cells. The specific concentration, combined with precise neutron beam control, provides a better cancer treatment option than traditional radiation.

Various types of radiation are produced during radiotherapy. For example, boron neutron capture therapy produces low-energy to high-energy neutrons and photons. These radiations may cause varying degrees of damage to normal tissues of the human body. Therefore, in the field of radiotherapy, how to achieve effective treatment while reducing radiation contamination to the external environment, medical staff or patients' normal tissues is an extremely important issue. Radiation therapy equipment is usually installed in a space surrounded by shielding materials. The shielding wall formed by the shielding material cannot be closed shielded where components or components pass through it, which can easily cause leakage of radiation. Wherever components or components pass through, Set up a shielding structure to enhance the shielding effect; the auxiliary parts between the reinforced shielding structure and the shielding wall are usually steel structures. After the steel is irradiated by neutrons, it will produce radioactive isotopes with long half-lives, such as cobalt 60, forming secondary radiation, which will affect the environment and Radiation safety has negative consequences.

Therefore, it is necessary to propose a new technical solution to solve the above problems.

In order to solve the above problems, one aspect of the present invention provides a neutron capture therapy system, which includes an accelerator, a beam transmission part, and a neutron beam generation part. The accelerator accelerates charged particles to generate a charged particle beam. The beam transmission The part transmits the charged particle beam generated by the accelerator to the neutron beam generating part, and the The sub-beam generating part generates a neutron beam for treatment. The neutron capture treatment system further includes a shielding wall forming a space for accommodating the accelerator, the beam transmission part and the neutron beam generating part. The shielding wall faces the beam. A shield is provided on the upstream side of the transmission direction where the beam transmission part or the neutron beam generation part passes, and the neutron capture therapy system further includes an installation mechanism or a driving mechanism of the shield, so The installation mechanism is used to movably install the shielding body on the upstream side of the shielding wall toward the beam transmission direction, and the driving mechanism is used to drive the shielding body to move. The driving mechanism can be manually driven, or Can be electrically driven. The shielding body can avoid or reduce the leakage of neutrons and other radiation rays caused by the components or elements passing through the shielding wall. The installation mechanism of the shielding body is provided with a first neutron shielding structure or the driving mechanism is provided with a second Neutron shielding structure reduces the secondary radiation generated after the installation mechanism or driving mechanism is irradiated by neutrons.

Preferably, the installation mechanism includes a first connector carrying the shield, and the first neutron shielding structure blocks the exposed portion of the first connector.

Further, the installation mechanism includes a guide rail and a roller. The guide rail is fixed on the upstream side of the shielding wall toward the beam transmission direction. The roller is fixed on the shielding body. The shielding body can pass through the roller along the side of the shielding wall. The guide rail slides.

Furthermore, the installation mechanism includes a frame, the shielding body is a plate fixed to the frame, a connecting plate is fixed on the top of the frame, and the roller is transparent It is fixed to the connecting plate through the first connecting piece. Furthermore, the first connecting piece passes through the connecting plate, the roller is installed on one end of the first connecting piece, and the first neutron shielding structure covers the part of the other end of the first connecting piece that protrudes from the connecting plate or covers the first connecting piece at The part between the roller and the connecting plate or covering the first connecting part coincides with the connecting plate and the exposed part or the whole covering the first connecting part and the connecting plate.

」形或周向封閉的。 Preferably, the driving mechanism includes a fixed bracket and a second connecting piece carrying the driving mechanism. The fixed bracket is fixedly mounted to the shielding wall through the second connecting piece, and the second neutron shielding structure includes A baffle that blocks the second connecting piece. Further, the baffle is fixed on the fixed bracket to block the second connecting member on the upstream side facing the beam transmission direction, and can be L-shaped or "

” Shape or circumferentially closed.

Preferably, the driving mechanism includes a cylinder, the cylinder includes a cylinder body, and the second neutron shielding structure includes a collar covering the outer periphery of the cylinder body.

Further, the cylinder is fixed to the shielding wall, such as through a fixing bracket; the cylinder also includes a piston, one end of the piston extends into the cylinder, and the other end of the piston is connected to the shielding body, For example, it is fixedly connected to the shield through a connecting rod.

Furthermore, the driving mechanism also includes a transmission member connected to the piston, the shielding body includes a first shielding part and a second shielding part, the first shielding part and the second shielding part are between the cylinder and the Driven by the transmission component, it moves in the opposite direction.

Furthermore, the transmission component includes a sprocket and a chain located on both sides of the sprocket, and the chain can move around the sprocket; the chains on both sides of the sprocket are respectively connected to the first shielding part and The second shielding part, such as the chains on both sides of the sprocket, are respectively fixedly connected to the first and second frames that fix the first shielding part and the second shielding part, and the piston of the cylinder is connected to the first frame or the second frame, so The first shielding part and the second shielding part move in opposite directions driven by the piston and the chain.

Preferably, the material of the first and second neutron shielding structures is boron-containing resin or boron-containing glass fiber composite material.

Preferably, the material of the first shielding part and the second shielding part is a neutron shielding material, such as boron-containing PE; the material of the first and second frames is that the product after being irradiated by neutrons does not have Radioactivity or products produced after irradiation by neutrons are materials with low radioactivity or radioactive isotopes produced after irradiation by neutrons with a short half-life, such as aluminum alloys.

Preferably, the first and second connecting parts and the cylinder are made of steel.

The neutron capture treatment system of the present invention can avoid or reduce the leakage of neutrons and other radiation caused by components or elements passing through the shielding wall. The installation mechanism or driving mechanism of the shielding body includes a neutron shielding structure to avoid The installation mechanism or driving mechanism generates secondary radiation after being irradiated by neutrons.

100:Neutron capture therapy system

10:Accelerator

101,101A,101B,101C:Irradiation room

102: Charged particle beam generation chamber

1021:Accelerator Room

1022: Beam transmission room

103:Partition wall

1031: Accommodation slot

1032:Slot

1033:shielding plate

20: Beam transmission part

21,24,25A,25B,25C: Transmission Department

22,23: Beam direction switcher

26:Shielding cover

30, 30A, 30B, 30C: Neutron beam generation part

301:Heat dissipation layer

3011: Cooling channel

3012,3013: Cooling pipe

302: Base layer

303: Action layer

304: Antioxidant layer

31: Beam shaping body

311:Reflector

312:Retarding body

313: Thermal neutron absorber

314: Radiation shield

315:Beam exit

32:Collimator

40: Treatment table

50: Radiation shielding device

60:Support module

70:First shield

70A, 70A’: Installation mechanism

70B:Driving mechanism

70C: Neutron shielding structure

703a: First connector

704a:Connection board

705a:Frame

705a1: First frame

705a2: Second frame

706a:Chute

707a:wheel

701b: Cylinder

702b: connecting rod

703b:Chain

704b: sprocket

705b: Connection block

706b: Buffer component

707b: Stop member

708b: Fixed bracket

709b: Second connector

701c: Collar

702c: hat cover

703c: Collar

703c’: Collar

704c:Baffle

704c’: baffle

705c: Cover body

71:Accommodating hole

72:First shielding department

721,731: Groove

73:Second shielding department

74,701a: Guide rail

75,702a:Roller

80: Second shield

90:Third shield

200:Patient

C:Transmission tube

D: Main screen door

D’: secondary screen door

D1,D2,D3,D4,D5,D6,D7: screen door

L1, L2: floors

L1, L2: direction

L3, L4: direction

M: tumor cells

N: Neutron beam

P: charged particle beam

S:Floor

T:Target

W:Concrete wall

W1: Shielding wall

W2: First dividing shield wall

W3: Second dividing shield wall

W4: The third partition shielding wall

W5: Inner shielding wall

Figure 1 is a schematic structural diagram of a neutron capture therapy system in an embodiment of the present invention;

Figure 2 is a schematic structural diagram of the target material of the neutron capture therapy system in an embodiment of the present invention;

Figure 3 is a schematic layout diagram of the neutron capture therapy system in the XY plane in the embodiment of the present invention;

Figure 4 is a schematic diagram of the A-A section of Figure 3;

Figure 5 is a schematic diagram of the installation of the beam shaping body support module of the neutron capture therapy system in the embodiment of the present invention;

Figure 6 is a schematic structural diagram of a shielding body disposed at a position where the neutron beam generating part of the neutron capture therapy system passes through the shielding wall in an embodiment of the present invention;

Figure 7 is a schematic diagram of the shield of Figure 6 in another state;

Figure 8 is a schematic structural diagram of a shielding body disposed at a position where the neutron beam generating part of the neutron capture therapy system passes through the shielding wall in another embodiment of the present invention;

Figure 9 is a partially enlarged schematic diagram of the installation mechanism and driving mechanism of the shield in Figure 8 in another state;

Figure 10 is a partial enlarged schematic diagram of the installation mechanism of the shield body in Figure 8;

Figures 11a to 11g are schematic diagrams of the neutron shielding structure of the installation mechanism and driving mechanism of the shield in Figure 8.

The embodiments of the present invention will be described in further detail below in conjunction with the drawings. It is explained so that those skilled in the art can implement it according to the text of the description. An XYZ coordinate system is set in which the direction of the charged particle beam P emitted from the accelerator to be described later is the X-axis, the direction orthogonal to the direction of the charged particle beam P emitted from the accelerator is the Y-axis, and the direction perpendicular to the ground is the Z-axis. (Refer to Figures 3 and 4), and use X, Y, and Z in the description of the positional relationship of each component.

Referring to Figure 1, the neutron capture therapy system in this embodiment is preferably a boron neutron capture therapy system 100. The boron neutron capture therapy system 100 is a device for cancer treatment using boron neutron capture therapy. Boron neutron capture therapy performs cancer treatment by irradiating a patient 200 injected with boron (B-10) with a neutron beam N. After the patient 200 takes or injects a boron (B-10)-containing drug, the boron-containing drug selectively accumulates In tumor cells M, boron-containing (B-10) drugs are then used to have high capture cross-section characteristics for thermal neutrons, and ⁴ He and ⁷ Li are generated through ¹⁰ B(n,α) ⁷ Li neutron capture and nuclear fission reactions. A heavily charged particle. The average energy of the two charged particles is about 2.33 MeV, and it has the characteristics of high linear energy transfer (LET) and short range. The linear energy transfer and range of the α particle are 150keV/μm and 8μm respectively, while ^{the 7} Li heavy particle is 175keV/μm, 5μm, the total range of the two particles is approximately equivalent to the size of a cell. Therefore, the radiation damage caused to organisms can be limited to the cell level, and local killing can be achieved without causing too much damage to normal tissues. The purpose of tumor cells.

The boron neutron capture treatment system 100 includes an accelerator 10 , a beam transmission part 20 , a neutron beam generation part 30 and a treatment table 40 . Accelerator 10 pairs of charged particles (such as Protons, deuterons, etc.) are accelerated to generate a charged particle beam P such as a proton beam; the beam transmission part 20 transports the charged particle beam P generated by the accelerator 10 to the neutron beam generation part 30; the neutron beam generation part 30 generates The patient 200 on the treatment table 40 is irradiated with the therapeutic neutron beam N.

The neutron beam generation part 30 includes a target T, a beam shaper 31 and a collimator 32. The charged particle beam P generated by the accelerator 10 is irradiated to the target T through the beam transmission part 20 and interacts with the target T to generate neutrons. , the generated neutrons are sequentially transmitted through the beam shaper 31 and the collimator 32 to form a therapeutic neutron beam N and irradiated to the patient 200 on the treatment table 40 . The target material T is preferably a metal target material. The appropriate nuclear reaction is selected based on the required neutron yield and energy, the available accelerated charged particle energy and current size, and the physical and chemical properties of the metal target. Commonly discussed nuclear reactions include ⁷ Li(p,n) ⁷ Be and ⁹ Be(p,n) ⁹ B, both reactions are endothermic reactions. The energy thresholds of the two nuclear reactions are 1.881MeV and 2.055MeV respectively. Since the ideal neutron source for boron neutron capture therapy is epithermal neutrons with keV energy level, theoretically, if protons with energy only slightly higher than the threshold are used to bombard the metal Lithium targets can produce relatively low-energy neutrons and can be used clinically without much retarding. However, the interaction cross sections of lithium metal (Li) and beryllium metal (Be) with protons of threshold energy are different. High, in order to generate a large enough neutron flux, higher energy protons are usually used to initiate nuclear reactions. An ideal target material should have the characteristics of high neutron yield, generated neutron energy distribution close to the epithermal neutron energy region (to be described in detail below), no generation of too much strong penetrating radiation, safe, cheap, easy to operate, and high temperature resistance. However, It is not actually possible to find a nuclear reaction that meets all the requirements. As is well known to those skilled in the art, the target T can also be made of metal materials other than Li and Be, such as Ta or W and their alloys. The accelerator 10 may be a linear accelerator, a cyclotron, a synchrotron, or a synchrocyclotron.

The beam shaper 31 can adjust the beam quality of the neutron beam N generated by the interaction between the charged particle beam P and the target T, and the collimator 32 is used to converge the neutron beam N so that the neutron beam N can be used during treatment. Has high targeting ability. The beam shaping body 31 further includes a reflector 311, a retarder 312, a thermal neutron absorber 313, a radiation shield 314 and a beam outlet 315. The neutrons generated by the interaction between the charged particle beam P and the target T have a wide energy spectrum. In addition to meeting the treatment needs of epithermal neutrons, it is necessary to reduce the content of other types of neutrons and photons as much as possible to avoid causing harm to operators or patients. Therefore, the neutrons coming out of the target T need to pass through the retarder 312. The fast neutron energy (>40keV) is adjusted to the epithermal neutron energy region (0.5eV-40keV) and the thermal neutrons (<0.5eV) are reduced as much as possible. The retarder 312 has a large interaction cross-section with fast neutrons and the superthermal neutrons. Made of materials with small action cross-sections. In this embodiment, the retarder 312 is made of at least one of D ₂ O, AlF ₃ , Fluental ^TM , CaF ₂ , Li ₂ CO ₃ , MgF ₂ and Al ₂ O ₃ ; The reflector 311 surrounds the retarder 312 and reflects the neutrons that diffuse around the retarder 312 back to the neutron beam N to improve the utilization rate of neutrons. It is made of a material with strong neutron reflection ability. In this embodiment, the reflector 311 is made of at least one of Pb or Ni; there is a thermal neutron absorber 313 at the rear of the retarder 312, which is made of a material with a large interaction cross-section with thermal neutrons. In this embodiment, the thermal neutron absorber 313 is The thermal neutron absorber 313 is made of Li-6. The thermal neutron absorber 313 is used to absorb thermal neutrons passing through the retarder 312 to reduce the content of thermal neutrons in the neutron beam N and avoid excessive interaction with superficial normal tissues during treatment. dose, it can be understood that the thermal neutron absorber can also be integrated with the retarder, and the material of the retarder contains Li-6; the radiation shield 314 is used to shield neutrons and photons leaking from parts other than the beam exit 315 , the material of the radiation shielding body 314 includes at least one of a photon shielding material and a neutron shielding material. In this embodiment, the material of the radiation shielding body 314 includes a photon shielding material lead (Pb) and a neutron shielding material polyethylene (PE). . It can be understood that the beam shaping body 31 can also have other structures, as long as it can obtain the super-thermal neutron beam required for treatment. A radiation detection component (not shown) can also be installed in the beam shaping body 31 to monitor the neutron generation process. Detect various types of radiation in the system. The collimator 32 is arranged at the rear of the beam outlet 315. The super-thermal neutron beam coming out of the collimator 32 is irradiated to the patient 200. After passing through the superficial normal tissue, it is slowed down into thermal neutrons and reaches the tumor cells M. It can be understood that collimation The detector 32 can also be eliminated or replaced by other structures, and the neutron beam comes out of the beam outlet 315 and irradiates the patient 200 directly. In this embodiment, a radiation shielding device 50 is also provided between the patient 200 and the beam outlet 315 to shield the normal tissue of the patient from being radiated by the beam coming out of the beam outlet 315. It can be understood that the radiation shielding device 50 may not be provided. .

The target T is disposed between the beam transmission part 20 and the beam shaping body 31. The beam transmission part 20 has a transmission tube C that accelerates or transmits the charged particle beam P, In this embodiment, the transmission tube C extends into the beam shaping body 31 along the direction of the charged particle beam P, and passes through the reflector 311 and the retardation body 312 in sequence. The target T is arranged in the retardation body 312 and located at the end of the transmission tube C end to obtain better neutron beam quality. It can be understood that the target can be arranged in other ways, and can also be movable relative to the accelerator or beam shaping body to facilitate target replacement or to make the charged particle beam interact with the target uniformly. 2, the target T includes a heat dissipation layer 301, a base layer 302 and an action layer 303. The action layer 303 interacts with the charged particle beam P to generate a neutron beam, and the base layer 302 supports the action layer 303. In this embodiment, the material of the active layer 303 is Li or its alloy, the charged particle beam P is a proton beam, the target T also includes an antioxidant layer 304 located on one side of the active layer 303 to prevent oxidation of the active layer, and the charged particle beam P passes through the anti-oxidation layer 304, the active layer 303 and the base layer 302 in sequence along the incident direction. The material of the anti-oxidation layer 304 is not easily corroded by the active layer and can reduce the loss of the incident proton beam and the heat generated by the proton beam, such as at least one of Al, Ti and their alloys, or stainless steel. The heat dissipation layer 301 is made of a material with good thermal conductivity (for example, at least one of Cu, Fe, and Al) or is at least partially made of the same material or integrated with the base layer. The heat dissipation layer can have various structures, such as a flat plate shape, which will not be described in detail in this embodiment. The heat dissipation layer 301 is provided with a cooling inlet IN (not shown), a cooling outlet OUT (not shown), and a cooling channel 3011 connecting the cooling inlet IN and the cooling outlet OUT. The cooling medium enters from the cooling inlet IN and passes through the cooling channel 3011 from the cooling channel 3011 . Exit OUT. In this embodiment, first, The second cooling pipes 3012 and 3013 have one ends connected to the cooling inlet IN and the cooling outlet OUT of the target T respectively, and the other ends are connected to an external cooling source. It can be understood that the first and second cooling tubes can also be arranged in the beam shaping body in other ways, and can also be eliminated when the target is placed outside the beam shaping body. With reference to Figures 3 and 4, the boron neutron capture treatment system 100 is overall configured in the space of two floors L1 and L2. The boron neutron capture treatment system 100 also includes an irradiation chamber 101 (101A, 101B, 101C) and a charged particle beam generation In the chamber 102, the patient 200 on the treatment table 40 undergoes treatment with neutron beam N irradiation in the irradiation chamber 101 (101A, 101B, 101C). The charged particle beam generation chamber 102 accommodates the accelerator 10 and at least part of the beam delivery part 20. There may be one or more neutron beam generating parts 30 to generate one or more neutron beams N for treatment, and the beam transmitting part 20 may selectively transmit the charged particle beam P to one or several neutron beam generating parts 30 Or, the charged particle beam P is transmitted to multiple neutron beam generating parts 30 at the same time, and each neutron beam generating part 30 corresponds to one irradiation chamber 101 . In this embodiment, there are three neutron beam generating parts and three irradiation chambers respectively, namely neutron beam generating parts 30A, 30B, and 30C and irradiation chambers 101A, 101B, and 101C. The beam transmission part 20 includes: a first transmission part 21, connected to the accelerator 10; first and second beam direction switchers 22, 23, switching the traveling direction of the charged particle beam P; a second transmission part 24, connected to the first , the second beam direction switcher 22, 23; the third, fourth, and fifth transmission parts 25A, 25B, and 25C respectively switch the charged particle beam P from the first beam direction switcher 22 or the second beam direction. 23 to the neutron beam generating parts 30A, 30B, 30C, the generated neutron beam N is irradiated to the patients in the irradiation chambers 101A, 101B, and 101C respectively. The third transmission part 25A is connected to the first beam direction switcher 22 and the neutron beam generation part 30A, the fourth transmission part 25B is connected to the second beam direction switcher 23 and the neutron beam generation part 30B, and the fifth transmission part 25C is connected to The second beam direction switch 23 and the neutron beam generating unit 30C. That is, the first transmission part 21 branches into the second transmission part 24 and the third transmission part 25A in the first beam direction switcher 22, and the second transmission part 24 branches into the third transmission part in the second beam direction switcher 23. The fourth transmission part 25B and the fifth transmission part 25C. The first and second transmission parts 21 and 24 transmit in the X-axis direction, the third transmission part 25A transmits in the Z-axis direction, and the transmission directions of the fourth and fifth transmission parts 25B and 25C are in the XY plane and are in line with the first and fifth transmission parts. The transmission directions of the two transmission parts 21 and 24 are in a "Y" shape, and the neutron beam generating parts 30A, 30B, and 30C and the corresponding irradiation chambers 101A, 101B, and 101C are respectively along the third, fourth, and fifth transmission parts 25A and 25B. , the transmission direction of 25C is set, and the N direction of the generated neutron beam is the same as the transmission direction of the third, fourth, and fifth transmission parts 25A, 25B, and 25C respectively, so that the neutron beam generated by the neutron beam generating parts 30B and 30C The directions are in the same plane, and the direction of the neutron beam generated by the neutron beam generating unit 30A is perpendicular to the plane. With such an arrangement, space can be effectively used to treat multiple patients at the same time without excessively extending the beam transmission line, resulting in less loss. It can be understood that the N direction of the neutron beam generated by the neutron beam generating part 30A (30B, 30C) and the transmission direction of the third (fourth, fifth) transmission part 25A (25B, 25C) may also be different; the first and third The transmission directions of the two transmission parts 21 and 24 may also be different. The second The transmission part 24 can also be eliminated and only have one beam direction switch to branch the beam into two or more transmission parts; the transmission directions of the fourth and fifth transmission parts 25B and 25C are the same as those of the first transmission part 21 The "Y" shape formed in the transmission direction may also 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. The fourth and fifth transmission parts The transmission directions of the parts 25B and 25C and the transmission direction of the first transmission part 21 can also be in other shapes, such as a "T" shape or an arrow shape, as long as the transmission directions of the fourth and fifth transmission parts 25B and 25C form a shape larger than An included angle of 0 degrees is enough; the transmission directions of the fourth and fifth transmission parts 25B and 25C are not limited to the XY plane, and the transmission direction of the third transmission part 25A does not need to be along the Z axis, as long as the transmission direction of the fourth transmission part 25B , two of the transmission direction of the fifth transmission part 25C and the transmission direction of the first transmission part 21 are in the same plane (first plane), and the transmission direction of the first transmission part 21 and the transmission direction of the third transmission part 25A are also In the same plane (second plane), and the first plane and the second plane are different; the third transmission part 25A, the neutron beam generation part 30A and the irradiation chamber 101A can also be eliminated, so that there is only beam transmission in the XY plane .

The first and second beam direction switches 22 and 23 include a deflection electromagnet that deflects the charged particle beam P and a switching electromagnet that controls the traveling direction of the charged particle beam P. The boron neutron capture therapy system 100 may also include a beam The collector (not shown) is used to confirm the output of the charged particle beam P before treatment, etc., and the first or second beam direction switchers 22 and 23 can cause the charged particle beam P to deviate from the normal orbit and guide it to the radiation source. Beam Collector.

The first transmission part 21, the second transmission part 24 and the third, fourth and fifth transmission parts 25A, 25B and 25C are all constructed of transmission tubes C, and may be formed by connecting multiple sub-transmission parts respectively. The transmission of multiple sub-transmission parts The directions can be the same or different. For example, the beam transmission direction can be deflected through a deflection electromagnet, and the transmission of the first, second, third, fourth, and fifth transmission parts 21, 24, 25A, 25B, and 25C The direction can be the transmission direction of any of its sub-transmission sections. The first plane and the second plane formed above are the planes formed between the sub-transmission sections directly connected to the beam direction switch; A beam adjustment section (not shown) for the beam P. The beam adjustment section includes a horizontal diverter and a horizontal-vertical diverter for adjusting the axis of the charged particle beam P, and a quadrupole for suppressing the divergence of the charged particle beam P. Electromagnets, and four-way cutters for shaping the charged particle beam P, etc. The third, fourth, and fifth transmission parts 25A, 25B, and 25C may include a current monitor (not shown) and a charged particle beam scanning part (not shown) as necessary. The current monitor measures the current value (ie, charge, irradiation dose rate) of the charged particle beam P irradiated onto the target T in real time. 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, such as controlling the irradiation position of the charged particle beam P with respect to the target T.

The charged particle beam generation chamber 102 may include an accelerator chamber 1021 and a beam transmission chamber 1022. The accelerator chamber 1021 has two floors, and the accelerator 10 extends from L2 to L1. The beam transmission chamber 1022 is located at L2, and the first transmission part 21 passes from the accelerator chamber 1021 Extends to beam delivery 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. It can be understood that the opposite configuration is also possible. The material of the floor (ceiling) S can be concrete with a thickness of more than 0.5m or boron-containing barite concrete. The irradiation chambers 101A, 101B, 101C and the beam transmission chamber 1022 have a shielding space surrounded by a shielding wall W1. The shielding wall W1 can be a boron-containing barite concrete wall with a thickness of more than 1m and a density of 3g/cc. The first separation shielding wall W2 between the beam transfer chamber 1022 and the irradiation chambers 101B and 101C; the second separation shielding wall W3 at L1 that separates the accelerator chamber 1021 and the beam transport chamber 1022; and the second separation shielding wall W3 that separates the accelerator chamber 1021 and the irradiation chamber 101A at L2. The third dividing shield wall W4. The accelerator chamber 1021 is surrounded by a concrete wall W having a thickness of 1 m or more, and a second partition shield wall W3 and a third partition shield wall W4. At least part of the neutron beam generating parts 30B and 30C is embedded in the first partition shielding wall W2, and the fourth and fifth transmission parts 25B and 25C extend from the beam transmission chamber 1022 to the neutron beam generating parts 30B and 30C; neutron The beam generation part 30A is located in the irradiation chamber 101A, and the third transmission part 25A extends from the beam transmission chamber 1022 through the floor S to the irradiation chamber 101A. The irradiation rooms 101A, 101B, and 101C respectively have screen doors D1, D2, and D3 for the treatment table 40 and the physician to enter and exit. The accelerator room 1021 has screen doors D4 and D5 at L1 and L2 respectively for entering and exiting the accelerator room 1021 for maintenance of the accelerator 10. The beam transfer room 1022 has a shield door D6 for entering and exiting the accelerator room 1021 to maintain the beam transfer unit 20. The shield door D6 is provided at the second point. On the shielding wall W3. The irradiation chambers 101A, 101B, and 101C also have inner shielding walls W5 to form a labyrinth-shaped passage from the shielding doors D1, D2, and D3 to the beam exit to prevent the direct radiation of radiation when the shielding doors D1, D2, and D3 are accidentally opened. For irradiation, the inner shielding wall W5 can be set at different positions according to different layouts of the irradiation room. A shielding door D7 inside the irradiation room can also be set between the inner shielding wall W5 and the shielding wall W1 or the third dividing shielding wall W4, forming a Secondary protection during neutron beam irradiation therapy. The inner shielding wall W5 can be made of boron-containing barite concrete with a thickness of more than 0.5m and a density of 3g/c.c.; the screen doors D1, D2, D3, D4, D5, D6 and D7 can be made of two independent main screen doors It consists of D and secondary screen door D' or only the main screen door D or secondary screen door D', which can be decided according to the actual situation. The main screen door D can be made of the same material with a thickness of more than 0.5m and a density of 6g/c.c. Boron-containing PE or barite concrete or lead, the secondary screen door D' can be made of the same material with a thickness of more than 0.2m and a density of 6g/c.c. boron-containing PE or barite concrete or lead. In this embodiment, the screen doors D1, D4, D5 and D6 are composed of a main screen door D and a secondary screen door D', the screen doors D1, D2 and D3 only include the main screen door D, and the screen door D7 only includes the secondary screen door D. '. The shielding wall and the shielding door form a shielding space to suppress the intrusion of radiation from the outdoors of the irradiation chambers 101A, 101B, and 101C and the beam transmission chamber 1022 into the indoors and the radiation of radiation from the indoors to the outdoors. In this embodiment, the second partition shielding wall W3 that separates the accelerator chamber 1021 and the beam transmission chamber 1022 is provided between the accelerator 10 and the first beam direction switcher 22 , that is, the first transmission part 21 passes through the second partition Shielding wall W3, OK It is understood that the second dividing shielding wall W3 and the shielding door D6 can be eliminated, or can be arranged at other locations, such as between the first and second beam direction switchers 22 and 23 or between the second beam direction switcher 23 and the neutron Between the beam generating parts 30B and 30C; or between the second dividing shielding wall W3 and the first dividing shielding wall W2, an additional dividing shielding wall and a shielding door are provided. That is to say, a shielding wall is set up between the neutron beam generation part and the accelerator. During the accelerator inspection and maintenance, the operator is protected from neutrons and other radiation leaked from the neutron beam generation part, and at the same time, the accelerator is reduced by neutrons. activation reaction.

5 , the beam shaping body 31 is supported by the support module 60 provided in the partition wall 103 (the first partition shielding wall W2). The support module 60 is at least partially provided on the side of the partition wall 103 close to the irradiation chamber 101. The accommodation tank 1031 is provided with a slot 1032 on the side close to the charged particle beam generation chamber 102 for the transmission pipe of the accelerator to pass through, so that the accommodation slot 1031 and the slot 1032 penetrate the partition wall in the neutron beam N transmission direction. This embodiment , the wall surface of the partition wall 103 is a plane, and the propagation direction of the neutron beam N is perpendicular to the wall surface of the partition wall 103 . The modular support structure allows the beam shaping body to be locally adjusted to meet accuracy requirements, improve beam quality and meet target assembly tolerances. On a plane perpendicular to the propagation direction of the neutron beam N, the cross-sectional profile of the support module 60 is located between the cross-sectional profiles of the accommodating groove 1031 and the groove 1032, thereby avoiding the occurrence of through gaps in the beam propagation direction and further reducing radiation. , and at the same time, it is convenient to adjust the support module 60. In this embodiment, the support module 60 is a rectangular parallelepiped as a whole, and the cross-sections of the receiving groove 1031 and the groove 1032 perpendicular to the transmission direction of the neutron beam N are both "冂". Shape, the side walls of the receiving groove 1031 and the groove 1032 are parallel to the neutron beam N transmission direction. A shielding plate 1033 is also provided on the side of the partition wall 103 close to the irradiation chamber 102. The shielding plate 1033 can enhance the shielding effect of the partition wall and suppress secondary radiation generated by the partition wall, thereby avoiding radiation to the patient's normal tissue. On a plane perpendicular to the propagation direction of the neutron beam N, the shielding plate 1033 can match the cross-sectional profile of the support module 60, thereby shielding neutrons leaking from between the support module and the partition wall. The shielding plate is a PE plate. It can be understood that the side of the partition wall 103 close to the charged particle beam generation chamber 102 and the side of the support module 60 close to the irradiation chamber 101 can also be provided with shielding plates. The shielding plates can be made of lead or other neutrons or other materials. It is made of photon shielding material and does not need to be provided with a shielding plate.

The emission directions of the neutrons generated by the interaction between the charged particle beam P and the target material T are almost uniformly distributed in space. At the same time, during the "shaping" process of the neutrons by the beam shaping body 31, a large number of recoil neutrons will be generated. This part Recoil neutrons are an important consideration in radiation shielding design. Closed shielding cannot be achieved where the shielding wall or floor is penetrated by components or elements, which may easily cause the leakage of neutrons and other radiation. For example, in this embodiment, the neutron beam generating parts 30B and 30C pass through the first partition The shielding wall W2 and the first transmission part 21 pass through the second dividing shielding wall W3 and the third transmission part 25A passes through the floor S. The first dividing shielding wall W2, the second dividing shielding wall W3 and the floor S face the beam transmission direction. The first shielding body 70 , the second shielding body 80 and the third shielding body 90 may be respectively provided at the upstream side portions where the neutron beam generating parts 30B and 30C, the first transmission part 21 and the third transmission part 25A pass through. The first shield 70 covers the neutron beam generating part 30B and 30C face the ends of the accelerator to prevent neutrons from overflowing or reflecting from the beam shapers of the neutron beam generating parts 30B and 30C from entering the accelerator chamber 1021 and the beam transmission chamber 1022. The fourth and fifth transmission parts 25B and 25C The target T passes through the first shield 70 and reaches the neutron beam generating parts 30B and 30C. The second shielding body 80 prevents neutrons that overflow or reflect from the beam transmission part 20 from entering the accelerator chamber 1021. The first transmission part 21 passes through the second shielding body 80 and the second dividing shielding wall W3 to reach the first beam direction switcher. twenty two. The third shielding body 90 prevents neutrons that overflow or reflect from the irradiation chamber 101A from entering the beam transmission chamber 1022, and the third transmission part 25A passes through the third shielding body 90 and the floor S to reach the neutron beam generation part 30A. The material of the first shielding body 70 , the second shielding body 80 and the third shielding body 90 may be boron-containing PE or barite concrete or lead, and may also include other neutron shielding materials.

The following describes the first, second and third shielding bodies 70, 80 and 90 in detail, taking the first shielding body 70 as an example. In one embodiment, the first shielding body 70 is movable and is movably installed on the upstream side of the first dividing shielding wall W2 toward the beam transmission direction (the side close to the charged particle beam generating chamber 102 through the installation mechanism 70A). ), and has a first position and a second position. In the first position, a receiving hole 71 is formed through which the fourth and fifth transmission parts 25B and 25C pass, and covers the ends of the neutron beam generating parts 30B and 30C facing the accelerator 10 to shield recoil neutrons and limit the dose of high and medium neutrons. area to protect the accelerator components, reduce radiation damage to the components, and reduce element activation of the accelerator components. At the same time, when one irradiation chamber is operating, it protects the other irradiation chamber to ensure non-operational The radiation dose in the row irradiation chamber is at a safe level; in the second position, the accommodating hole 71 is opened, exposing the ends of the neutron beam generating parts 30B and 30C facing the accelerator 10, without removing the transmission tube C passing through the accommodating hole 71. The operating space allows the neutron beam generating parts 30B and 30C to be replaced when the accelerator 10 is turned off, such as the target T, the beam shaping body 31 , the radiation detection assembly provided in the beam shaping body 31 or the first and second cooling tubes 3012 , 3013, it is also possible to make room for removing part of the transmission pipe during replacement, or to install, debug, and repair the beam transmission part 20 that passes through the first separation shielding wall W2 and the first shielding body 70 . The accommodating hole can accommodate the transmission tube C, magnet, etc. of the fourth and fifth transmission parts 25B and 25C, and can also accommodate the first and second cooling tubes 3012, 3013 or other functional components, and can facilitate movement and provide operating space without disturbing the Immovable component of the beam delivery section. The first shielding body 70 and the first dividing shielding wall W2 may be in sealed contact to enhance the shielding effect, or they may have a gap, and the shielding effect may be achieved by adjusting the size of the first shielding body 70 .

As shown in FIGS. 6 and 7 , in this embodiment, the first shielding body 70 includes a first shielding part 72 and a second shielding part 73 . The first shielding part 72 and the second shielding part 73 are respectively generated along the lines close to the neutron beam. The first and second directions L1 and L2 of the parts 30B and 30C move to the first position. The first shielding part 72 and the second shielding part 73 have first and second grooves 721 and 731 respectively. The grooves 721 and 731 jointly form the receiving hole 71 through which the fourth and fifth transmission parts 25B and 25C pass in the first position, and cover the ends of the neutron beam generating parts 30B and 30C facing the accelerator 10; the first shielding part 72 and No. The two shielding parts 73 respectively move to the second position along the third and fourth directions L3 and L4 away from the neutron beam generating parts 30B and 30C. At the second position, the receiving hole 71 is opened to expose the neutron beam generating parts 30B and 30C. Toward the end of the accelerator 10, an operating space is formed without removing the transmission pipe C passing through the receiving hole 71. It can be understood that the first shielding body 70 may also include a third shielding part or be composed of three or more shielding parts.

In this embodiment, the first shielding part 72 and the second shielding part 73 are sliding, and the guide rail 74 and the roller 75 fixed on the first and second shielding parts 72 and 73 constitute the sliding assembly (installation) of the first shielding body 70 Mechanism 70A), the roller 75 rolls along the guide rail 74 to drive the first and second shielding parts 72 and 73 to slide along the guide rail 74. The guide rail 74 is fixed on the side of the first dividing shielding wall W2 facing the charged particle beam generation chamber 102 and in the extending direction. Parallel to the ground (XY plane), that is, the first and second shielding parts 72 and 73 are configured as horizontal double-opening sliding doors. It can be understood that the installation mechanism 70A can have other settings, or can be moved in other ways, such as rotation, etc. .

As shown in Figure 8, in another embodiment, the installation mechanism 70A' includes a guide rail 701a (74') and a roller 702a (75'). The guide rail 701a is directly fixed on the first partition shielding wall W2 through expansion screws. Combined with Figure 9 As shown in Figure 11b, the roller 702a is connected to the connecting plate 704a fixed to the first and second shielding parts 72 and 73 through the first connecting member 703a (such as a bolt and nut). Specifically, the roller 702a is rotatably arranged around its central axis. One end of the bolt (such as through a bearing), the other end of the bolt passes through the connecting plate 704a and is tightened on both sides of the connecting plate 704a through nuts. It can be understood that the guide rail 701a and the roller The wheel 702a can also be fixed in other ways. The installation mechanism 70A' also includes a frame, which includes a first frame 705a1 and a second frame 705a2 that fix the first and second shielding parts 72 and 73 (the second frame has the same structure and function as the first frame, not shown in the figure). (shown), the first and second shielding parts 72 and 73 are both constructed of multiple plates, and the multiple plates are spliced together and fixed to the first frame 705a1 and the second frame 705a2 of the first and second shielding parts 72 and 73 respectively. , the connecting plate 704a is fixed on the top of the frame, thereby forming a hanging rail. Referring to Figure 10, the bottom of the frame can also be fixed with a chute 706a. The chute 706a cooperates with the wheel 707a fixed on the shielding wall W2 to form an auxiliary limit for the first and second shielding parts 72 and 73 to slide horizontally along the guide rail 701a. The first and second shielding parts 72 and 73 and their first and second frames 705a1 and 705a2 are prevented from flipping in the direction perpendicular to the shielding wall W2. The frame is constructed of aluminum alloy profiles. The radioactive half-life of the product after being irradiated by neutrons is short, which reduces the secondary radiation generated. The first and second shielding parts 72 and 73 are boron-containing PE plates. It is understandable that the frame can also be used Other materials whose products after being irradiated by neutrons are not radioactive or whose products after being irradiated by neutrons have low radioactive activity or where the radioactive isotopes produced after being irradiated by neutrons have a short half-life, the first and second shielding parts 72 and 73 can also be used. Use other neutron shielding materials.

The neutron capture therapy system 100 may also include a driving mechanism 70B of the first shield 70. The driving mechanism 70B drives the movement of the first shield 70. The driving mechanism 70B includes a cylinder 701b, a connecting rod 702b, a chain 703b, a sprocket 704b, and a connection. Block 705b. The cylinder body of the cylinder 701b is driven by air supply through an air supply device (not shown). The piston of the cylinder 701b moves. The piston of the cylinder 701b is connected to the first frame 705a1 of the first shielding part 72 through the connecting rod 702b, thereby driving the first shielding part 72 to move. Specifically, the piston moves in the horizontal direction. One end of the piston of the cylinder 701b The other end of the cylinder body of the cylinder 701b is connected to the connecting rod 702b. The connecting rod 702b is fixed to the side of the first frame 705a1 of the first shielding part 72 away from the second shielding part 73; the chain 703b is located on both sides of the sprocket 704b. The first frame 705a1 and the second frame 705a2 are respectively connected to the first and second shielding parts 72 and 73 through the connecting block 705b. The movement of the first shielding part 72 drives the second shielding part 73 to move in the opposite direction through the chain 703b. , thereby reaching the first position or the second position. Specifically, one end of the connecting block 705b is fixed to the top of the frame 705a, and the other end is engaged with the chain 703b through teeth. It can be understood that in this embodiment, the connecting rod 702b, the chain 703b, the sprocket 704b, and the connecting block 705b constitute the transmission component of the driving mechanism 70B. The transmission component is connected to the piston of the cylinder 701b. It can be understood that the transmission component can also have other components. setting; a buffering member 706b may also be provided. When the first shielding part 72 is about to move to the end position in the direction away from the second shielding part 73, the connecting rod 702b contacts the buffering member 706b to prevent impact caused by collision; a stop member may also be provided 707b (such as a fixed screw), the stop member 707b interacts with the connecting rod 702b to limit the maximum distance that the first shielding part 72 can move in the direction away from the second shielding part 73; there are other driving methods, such as driving by a motor. The first or second shield part moves. The driving mechanism 70B also includes a fixed bracket 708b, which is fixed to the shielding wall through a second connector 709b (as shown in Figure 11d). On W2, other parts of the driving mechanism 70B (such as the cylinder body of the cylinder 701b, the sprocket 704b, the buffer member 706b, the stop member 707b) can be fixed on the fixed bracket 708b.

The neutron capture therapy system 100 can also control the operation of the driving mechanism 70B through a control mechanism (not shown) to control the movement of the first shield 70. The control mechanism can be set outside the charged particle beam generation chamber 102, such as a control room. (as described below) to prevent the control mechanism from being activated by neutrons and failing.

形，在框架705a上方包圍連接板704a和穿過連接板704a的第一連接件703a，可以理解，罩體705c還可以包括頂部，中子屏蔽結構所覆蓋的面積越大，對安裝機構在中子輻射後的二次輻射屏蔽效果越好。 Each component of the mounting mechanism 70A, 70A' or the driving mechanism 70B can be made of a radioisotope produced after being irradiated by neutrons that has no radioactivity or has a low radioactive activity after being irradiated by neutrons, or a radioisotope produced after being irradiated by neutrons has a short half-life. material, such as aluminum alloy, but due to mechanical performance requirements, some components are still made of steel in this embodiment, such as the components carrying the driving force (such as the cylinder body of the cylinder 701b), the connection carrying the first shield 70 (the first connector 703a) and the connector (the second connector 709b) carrying the driving mechanism 70B. After the steel is irradiated by neutrons, it will produce radioactive isotopes with a long half-life, such as cobalt 60, and a neutron shielding structure 70C needs to be set up. Block and reduce the secondary radiation generated after the installation mechanism or driving mechanism is irradiated by neutrons. As shown in Fig. 11a, a collar 701c is provided around the cylinder body of the cylinder 701b. As shown in Figure 11b, a cap 702c is provided outside the first connecting member 703a. The cap 702c covers the portion of the first connecting member 703a protruding from the connecting plate 704a at one end that passes through the connecting plate 704a (the nuts and bolts pass through the connecting plate 704a. end); a collar 703c can also be set to cover other exposed parts of the first connecting piece 703a, such as the part where the bolt passes through the connecting plate 704a and is located between the two side plates of the connecting plate 704a (the first connecting piece and the connecting plate The overlapping and exposed part), the part between the roller 702a and the connecting plate 704a. It can be understood that the part where the bolt passes through the connecting plate 704a and is located between the two side plates of the connecting plate 704a is also limited by space, as shown in Figure 11c. Collar 703c' can be placed to cover the bolt from outside connecting plate 704a. As shown in the Z-direction diagram in Figure 11d, without affecting the mechanical connection relationship, the cover body 705c can also be integrally wrapped outside the connecting plate 704a to completely cover the connecting plate 704a and the first connecting member 703a passing through the connecting plate 704a. For shielding, the cover body 705c can be

Shape, surrounding the connecting plate 704a above the frame 705a and the first connecting piece 703a passing through the connecting plate 704a. It can be understood that the cover 705c can also include a top. The larger the area covered by the neutron shielding structure, the more important it is for the installation mechanism in the center. The better the secondary radiation shielding effect after sub-radiation.

”形，在第二連接件709b的上側、下側和朝向射束傳輸方向上游的一側(靠近帶電粒子束生成室102的一側)對反衝中子進行遮擋。可以理解，擋板704c和704c’還可以包括側部以形成周向封閉，增強輻射屏蔽 效果，如圖11g所示，擋板704c’還對第二連接件709b進行了側部包覆。 As shown in Figure 11e, a baffle 704c is provided outside the second connecting member 709b, and the baffle 704c is fixed on the fixed bracket 708b. In this embodiment, the baffle 704c is L-shaped, and is located on the lower side and direction of the second connecting member 709b. The side upstream of the beam propagation direction (the side close to the charged particle beam generation chamber 102) blocks the recoil neutrons. In another embodiment, as shown in Figure 11f, baffle 704c' is "

” shape, the recoil neutrons are blocked on the upper and lower sides of the second connecting member 709b and the side upstream of the beam transmission direction (the side close to the charged particle beam generation chamber 102). It can be understood that the baffle 704c and 704c' may also include side portions to form a circumferential closure and enhance the radiation shielding effect. As shown in Figure 11g, the baffle 704c' also side-covers the second connector 709b.

The material of the neutron shielding structure 70C may include boron-containing resin, boron-containing glass fiber composite material, etc. It can be understood that the form and position of the neutron shielding structure 70C can also be set according to specific needs.

The first and second beam direction switchers 22 and 23 are respectively surrounded by a shielding cover 26 to prevent neutrons and other radiation from leaking from the beam direction switcher. The material of the shielding cover 26 can be boron-containing PE or barite. concrete or lead. It can be understood that the first and second beam direction switches 22 and 23 can also be entirely surrounded by a shielding cover 26; other parts of the beam transmission part, such as vacuum tubes, can also be surrounded by a shielding cover to prevent neutrons and other radiation. Line leaks from the beam delivery section.

The boron neutron capture therapy system 100 can also include a preparation room, a control room and other spaces for auxiliary treatment. Each irradiation room can be equipped with a preparation room for fixing the patient to the treatment table, injecting boron medicine, and For preparation work such as treatment plan simulation, a connecting channel is set up between the preparation room and the irradiation room. After the preparation is completed, the patient is directly pushed into the irradiation room or controlled by a control mechanism through the track to automatically enter the irradiation room. The preparation room and the connecting channel are also shielded. The walls are enclosed and the preparation room also has a screen door. The control room is used to control the accelerator, beam transmission section, treatment table, etc., to control and manage the entire irradiation process. Managers can also monitor multiple irradiation rooms at the same time in the control room.

It can be understood that the shielding wall (including the concrete wall W), the shielding door, the shielding body, and the shielding cover in this embodiment can have other thicknesses or densities or be replaced with other materials.

Although the illustrative specific embodiments of the present invention are described above to facilitate those skilled in the art to understand the present invention, it should be clear that the present invention is not limited to the scope of the specific embodiments. For those of ordinary skill in the art, As long as various changes are within the spirit and scope of the present invention as defined and determined by the appended patent application scope, these changes are obvious and are within the scope of protection claimed by the present invention.

100:Neutron capture therapy system

10:Accelerator

20: Beam transmission part

30: Neutron beam generation section

3012,3013: Cooling pipe

31: Beam shaping body

311:Reflector

312:Retarding body

313: Thermal neutron absorber

314: Radiation shield

315:Beam exit

32:Collimator

40: Treatment table

50: Radiation shielding device

200:Patient

C:Transmission tube

M: tumor cells

N: Neutron beam

P: charged particle beam

T:Target

Claims (10)

A neutron capture therapy system includes an accelerator, a beam transmission part, and a neutron beam generation part. The aforesaid accelerator accelerates charged particles to generate a charged particle beam, and the aforementioned beam transmission part transmits the charged particle beam generated by the aforementioned accelerator to the aforementioned medium. The neutron beam generating part generates a neutron beam for treatment, wherein the neutron capture therapy system further includes a shielding wall forming a space for accommodating the accelerator, the beam transmission part, and the neutron beam generating part, in A shielding body is provided on the upstream side of the shielding wall toward the beam transmission direction where the beam transmission part or the neutron beam generation part passes, and the shielding body is movable and has a first position and a second position, In the aforementioned first position, a receiving hole is formed through which the beam transmission part passes, and in the aforementioned second position, the receiving hole is opened. The neutron capture therapy system according to claim 1, wherein the neutron capture therapy system further includes a charged particle beam generation chamber and an irradiation chamber, and the aforementioned charged particle beam generation chamber accommodates the aforementioned accelerator and at least part of the aforementioned beam transmission part, The patient undergoes neutron beam irradiation treatment in the irradiation chamber. The shielding wall includes a partition wall between the irradiation chamber and the charged particle beam generation chamber. At least a part of the neutron beam generation part is embedded in the partition wall. The first position covers the end of the neutron beam generating part facing the accelerator, and the second position at least partially exposes the end of the neutron beam generating part facing the accelerator. The neutron capture therapy system according to claim 2, wherein the beam transmission part includes a first transmission part connected to an accelerator, a switching charged particle A beam switch in the beam traveling direction and a second transmission part that transmits the charged particle beam to the aforementioned neutron beam generating part, the aforementioned second transmission part passes through the aforementioned shielding body to the aforementioned neutron beam generating part, and the aforementioned accommodating hole accommodates the aforementioned Second transmission section. The neutron capture therapy system according to claim 2, wherein the side of the partition wall close to the irradiation chamber is provided with a support module that at least partially accommodates the neutron beam generating part and is used to support the neutron beam generating part. A receiving groove, a groove for the beam transmission part to pass through is provided on one side of the charged particle beam generating chamber, the receiving groove and the groove penetrate the partition wall in the neutron beam transmission direction, and are vertical to the neutron beam. On the plane of the transmission direction, the cross-sectional profile of the neutron beam generating part and its supporting module is located between the cross-sectional profile of the accommodating groove and the groove. The neutron capture therapy system according to claim 1, wherein the shielding body includes a first shielding part and a second shielding part, and the first shielding part and the second shielding part respectively extend along the first edge of the neutron beam generating part close to the neutron beam generating part. , move to the aforementioned first position in the second direction, the aforementioned first shielding part and the second shielding part have first and second grooves respectively, and the aforementioned first and second grooves jointly form the aforementioned receiving hole at the aforementioned first position. The neutron capture therapy system according to claim 5, wherein the first shielding part and the second shielding part slide along a guide rail, and the guide rail is fixed on the upstream side of the shielding wall facing the beam transmission direction and the extending direction is parallel to ground. The neutron capture therapy system according to claim 5, wherein the first shielding part and the second shielding part are made of neutron shielding material, and the neutron shielding material is boron-containing PE or barite concrete or lead. . The neutron capture therapy system according to claim 1, wherein the neutron capture therapy system further includes an installation mechanism or a driving mechanism of the shield, and the installation mechanism is used to movably install the shield on the shield wall toward the radiation source. On the upstream side of the beam transmission direction, the driving mechanism is used to drive the shielding body to move. The neutron capture therapy system according to claim 8, wherein the installation mechanism includes a guide rail and a roller, the guide rail is fixed on the upstream side of the shielding wall facing the beam transmission direction, and the roller is fixed on the shielding body, and the shielding body Move along the guide rail through rollers. The neutron capture therapy system according to claim 8, wherein the driving mechanism includes a cylinder, the cylinder includes a cylinder and a piston, one end of the piston extends into the cylinder, and the other end is connected to the shielding body.

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