WO2017118291A1 - 用于中子捕获治疗的射束整形体 - Google Patents

用于中子捕获治疗的射束整形体 Download PDF

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Publication number
WO2017118291A1
WO2017118291A1 PCT/CN2016/111346 CN2016111346W WO2017118291A1 WO 2017118291 A1 WO2017118291 A1 WO 2017118291A1 CN 2016111346 W CN2016111346 W CN 2016111346W WO 2017118291 A1 WO2017118291 A1 WO 2017118291A1
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Prior art keywords
cooling
neutron
target
cooling portion
beam shaping
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PCT/CN2016/111346
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English (en)
French (fr)
Inventor
刘渊豪
李珮仪
Original Assignee
南京中硼联康医疗科技有限公司
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Priority claimed from CN201620017409.9U external-priority patent/CN205460520U/zh
Priority claimed from CN201610013472.XA external-priority patent/CN106955427B/zh
Application filed by 南京中硼联康医疗科技有限公司 filed Critical 南京中硼联康医疗科技有限公司
Priority to EP16883417.4A priority Critical patent/EP3395404B1/en
Priority to RU2018127729A priority patent/RU2720707C2/ru
Priority to JP2018532142A priority patent/JP2019502455A/ja
Publication of WO2017118291A1 publication Critical patent/WO2017118291A1/zh
Priority to US16/028,967 priority patent/US10434333B2/en
Priority to JP2022161810A priority patent/JP7464672B2/ja

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1042—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1077—Beam delivery systems
    • G—PHYSICS
    • G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
    • G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
    • G21K5/00—Irradiation devices
    • G21K5/08—Holders for targets or for other objects to be irradiated
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H3/00—Production or acceleration of neutral particle beams, e.g. molecular or atomic beams
    • H05H3/06—Generating neutron beams
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N2005/002—Cooling systems
    • A61N2005/005—Cooling systems for cooling the radiator
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
    • A61N2005/1087—Ions; Protons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
    • A61N2005/109—Neutrons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1092—Details
    • A61N2005/1094—Shielding, protecting against radiation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1092—Details
    • A61N2005/1095—Elements inserted into the radiation path within the system, e.g. filters or wedges
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H2277/00—Applications of particle accelerators
    • H05H2277/10—Medical devices
    • H05H2277/11—Radiotherapy

Definitions

  • the present invention relates to a beam shaping body, and more particularly to a beam shaping body for neutron capture therapy.
  • neutron capture therapy combines the above two concepts, such as boron neutron capture therapy, by the specific agglomeration of boron-containing drugs in tumor cells, combined with precise neutron beam regulation, providing better radiation than traditional radiation. Cancer treatment options.
  • the accelerator boron neutron capture treatment accelerates the proton beam by an accelerator that accelerates to an energy sufficient to overcome the coulomb repulsion of the target nucleus and reacts nuclearly with the target to produce neutrons, Therefore, in the process of generating neutrons, the target will be irradiated by an accelerated proton beam of a very high energy level, and the temperature of the target will rise sharply, thereby affecting the service life of the target.
  • an aspect of the present application provides a beam shaping body for neutron capture therapy, the neutron capture treatment comprising an accelerating tube for accelerating a proton beam, the beam shaping body including a beam entrance a target provided in the accelerating tube, a retarding body adjacent to the target, a reflector surrounding the retarding body, and a thermal neutron absorber adjacent to the retarding body, provided in the a radiation shield and a beam exit within the beam shaping body, the target reacting nuclearly with a proton beam incident from the beam entrance to generate neutrons, the neutron forming a neutron beam, the retarding body
  • the neutrons generated from the target are decelerated to an epithermal neutron energy region, the reflector directing the deviated neutrons back to the slowing body to increase the intensity of the epithermal neutron beam, the thermal neutron
  • the absorber is for absorbing thermal neutrons to avoid excessive doses with shallow normal tissue for shielding leakage of neutrons and photons to reduce normal tissue dose in the non
  • cooling portion By “extending in the direction parallel to the axis of the accelerating tube” is meant that the overall extension of the cooling portion (whether the second cooling portion or the third cooling portion) is from one end of the accelerating tube (the accelerating tube embedding section as will be mentioned later) End) toward the other end (the end of the accelerating tube extending as described below away from the end of the embedding section), such as the cooling section extending from one end of the accelerating tube to the other with a wavy line, or cooling The portion extends from one end of the accelerating tube to the other end in a spiral line.
  • the accelerating tube includes an embedding section and an extending section
  • the target is disposed at an end of the accelerating tube embedding section
  • the embedding section is embedded in the retarding body
  • the extending section extends outside the retarding body
  • the first cooling portion is located between the target and the retarding body
  • the second cooling portion and the third cooling portion are extended in the direction parallel to the axis of the accelerating tube to the outside of the embedding section of the accelerating tube.
  • the cooling device is set to a crucible structure.
  • the first cooling portion is located at an end of the acceleration tube and is in contact with the target plane
  • the second cooling portion and the third cooling portion are respectively located on upper and lower sides of the acceleration tube to form a first cooling portion. ⁇ type structure.
  • the provision of the second cooling portion and the third cooling portion on the upper and lower sides of the accelerating tube is only a preferred embodiment.
  • the second cooling portion and the third cooling portion may not be disposed on the upper and lower sides of the accelerating tube.
  • the second cooling portion may be disposed side by side on one side of the accelerating tube.
  • the second cooling portion and the third cooling portion are both tubular structures made of copper, and the second cooling portion and the third cooling portion are perpendicular to a contact plane of the target and the first cooling portion, respectively.
  • the first cooling portion includes a first contact portion in direct contact with the target, a second contact portion in contact with the retarding body, and a cooling medium passing between the first contact portion and the second contact portion.
  • a cooling tank having an input tank that communicates with the second cooling unit and an output tank that communicates with the third cooling unit.
  • the upper edge of the input slot is located above the upper edge of the second cooling portion, and the lower edge of the output slot is located below the lower edge of the third cooling portion.
  • the generated neutron beam achieves a better retarding effect, and at the same time, the beam shaping body obtains better beam quality, and further, the retarding body is set. It has at least one pyramidal structure.
  • the cone shape has a first end portion, a second end portion, and a main body portion connecting the first end portion and the second end portion, and the insertion portion of the accelerating tube is located at the first end portion and the second end portion of the cone shape Between the portions, the first cooling portion is located between the target and the second end of the cone shape.
  • the target includes a lithium target layer and an oxidation resistant layer on the side of the lithium target layer for preventing oxidation of the lithium target layer.
  • the first contact portion is made of a heat conductive material or a material capable of both heat conduction and foaming
  • the second contact portion is made of a material that suppresses foaming. That is to say, the first contact portion and the second contact portion can be made as a whole from a material which is both heat-conducting and foam-inhibitable, or the first contact portion is thermally conductive better than the material which inhibits foaming.
  • the second contact portion is made of a material that inhibits foaming. This setting is beneficial Heats the target and inhibits foaming.
  • the oxidation resistant layer is made of Al or stainless steel, and when the first contact portion is made of a material capable of both heat conduction and foaming inhibition, the first contact portion is selected from any one of Fe, Ta or V.
  • the second contact portion is made of any one of Fe, Ta or V, and the cooling medium is water.
  • the beam shaping body for neutron capture treatment of the present application cools the target by providing a cooling device, has a simple structure, is easy to assemble, and can obtain higher quality. Neutron beam.
  • the "cone” or “tapered shape” as used in the embodiment of the present application refers to a structure in which the overall tendency of the outer contour of the outer contour is gradually reduced from one side to the other side in the illustrated direction, and one contour of the outer contour
  • the line may be a line segment, such as a corresponding contour line of a cone shape, or may be an arc, such as a corresponding contour line of a spherical body, and the entire surface of the outer contour may be a smooth transition or a non-smooth transition, such as A lot of protrusions and grooves are made on the surface of the cone or spherical body.
  • connection means that the connection between two or more members includes both direct and indirect, that is, including “direct contact” and “indirect contact”. "directly connected” and “indirectly connected.”
  • Figure 1 is a schematic illustration of a rate-increasing body for neutron capture therapy of the present application
  • Figure 2 is a schematic view of a cooling device of the ⁇ type structure of the present application.
  • FIG. 3 is a schematic view of a cooling device of the type I structure of the present application.
  • FIG. 4 is a schematic view showing the structure of a target of the present application.
  • Neutron capture therapy has been increasingly used as an effective means of treating cancer in recent years, with boron neutron capture therapy being the most common, and neutrons supplying boron neutron capture therapy can be supplied by nuclear reactors or accelerators.
  • Embodiments of the present application take the accelerator boron neutron capture treatment as an example.
  • the basic components of the accelerator boron neutron capture treatment typically include an accelerator, a neutron generator, and a heat for accelerating charged particles (eg, protons, helium nuclei, etc.).
  • the removal system and the beam shaping body, wherein the accelerated charged particles interact with the metal neutron generating portion to generate neutrons, depending on the desired neutron yield and energy, the available charged charged particle energy and current magnitude, and metal neutron production.
  • the physicochemical properties of the part are used to select suitable nuclear reactions.
  • the nuclear reactions often discussed are 7 Li(p,n) 7 Be and 9 Be(p,n) 9 B, both of which are endothermic reactions.
  • the energy thresholds of the two nuclear reactions are 1.881 MeV and 2.055 MeV, respectively. Since the ideal neutron source for boron neutron capture therapy is the superheated neutron of the keV energy level, theoretically, if proton bombardment with energy only slightly higher than the threshold is used.
  • the metal lithium neutron generating part can generate relatively low-energy neutrons, which can be used in clinic without too much slow processing. However, the two neutron generating parts and threshold energy of lithium metal (Li) and base metal (Be) The proton interaction has a low cross section. In order to generate a sufficiently large neutron flux, a higher energy proton is usually used to initiate the nuclear reaction.
  • the ideal target should have a high neutron yield and produce a neutron energy distribution close to the hyperthermal neutron energy zone (described below) Description), there are not many characteristics such as strong radiation generation, safe and easy to operate, and high temperature resistance, but in fact, it is impossible to find a nuclear reaction that meets all requirements.
  • a target made of lithium metal is used.
  • the material of the target can also be made of other metallic materials than the metal materials discussed above.
  • the requirements for the heat removal system vary depending on the selected nuclear reaction.
  • 7 Li(p,n) 7 Be has a lower melting point and thermal conductivity coefficient of the metal target (lithium metal), and the requirements for the heat removal system are higher.
  • 9 Be(p,n) 9 B is high.
  • a nuclear reaction of 7 Li(p,n) 7 Be is employed in the examples of the present application. It can be seen that the temperature of the target irradiated by the accelerated proton beam at a high energy level is inevitably increased, thereby affecting the service life of the target.
  • the nuclear reaction of the charged particles from the nuclear reactor or the accelerator produces a mixed radiation field, that is, the beam contains low-energy to high-energy neutrons and photons; for deep tumors in boron
  • Sub-capture treatment in addition to super-thermal neutrons, the more radiation content, the greater the proportion of non-selective dose deposition in normal tissue, so these will cause unnecessary doses of radiation should be minimized.
  • the human head tissue prosthesis is used for dose calculation in the embodiment of the present application, and the prosthetic beam quality factor is used as the neutron shot. The design reference for the bundle will be described in detail below.
  • the International Atomic Energy Agency has given five air beam quality factor recommendations for clinical neutron sources for clinical boron neutron capture therapy. These five recommendations can be used to compare the pros and cons of different neutron sources and provide The reference basis for selecting the neutron generation route and designing the beam shaping body.
  • the five recommendations are as follows:
  • Epithermal neutron beam flux Epithermal neutron flux>1x 10 9 n/cm 2 s
  • the superheated neutron energy region is between 0.5eV and 40keV, the thermal neutron energy region is less than 0.5eV, and the fast neutron energy region is greater than 40keV.
  • the neutron beam flux and the concentration of boron-containing drugs in the tumor determine the clinical treatment time. If the concentration of the boron-containing drug in the tumor is high enough, the requirement for the flux of the neutron beam can be reduced; conversely, if the concentration of the boron-containing drug in the tumor is low, a high-flux superheated neutron is required to give the tumor a sufficient dose.
  • the IAEA's requirement for the epithermal neutron beam flux is that the number of epithermal neutrons per square centimeter per second is greater than 10 9 .
  • the neutron beam at this flux can roughly control the treatment of current boron-containing drugs. In one hour, short treatment time, in addition to the advantages of patient positioning and comfort, can also make more effective use of boron-containing drugs in the tumor for a limited residence time.
  • fast neutron contamination is defined as the fast neutron dose accompanying the unit's superheated neutron flux.
  • the IAEA's recommendation for fast neutron contamination is less than 2x 10 -13 Gy-cm 2 /n.
  • ⁇ -rays are strong radiation, which will non-selectively cause dose deposition of all tissues in the beam path. Therefore, reducing ⁇ -ray content is also a necessary requirement for neutron beam design.
  • ⁇ -ray pollution is defined as the unit of superheated neutron flux.
  • the gamma dose is recommended by IAEA for gamma ray contamination to be less than 2 x 10 -13 Gy-cm 2 /n.
  • thermal neutrons Due to the fast decay rate and poor penetrability of thermal neutrons, most of the energy is deposited on the skin tissue after entering the human body. In addition to melanoma and other epidermal tumors, thermal neutrons are needed as the neutron source for boron neutron capture therapy. Deep tumors such as tumors should reduce the thermal neutron content.
  • the IAEA's ratio of thermal neutron to superheated neutron flux is recommended to be less than 0.05.
  • the ratio of superheated neutron current to flux represents the directionality of the epithermal neutron beam. The larger the ratio, the better the forward neutron beam, and the higher forward neutron beam can reduce the neutron divergence.
  • the surrounding normal tissue dose also increases the flexibility of the treatment depth and posture.
  • the IAEA's ratio of neutron current to flux is recommended to be greater than 0.7.
  • the present application provides a beam shaping body 10 for neutron capture therapy.
  • a cooling device 20 for cooling the target is provided in the radiation shaping body 10.
  • the radiation shaping body 10 includes a beam inlet 11 , an accelerating tube 12 located in the beam shaping body 10 , a target 13 disposed in the accelerating tube 12 , and a target adjacent to the target 13 .
  • the target 13 undergoes a nuclear reaction with a proton beam incident from the beam entrance 11 to produce a neutron which forms a neutron beam, the neutron beam defining a major axis X.
  • the retarding body 14 decelerates neutrons generated from the target 13 to an epithermal neutron energy region, and the reflector 15 directs neutrons deviating from the neutron beam main axis X back to the retarding body 14 to increase the intensity of the epithermal neutron beam.
  • the thermal neutron absorber 16 is used to absorb thermal neutrons to avoid excessive doses with shallow normal tissue during treatment.
  • the radiation shield 17 is used to shield leaking neutrons and photons to reduce the normal tissue dose in the non-irradiated area.
  • the accelerator boron neutron capture treatment accelerates the proton beam by an accelerator.
  • the target 13 is made of lithium metal, and the proton beam is accelerated to an energy sufficient to overcome the coulomb repulsion of the target nucleus, and 7 Li occurs with the target 13 (p,n) 7 Be nuclear reaction to generate neutrons, beam shaping body 10 can slow the neutrons to the superheated neutron energy zone and reduce the thermal neutron and fast neutron content.
  • the retarding body 14 is made of a material having a large fast neutron action cross section and a small thermal neutron action cross section, and the reflector 15 is made of a material having strong neutron reflection capability, and the thermal neutron absorber 16 Made of a material with a large cross section with thermal neutrons.
  • the retarding body 14 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 15 is made of Pb.
  • the thermal neutron absorber 16 is made of 6 Li.
  • the radiation shield 17 includes a photon shield 171 and a neutron shield 172.
  • the radiation shield 17 includes a photon shield 171 made of lead (Pb) and a neutron shield 172 made of polyethylene (PE).
  • the accelerating tube 12 includes an embedding section 121 and an extending section 122, and the target 13 is disposed at an end of the accelerating tube 12 embedded in the section 121.
  • the insertion section 121 is embedded in the retarding body 14
  • the extended section 122 extends outside the retarding body 14 and is surrounded by the reflector 15 .
  • the accelerating tube 12 is embedded in the retarding body 14 in order to ensure that the cooling device 20 cools the target 13 in the embedded accelerating tube 12 while ensuring that the beam shaping body 10 obtains better neutrons.
  • the beam quality is set as follows.
  • the cooling device 20 includes a first cooling portion 21 for cooling the target 13, a second cooling portion 22 and a third cooling portion 23 extending along the axial direction of the accelerating tube 12 on both sides of the accelerating tube 12, the second The cooling unit 22 inputs a cooling medium to the first cooling unit 21, and the third cooling unit 23 outputs the cooling medium in the first cooling unit 21.
  • the first cooling portion 21 is located between the target 13 and the retarding body 14, and one side of the first cooling portion 21 is in contact with the target 13 and the other side is in contact with the retarding body 14.
  • the second cooling portion 22 and the third cooling portion 23 extend from the outer side of the extension portion 122 of the acceleration tube 12 to the outer side of the insertion portion 121 of the acceleration tube 12, respectively, and communicate with the first cooling portion 21 and are located in the retarding body 14. That is, the first cooling portion 21 is located at the end of the insertion section 121 of the accelerating tube 12 and is located on the side of the target 13 and is in direct contact with the target 13, and the second cooling portion 22 and the third cooling portion 23 are respectively located.
  • the upper and lower sides of the accelerating tube 12 are respectively in communication with the first cooling portion 21, so that the entire cooling device 20 is disposed in a meandering structure.
  • the first cooling portion 21 is in planar contact with the target material 13, and the second cooling portion 22 and the third cooling portion 23 are both tubular structures made of copper, and the second cooling portion 22 and the third cooling portion are cooled.
  • the portions 23 are perpendicular to the contact planes of the first cooling portion 21 and the target 13 (in conjunction with FIG. 2).
  • the first cooling portion 21 includes a first contact portion 211 , a second contact portion 212 , and a cooling groove 213 between the first contact portion 211 and the second contact portion 212 through which the cooling medium passes.
  • the first contact portion 211 is in direct contact with the target material 13.
  • the second contact portion 212 may be in direct contact with the retarding body 14 or may be indirectly contacted by air.
  • the cooling tank 213 has an input groove 214 that communicates with the second cooling unit 22 and an output groove 215 that communicates with the third cooling unit 23 .
  • the first contact portion 211 is made of a heat conductive material.
  • the upper edge of the input slot 214 is located above the upper edge of the second cooling portion 22, and the lower edge of the output slot 215 is located below the lower edge of the third cooling portion 23.
  • the advantage of this arrangement is that the cooling device 20 can more smoothly input the cooling water into the cooling tank 213 and cool the target 13 in a timely manner, and the heated cooling water can be smoothly discharged from the cooling tank 213. At the same time, it is also possible to reduce the water pressure of the cooling water in the cooling tank 213 to some extent.
  • the cooling device can also be arranged in an I-shaped configuration to cool the target 13 in the embedded accelerating tube 12.
  • the first cooling portion 21' in the I-type cooling device 20 is disposed the same as the first cooling portion 21 of the ⁇ -type cooling device 20, except that the second cooling portion 22' of the I-type cooling device 20 and The third cooling portion 23' and the first cooling portion 21' In the same plane, the second cooling portion 22' and the third cooling portion 23 respectively pass through the retarding body 14 in a direction perpendicular to the axis of the accelerating tube 12, that is, the above-described I-shaped structure (as shown in Fig. 3).
  • the cooling device 20 of the I-type structure can also achieve cooling of the target 13, it is necessary to provide a groove 24 through which the second cooling portion 22' and the third cooling portion 23' pass through the retarding body 14 to be assembled. It is more complicated. And the neutron flux of the beam shaping body 10 after the cooling device is set to the I-type structure and the beam quality factor in the air are compared with the neutrons of the beam shaping body 10 after the cooling device is set to the ⁇ -shaped structure. Flux and air quality factors in the air perform poorly.
  • the slow-speed body 14 is made of AlF---- 3 (2.78g/cm---) material
  • the MCNP software (based on the Los Alamos National Laboratory) is based on Monte.
  • the general software package for the calculation of neutrons, photons, charged particles or coupled neutron/photon/charged particle transport problems in three-dimensional complex geometries by the Carlo method, respectively, after the installation of the ⁇ -type and I-type cooling devices The beam shaping body performs simulation calculations:
  • Table 1 shows the performance of the beam quality factor in air in these two embodiments:
  • This example is to conservatively evaluate the superheated neutron flux and fast neutron pollution, set the superthermal neutron energy zone to be between 0.5eV and 10keV, and the thermal neutron energy zone to be less than 0.5eV.
  • the fast neutron energy zone is set to be greater than 10 keV.
  • Table 2 shows the performance of neutron flux in these two examples:
  • This example is to conservatively evaluate the superheated neutron flux and fast neutron pollution, set the superthermal neutron energy zone to be between 0.5eV and 10keV, and the thermal neutron energy zone to be less than 0.5eV.
  • the fast neutron energy zone is set to be greater than 10 keV.
  • the target 13 includes a lithium target layer 131 and an oxidation resistant layer 132 on the side of the lithium target layer 131 for preventing oxidation of the lithium target layer 131.
  • the oxidation resistant layer 132 of the target 13 is made of Al or stainless steel.
  • the first contact portion 211 is made of a heat conductive material (such as a material having good thermal conductivity such as Cu, Fe, Al, etc.) or a material capable of both heat conduction and foaming inhibition
  • the second contact portion is made of a material that suppresses foaming, and is suppressed.
  • the foamed material or the material capable of both heat conduction and foaming inhibition is made of any one of Fe, Ta or V.
  • the target 13 is heated by an accelerated proton beam irradiation temperature increase of a high energy level, and the first contact portion 211 derives heat and carries the heat out through a cooling medium circulating in the cooling bath 213, thereby performing the target 13 cool down.
  • the cooling medium is water.
  • the retarding body 14 is configured to have at least one pyramid shape 140.
  • the retarding body 14 has a first end portion 141 and a second end portion 142 having a third end portion 143 between the first end portion 141 and the second end portion 142 and a first connection The body portion 144 of the end portion 141 and the third end portion 143.
  • the insertion section 121 of the accelerating tube 12 is located between the first end portion 141 and the third end portion 143 of the cone shape 140, and the first cooling portion 21 is located at the third end portion of the target 13 and the cone shape 140. Between 143.
  • the advantage of this arrangement is that the size of the retarding body 14 can be controlled reasonably, so that the generated neutron beam achieves a better retarding effect, and at the same time, the beam shaping body obtains better beam quality. Specifically, since the first cooling portion 21 is located between the target 13 and the third end portion 143 of the pyramid 140, the retarding body 14 located behind the third end portion 143 can have better forward orientation.
  • the higher energy neutrons are retarded, that is to say, such a setting is still sufficient for the neutrons with better forward direction and higher energy to have a longer size slower body to sufficiently retard the neutrons;
  • the neutron deviating from the neutron beam main axis X when the neutron deviated from the main beam X of the beam passes through the main body portion 144, moves to the reflector 15, and the reflector 15 is designed to have a certain angle by the cone shape of the retarding body 14.
  • the neutron deviating from the main beam X of the beam is reflected back to the neutron beam main axis X, while the cone-shaped design prevents the neutrons with lower energy from being excessively slow on the path of the main axis X of the reflected retroreflector, in improving the forwardness. While the retardation effect of the high neutrons is maintained, the intensity of the neutron beam can be maintained, which in turn ensures that the beam shaping body 10 achieves better neutron beam quality.
  • the "cone” or “tapered” structure of the retarding body in the embodiment of the present application refers to a structure in which the overall tendency of the outer contour of the retarding body along the one side to the other side in the illustrated direction is gradually reduced.
  • One of the outlines of the outer contour may be a line segment, such as a corresponding contour line of a cone shape, or may be an arc, such as a corresponding contour line of a spherical body, and the entire surface of the outer contour may be a smooth transition. It can be non-smooth transitions, such as a lot of protrusions and grooves on the surface of a cone or a spherical body.
  • the neutron capture treatment system disclosed herein is not limited to the contents described in the above embodiments and the structures represented in the drawings. Obvious modifications, substitutions, or alterations of the materials, shapes, and positions of the components in the present application are within the scope of the present disclosure.

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Abstract

一种用于中子捕获治疗的射束整形体(10)，所述中子捕获治疗包括用于给质子束加速的加速管(12)，射束整形体(10)包括射束入口(11)、设于加速管(12)中的靶材(13)、邻接于所述靶材(13)的缓速体(14)、包围在所述缓速体(14)外的反射体(15)、与所述缓速体(14)邻接的热中子吸收体(16)、设置在所述射束整形体(10)内的辐射屏蔽(17)和射束出口(18)，射束整形体(10)还具有冷却装置(20)，冷却装置(20)包括用于冷却靶材(13)的第一冷却部(21)、分别沿平行于加速管(12)轴线方向延伸并与第一冷却部(21)连通的第二冷却部(22)和第三冷却部(23)，所述第一冷却部(21)与靶材(13)平面接触，第二冷却部(22)向第一冷却部(21)输入冷却介质，第三冷却部(23)将第一冷却部(21)中的冷却介质输出。所述射束整形体(10)通过设置冷却装置(20)对靶材(13)进行冷却，结构简单，装配容易。

Description

用于中子捕获治疗的射束整形体 技术领域
本发明涉及一种射束整形体，尤其涉及一种用于中子捕获治疗的射束整形体。
背景技术
随着原子科学的发展，例如钴六十、直线加速器、电子射束等放射线治疗已成为癌症治疗的主要手段之一。然而传统光子或电子治疗受到放射线本身物理条件的限制，在杀死肿瘤细胞的同时，也会对射束途径上大量的正常组织造成伤害；另外由于肿瘤细胞对放射线敏感程度的不同，传统放射治疗对于较具抗辐射性的恶性肿瘤(如：多行性胶质母细胞瘤(glioblastoma multiforme)、黑色素细胞瘤(melanoma))的治疗成效往往不佳。
为了减少肿瘤周边正常组织的辐射伤害，化学治疗(chemotherapy)中的标靶治疗概念便被应用于放射线治疗中；而针对高抗辐射性的肿瘤细胞，目前也积极发展具有高相对生物效应(relative biological effectiveness,RBE)的辐射源，如质子治疗、重粒子治疗、中子捕获治疗等。其中，中子捕获治疗便是结合上述两种概念，如硼中子捕获治疗，借由含硼药物在肿瘤细胞的特异性集聚，配合精准的中子射束调控，提供比传统放射线更好的癌症治疗选择。
在加速器硼中子捕获治疗中，加速器硼中子捕获治疗通过加速器将质子束加速，所述质子束加速至足以克服靶材原子核库伦斥力的能量，与所述靶材发生核反应以产生中子，因此在产生中子的过程中靶材会受到非常高能量等级的加速质子束的照射，靶材的温度会大幅上升，从而影响靶材的使用寿命。
因此，实有必要提供一种新的技术方案以解决上述问题。
发明内容
为了解决上述问题，本申请的一个方面提供用于中子捕获治疗的射束整形体，所述中子捕获治疗包括用于给质子束加速的加速管，所述射束整形体包括射束入口、设于加速管中的靶材、邻接于所述靶材的缓速体、包围在所述缓速体外的反射体、与所述缓速体邻接的热中子吸收体、设置在所述射束整形体内的辐射屏蔽和射束出口，所述靶材与自所述射束入口入射的质子束发生核反应以产生中子，所述中子形成中子射束，所述缓速体将自所述靶材产生的中子减速至超热中子能区，所述反射体将偏离的中子导回至所述缓速体以提高超热中子射束强度，所述热中子吸收体用于吸收热中子以避免治疗时与浅层正常组织造成过多剂量，所述辐射屏蔽用于屏蔽渗漏的中子和光子以减少非照射区的正常组织剂量，其中，所述射束整形体还具有冷却装置，所述冷却装置包括用于冷却靶材的第一冷却部、分别沿平行于加速管轴线方向延伸并与第一冷却部连通的第二冷却部和第三冷却部，所述第一冷却部与靶材平面 接触，所述第二冷却部向第一冷却部输入冷却介质，第三冷却部将第一冷却部中的冷却介质输出。
所谓“沿平行于加速管轴线方向延伸”是指冷却部(不论第二冷却部还是第三冷却部)的整体上的延伸方向是从加速管的一端(如下文将要提到的加速管嵌入段的端部)向着另一端(如下文将要提到的加速管延伸段远离嵌入段的端部)有延伸趋势，如冷却部以波浪形的管路从加速管的一端延伸到另一端，或者冷却部以螺旋形的管路从加速管的一端延伸到另一端。
进一步地，所述加速管包括嵌入段和延伸段，所述靶材设于加速管嵌入段的端部，所述嵌入段嵌设于缓速体中，所述延伸段延伸于缓速体外侧而被反射体包围，所述第一冷却部位于靶材和缓速体之间，所述第二冷却部和第三冷却部沿平行于加速管轴线方向延伸至加速管嵌入段的外侧而位于射束整形体中。
因为加速管嵌设在缓速体中，为了便于对嵌入式加速管中靶材的冷却，将冷却装置设置为匚型结构。具体地，所述第一冷却部位于加速管的端部而与所述靶材平面接触，所述第二冷却部和第三冷却部分别位于加速管的上下两侧而与第一冷却部形成匚型结构。本领域技术人员熟知地，将第二冷却部和第三冷却部设置在加速管的上下两侧只是作为优选实施例。当然，第二冷却部和第三冷却部也可以不设置在加速管的上下两侧，例如可以将第二冷却部并排设置在加速管的一侧。
进一步地，所述第二冷却部和第三冷却部都是由铜制成的管状结构，所述第二冷却部和第三冷却部分别垂直于靶材和第一冷却部的接触平面。
进一步地，所述第一冷却部包括与靶材直接接触的第一接触部、与缓速体接触的第二接触部及位于第一接触部和第二接触部之间的供冷却介质通过的冷却槽，所述冷却槽具有与第二冷却部连通的输入槽及与第三冷却部连通的输出槽。
为了能够使冷却介质更加顺畅地从冷却槽中输入或者输出，同时还能够在一定程度上降低冷却槽中冷却水的水压。所述输入槽的上边沿位于第二冷却部的上边沿的上方，所述输出槽的下边沿位于第三冷却部的下边沿的下方。
为了能够比较合理的控制缓速体的尺寸，使产生的中子束达到较好的缓速效果，同时使射束整形体获得较好的射束品质，进一步地，将所述缓速体设置为具有至少一个锥体状的结构。所述锥体状具有第一端部、第二端部及连接第一端部和第二端部的主体部，所述加速管的嵌入段位于锥体状的第一端部和第二端部之间，所述第一冷却部位于靶材和锥体状的第二端部之间。
所述靶材包括锂靶层、位于锂靶层一侧用于防止锂靶层氧化的抗氧化层。
为了利于靶材的冷却，进一步地，所述第一接触部由导热材料或既能导热又能抑制发泡的材料制成，所述第二接触部由抑制发泡的材料制成。也就是说，第一接触部和第二接触部可以作为一个整体由既能导热又能抑制发泡的材料制成，或者是第一接触部由比抑制发泡的材料的导热性能更好的导热材料制成，第二接触部由抑制发泡的材料制成。这样设置，有利 于靶材的散热及抑制发泡。
所述抗氧化层由Al或者不锈钢制成，当所述第一接触部由既能导热又能抑制发泡的材料制成时，所述第一接触部选自Fe、Ta或V的任一种，所述第二接触部由Fe、Ta或V的任一种制成，所述冷却介质为水。
与现有技术相比，本申请具有以下有益效果：本申请用于中子捕获治疗的射束整形体通过设置冷却装置对靶材进行冷却，结构简单，装配容易，且能够获得较高品质的中子射束。
本申请实施例中所述的“锥体”或“锥体状”是指沿着图示方向的一侧到另一侧其外轮廓的整体趋势逐渐变小的结构，外轮廓的其中一条轮廓线可以是线段，如圆锥体状的对应的轮廓线，也可以是圆弧，如球面体状的对应的轮廓线，外轮廓的整个表面可以是圆滑过渡的，也可以是非圆滑过渡的，如在圆锥体状或球面体状的表面做了很多凸起和凹槽。
本申请实施例中所述的术语“接触”、“连通”等是指两个或多个构件之间的连接均包括直接地及间接地，即包括“直接地接触”和“间接地接触”；“直接地连通”和“间接地连通”。
附图说明
图1是本申请用于中子捕获治疗的射速整形体的示意图；
图2是本申请匚型结构的冷却装置示意图；
图3是本申请I型结构的冷却装置的示意图；
图4是本申请的靶材结构示意图。
具体实施方式
中子捕获治疗作为一种有效的治疗癌症的手段近年来的应用逐渐增加，其中以硼中子捕获治疗最为常见，供应硼中子捕获治疗的中子可以由核反应堆或加速器供应。本申请的实施例以加速器硼中子捕获治疗为例，加速器硼中子捕获治疗的基本组件通常包括用于对带电粒子(如质子、氘核等)进行加速的加速器、中子产生部与热移除系统以及射束整形体，其中加速带电粒子与金属中子产生部作用产生中子，依据所需的中子产率与能量、可提供的加速带电粒子能量与电流大小、金属中子产生部的物化性等特性来挑选合适的核反应，常被讨论的核反应有7Li(p,n)7Be及9Be(p,n)9B，这两种反应皆为吸热反应。两种核反应的能量阀值分别为1.881MeV和2.055MeV，由于硼中子捕获治疗的理想中子源为keV能量等级的超热中子，理论上若使用能量仅稍高于阀值的质子轰击金属锂中子产生部，可产生相对低能的中子，不须太多的缓速处理便可用于临床，然而锂金属(Li)和铍金属(Be)两种中子产生部与阀值能量的质子作用截面不高，为产生足够大的中子通量，通常选用较高能量的质子来引发核反应。
理想的靶材应具备高中子产率、产生的中子能量分布接近超热中子能区(将在下文详细 描述)、无太多强穿辐射产生、安全便宜易于操作且耐高温等特性，但实际上并无法找到符合所有要求的核反应，本申请的实施例中采用锂金属制成的靶材。但是本领域技术人员熟知的，靶材的材料也可以由其他除了上述谈论到的金属材料之外的金属材料制成。
针对热移除系统的要求则根据选择的核反应而异，如7Li(p,n)7Be因金属靶材(锂金属)的熔点及热导系数差，对热移除系统的要求便较9Be(p,n)9B高。本申请的实施例中采用7Li(p,n)7Be的核反应。由此可知，受到高能量等级的加速质子束照射的靶材的温度必然会大幅上升，从而影响靶材的使用寿命。
无论硼中子捕获治疗的中子源来自核反应堆或加速器带电粒子与靶材的核反应，产生的皆为混合辐射场，即射束包含了低能至高能的中子、光子；对于深部肿瘤的硼中子捕获治疗，除了超热中子外，其余的辐射线含量越多，造成正常组织非选择性剂量沉积的比例越大，因此这些会造成不必要剂量的辐射应尽量降低。除了空气射束品质因素，为更了解中子在人体中造成的剂量分布，本申请的实施例中使用人体头部组织假体进行剂量计算，并以假体射束品质因素来作为中子射束的设计参考，将在下文详细描述。
国际原子能机构(IAEA)针对临床硼中子捕获治疗用的中子源，给定了五项空气射束品质因素建议，此五项建议可用于比较不同中子源的优劣，并供以作为挑选中子产生途径、设计射束整形体时的参考依据。这五项建议分别如下：
超热中子射束通量Epithermal neutron flux>1x 109n/cm2s
快中子污染Fast neutron contamination<2x 10-13Gy-cm2/n
光子污染Photon contamination<2x 10-13Gy-cm2/n
热中子与超热中子通量比值thermal to epithermal neutron flux ratio<0.05
超热中子电流与通量比值epithermal neutron current to flux ratio>0.7
注：超热中子能区在0.5eV到40keV之间，热中子能区小于0.5eV，快中子能区大于40keV。
1、超热中子射束通量：
中子射束通量和肿瘤中含硼药物浓度共同决定了临床治疗时间。若肿瘤含硼药物浓度够高，对于中子射束通量的要求便可降低；反之，若肿瘤中含硼药物浓度低，则需高通量超热中子来给予肿瘤足够的剂量。IAEA对于超热中子射束通量的要求为每秒每平方厘米的超热中子个数大于109，此通量下的中子射束对于目前的含硼药物而言可大致控制治疗时间在一小时内，短治疗时间除了对病人定位和舒适度有优势外，也可较有效利用含硼药物在肿瘤内有限的滞留时间。
2、快中子污染：
由于快中子会造成不必要的正常组织剂量，因此视之为污染，此剂量大小和中子能量呈正相关，因此在中子射束设计上应尽量减少快中子的含量。快中子污染定义为单位超热中子通量伴随的快中子剂量，IAEA对快中子污染的建议为小于2x 10-13Gy-cm2/n。
3、光子污染(γ射线污染)：
γ射线属于强穿辐射，会非选择性地造成射束路径上所有组织的剂量沉积，因此降低γ射线含量也是中子束设计的必要要求，γ射线污染定义为单位超热中子通量伴随的γ射线剂量，IAEA对γ射线污染的建议为小于2x 10-13Gy-cm2/n。
4、热中子与超热中子通量比值：
由于热中子衰减速度快、穿透能力差，进入人体后大部分能量沉积在皮肤组织，除黑色素细胞瘤等表皮肿瘤需用热中子作为硼中子捕获治疗的中子源外，针对脑瘤等深层肿瘤应降低热中子含量。IAEA对热中子与超热中子通量比值建议为小于0.05。
5、超热中子电流与通量比值：
超热中子电流与通量比值代表了超热中子射束的方向性，比值越大表示中子射束前向性佳，高前向性的中子束可减少因中子发散造成的周围正常组织剂量，另外也提高了可治疗深度及摆位姿势弹性。IAEA对中子电流与通量比值建议为大于0.7。
为了使中子捕获治疗的射束整形体在解决靶材冷却问题的同时，能够获得较好的中子射束品质，本申请提供一种用于中子捕获治疗的射束整形体10，所述射速整形体10内设有用于对靶材进行冷却的冷却装置20。
如图1所示，所述射速整形体10包括射束入口11、位于射束整形体10中的加速管12、设于加速管12中的靶材13、邻接于所述靶材13的缓速体14、包围在所述缓速体14外的反射体15、与所述缓速体14邻接的热中子吸收体16、设置在所述射束整形体10内的辐射屏蔽17和射束出口18。所述靶材13与自所述射束入口11入射的质子束发生核反应以产生中子，所述中子形成中子射束，所述中子射束限定一根主轴X。所述缓速体14将自所述靶材13产生的中子减速至超热中子能区，所述反射体15将偏离中子射束主轴X的中子导回至所述缓速体14以提高超热中子射束强度。所述热中子吸收体16用于吸收热中子以避免治疗时与浅层正常组织造成过多剂量。所述辐射屏蔽17用于屏蔽渗漏的中子和光子以减少非照射区的正常组织剂量。
加速器硼中子捕获治疗通过加速器将质子束加速，作为一种优选实施例，靶材13由锂金属制成，质子束加速至足以克服靶材原子核库伦斥力的能量，与靶材13发生7Li(p,n)7Be核反应以产生中子，射束整形体10能将中子缓速至超热中子能区，并降低热中子及快中子含量。
所述缓速体14由具有快中子作用截面大、超热中子作用截面小的材料制成，所述反射体15由具有中子反射能力强的材料制成，热中子吸收体16由与热中子作用截面大的材料制成。作为一种优选实施例，缓速体14由D2O、AlF3、FluentalTM、CaF2、Li2CO3、MgF2和Al2O3中的至少一种制成，反射体15由Pb或Ni中的至少一种制成，热中子吸收体16由6Li制成。辐射屏蔽17包括光子屏蔽171和中子屏蔽172，作为一种优选实施例，辐射屏蔽17包括由铅(Pb)制成的光子屏蔽171和由聚乙烯(PE)制成的中子屏蔽172。
所述加速管12包括嵌入段121和延伸段122，所述靶材13设于加速管12嵌入段121的端部。所述嵌入段121嵌设于缓速体14中，所述延伸段122延伸于缓速体14外侧而被反射体15包围。本实施方式中，加速管12嵌设于缓速体14中，为了使得冷却装置20对嵌入式的加速管12中的靶材13进行冷却的同时保证射束整形体10获得较好的中子射束品质，将冷却装置20设置如下。
所述冷却装置20包括用于冷却靶材13的第一冷却部21、沿加速管12轴线方向延伸而位于加速管12两侧的第二冷却部22和第三冷却部23，所述第二冷却部22向第一冷却部21输入冷却介质，第三冷却部23将第一冷却部21中的冷却介质输出。所述第一冷却部21位于靶材13和缓速体14之间，所述第一冷却部21的一侧与靶材13接触另一侧与缓速体14接触。所述第二冷却部22和第三冷却部23分别自加速管12延伸段122的外侧延伸至加速管12嵌入段121的外侧而分别与第一冷却部21连通并位于缓速体14中。也就是说，第一冷却部21位于加速管12的嵌入段121的端部而位于靶材13一侧并与靶材13直接接触，所述第二冷却部22和第三冷却部23分别位于加速管12的上下两侧而分别与第一冷却部21连通，从而使得整个冷却装置20呈匚型结构设置。本实施方式中，所述第一冷却部21与靶材13平面接触，第二冷却部22和第三冷却部23都是由铜制成的管状结构，且第二冷却部22和第三冷却部23分别垂直于所述第一冷却部21和靶材13的接触平面(结合图2)。
所述第一冷却部21包括第一接触部211、第二接触部212及位于第一接触部211和第二接触部212之间的供冷却介质通过的冷却槽213。所述第一接触部211与靶材13直接接触，所述第二接触部212与缓速体14可以是直接接触也可以通过空气间接接触。所述冷却槽213具有与第二冷却部22连通的输入槽214及与第三冷却部23连通的输出槽215。所述第一接触部211由导热材料制成。所述输入槽214的上边沿位于第二冷却部22的上边沿的上方，所述输出槽215的下边沿位于第三冷却部23的下边沿的下方。这样设置的好处是，冷却装置20能够更加顺畅地将冷却水输入冷却槽213中并且较及时地对靶材13进行冷却，而受热后的冷却水也能够较为顺畅的从冷却槽213中输出，同时，还能够在一定程度上降低冷却槽213中冷却水的水压。
当然，也可将冷却装置设置成I型结构对嵌入式的加速管12中的靶材13进行冷却。所述I型冷却装置20中的第一冷却部21’与匚型冷却装置20的第一冷却部21设置相同，不同之处在于，所述I型冷却装置20的第二冷却部22’和第三冷却部23’与第一冷却部21’位 于同一平面，且第二冷却部22’和第三冷却部23分别沿与加速管12轴线垂直的方向穿设出缓速体14，也就是上述I型结构(如图3所示)。所述I型结构的冷却装置20虽然也能够实现对靶材13的冷却，但是需要在缓速体14上设置让第二冷却部22’和第三冷却部23’穿过的槽24，装配起来比较复杂。并且将冷却装置设置为I型结构后的射束整形体10的中子通量和空气中射束品质因素表现相较于将冷却装置设置成匚型结构后的射束整形体10的中子通量和空气中射束品质因素表现差。
现以缓速体14采用AlF----3(2.78g/cm---)材料制成为例，采用MCNP软件(是由美国洛斯阿拉莫斯国家实验室(LosAlamos National Laboratory)开发的基于蒙特卡罗方法的用于计算三维复杂几何结构中的中子、光子、带电粒子或者耦合中子/光子/带电粒子输运问题的通用软件包)分别对设置匚型和I型冷却装置后的射束整形体进行模拟计算：
其中，如下表一示出了空气中射束品质因素在这两种实施例中的表现：
表一：空气中射束品质因素
Figure PCTCN2016111346-appb-000001
注：本实施例为保守地评估超热中子通量及快中子污染，将超热中子能区设定为0.5eV到10keV之间，热中子能区设定为小于0.5eV，快中子能区设定为大于10keV。
其中，如下表二示出了中子通量在这两种实施例中的表现：
表二：中子通量(n/cm2-mA)
Figure PCTCN2016111346-appb-000002
注：本实施例为保守地评估超热中子通量及快中子污染，将超热中子能区设定为0.5eV到10keV之间，热中子能区设定为小于0.5eV，快中子能区设定为大于10keV。
所述靶材13包括锂靶层131和位于锂靶层131一侧用于防止锂靶层131氧化的抗氧化层132。所述靶材13的抗氧化层132由Al或者不锈钢制成。第一接触部211由导热材料(如Cu、Fe、Al等导热性能好的材料)或既能导热又能抑制发泡的材料制成，第二接触部由抑制发泡的材料制成，抑制发泡的材料或既能导热又能抑制发泡的材料由Fe、Ta或V的任一种制成。靶材13受到高能量等级的加速质子束照射温度升高发热，所述第一接触部211将热量导出，并通过流通在冷却槽213中的冷却介质将热量带出，从而对靶材13进行冷却。在本实施方式中，所述冷却介质为水。
作为一种优选的实施方式，将所述缓速体14设置成具有至少一个锥体状140的结构。所述缓速体14具有第一端部141和第二端部142，所述锥体状140具有位于第一端部141和第二端部142之间的第三端部143和连接第一端部141和第三端部143的主体部144。所述加速管12的嵌入段121位于锥体状140的第一端部141和第三端部143之间，所述第一冷却部21位于靶材13和锥体状140的第三端部143之间。这样设置的好处是，能够比较合理的控制缓速体14的尺寸，使产生的中子束达到较好的缓速效果，同时使射束整形体获得较好的射束品质。具体来说是，因为第一冷却部21位于靶材13和锥体状140的第三端部143之间，位于第三端部143之后部分的缓速体14能够对前向性较好且能量较高的中子进行缓速，也就是说这样的设置对于前向性较好且能量较高的中子仍然留有较长尺寸的缓速体足以对中子进行充分缓速；而对于偏离中子射束主轴X的中子，当偏离射束主轴X的中子经过主体部144缓速后迁移到反射体15，反射体15通过缓速体14的锥体状设计以一定的角度将偏离射束主轴X的中子反射回中子射束主轴X，同时锥体状设计可避免能量较低的中子在反射回射束主轴X的路径上过度缓速，在提升前向性高的中子的缓速效果的同时，可维持中子射束的强度，继而保证射束整形体10得到较好的中子射束品质。
本申请实施例中所述缓速体的“锥体”或“锥体状”结构是指缓速体沿着图示方向的一侧到另一侧其外轮廓的整体趋势逐渐变小的结构，外轮廓的其中一条轮廓线可以是线段，如圆锥体状的对应的轮廓线，也可以是圆弧，如球面体状的对应的轮廓线，外轮廓的整个表面可以是圆滑过渡的，也可以是非圆滑过渡的，如在圆锥体状或球面体状的表面做了很多凸起和凹槽。
本申请揭示的中子捕获治疗系统并不局限于以上实施例所述的内容以及附图所表示的结构。在本申请的基础上对其中构件的材料、形状及位置所做的显而易见地改变、替代或者修改，都在本申请要求保护的范围之内。

Claims (10)

  1. 一种用于中子捕获治疗的射束整形体，所述中子捕获治疗包括用于给质子束加速的加速管，所述射束整形体包括射束入口、设于加速管中的靶材、邻接于所述靶材的缓速体、包围在所述缓速体外的反射体、与所述缓速体邻接的热中子吸收体、设置在所述射束整形体内的辐射屏蔽和射束出口，所述靶材与自所述射束入口入射的质子束发生核反应以产生中子，所述中子形成中子射束，所述缓速体将自所述靶材产生的中子减速至超热中子能区，所述反射体将偏离的中子导回至所述缓速体以提高超热中子射束强度，所述热中子吸收体用于吸收热中子以避免治疗时与浅层正常组织造成过多剂量，所述辐射屏蔽用于屏蔽渗漏的中子和光子以减少非照射区的正常组织剂量，其特征在于，所述射束整形体还具有冷却装置，所述冷却装置包括用于冷却靶材的第一冷却部、分别沿平行于加速管轴线方向延伸并与第一冷却部连通的第二冷却部和第三冷却部，所述第一冷却部与靶材平面接触，所述第二冷却部向第一冷却部输入冷却介质，第三冷却部将第一冷却部中的冷却介质输出。
  2. 根据权利要求1所述的用于中子捕获治疗的射束整形体，其特征在于：所述加速管包括嵌入段和延伸段，所述靶材设于加速管嵌入段的端部，所述嵌入段嵌设于缓速体中，所述延伸段延伸于缓速体外侧而被反射体包围，所述第一冷却部位于靶材和缓速体之间，所述第二冷却部和第三冷却部沿平行于加速管轴线方向延伸至加速管嵌入段的外侧而位于射束整形体中。
  3. 根据权利要求1所述的中子捕获治疗系统的射束整形体，其特征在于：所述第一冷却部位于加速管的端部而与所述靶材平面接触，所述第二冷却部和第三冷却部分别位于加速管的上下两侧而与第一冷却部形成匚型结构。
  4. 根据权利要求1所述的用于中子捕获治疗的射束整形体，其特征在于：所述第二冷却部和第三冷却部都是由铜制成的管状结构，所述第二冷却部和第三冷却部分别垂直于靶材和第一冷却部的接触平面。
  5. 根据权利要求1所述的用于中子捕获治疗的射束整形体，其特征在于：所述第一冷却部包括与靶材直接接触的第一接触部、与缓速体接触的第二接触部及位于第一接触部和第二接触部之间的供冷却介质通过的冷却槽，所述冷却槽具有与第二冷却部连通的输入槽及与第三冷却部连通的输出槽。
  6. 根据权利要求5所述的用于中子捕获治疗的射束整形体，其特征在于：所述输入槽的上边沿位于第二冷却部的上边沿的上方，所述输出槽的下边沿位于第三冷却部的下边沿的下方。
  7. 根据权利要求2所述的用于中子捕获治疗的射束整形体，其特征在于：所述缓速体具有至少一个锥体状，所述缓速体具有第一端部和第二端部，所述锥体状具有位于第一端部和第二端部之间的第三端部及连接第一端部和第三端部的主体部，所述加速管的嵌入段位于锥体状的第一端部和第三端部之间，所述第一冷却部位于靶材和锥体状的第三端部之间。
  8. 根据权利要求5所述的用于中子捕获治疗的射束整形体，其特征在于：所述靶材包括锂靶层和位于锂靶层一侧用于防止锂靶层氧化的抗氧化层。
  9. 根据权利要求5所述的用于中子捕获治疗的射束整形体，其特征在于：所述第一接触部由 导热材料或既能导热又能抑制发泡的材料制成，所述第二接触部由抑制发泡的材料制成。
  10. 根据权利要求8所述的中子捕获治疗系统的射束整形体，其特征在于：所述抗氧化层由Al或者不锈钢制成，当所述第一接触部由既能导热又能抑制发泡的材料制成时，所述第一接触部选自Fe、Ta或V的任一种，所述第二接触部由Fe、Ta或V的任一种制成，所述冷却介质为水。
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