CN108926784B - Neutron capture treatment system and target for particle beam generating device - Google Patents
Neutron capture treatment system and target for particle beam generating device Download PDFInfo
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Classifications
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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
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
-
- 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
- H05H6/00—Targets for producing nuclear reactions
-
- 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
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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
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N2005/1019—Sources therefor
- A61N2005/1022—Generators, e.g. X-ray tubes
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- 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
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N2005/1019—Sources therefor
- A61N2005/1025—Wires
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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
- A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
- A61N2005/109—Neutrons
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N2005/1092—Details
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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
- A61N2005/1092—Details
- A61N2005/1094—Shielding, protecting against radiation
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- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Physics & Mathematics (AREA)
- General Health & Medical Sciences (AREA)
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- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
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Abstract
The invention provides a neutron capture treatment system and a target for a particle beam generating device, which can improve the heat dissipation performance of the target, reduce bubbling and prolong the service life of the target. The neutron capture treatment system comprises a neutron generating device and a beam shaping body, wherein the neutron generating device comprises an accelerator and a target, charged particle rays generated by acceleration of the accelerator react with the target to generate neutron rays, the target comprises an action layer, a base layer and a heat dissipation layer, the action layer reacts with the charged particle rays to generate neutron rays, the base layer supports the action layer, and the heat dissipation layer comprises a tubular piece formed by a plurality of tubes in parallel.
Description
Technical Field
The present invention relates, in one aspect, to a radiation irradiation system, and in particular, to a neutron capture therapy system; another aspect of the invention relates to a target for a radiation irradiation system, in particular a target for a particle beam generating apparatus.
Background
With the development of atomic science, radiation therapy such as cobalt sixty, linac, electron beam, etc. has become one of the main means for cancer therapy. However, the traditional photon or electron treatment is limited by the physical condition of the radioactive rays, and a large amount of normal tissues on the beam path can be damaged while killing tumor cells; in addition, due to the different sensitivity of tumor cells to radiation, traditional radiotherapy often has poor therapeutic effects on malignant tumors with relatively high radiation resistance (such as glioblastoma multiforme (glioblastoma multiforme) and melanoma (melanoma)).
In order to reduce radiation damage to normal tissue surrounding a tumor, the concept of target treatment in chemotherapy (chemotherapy) has been applied to radiotherapy; for tumor cells with high radiation resistance, radiation sources with high relative biological effects (relative biological effectiveness, RBE) such as proton therapy, heavy particle therapy, neutron capture therapy, etc. are also actively developed. The neutron capture treatment combines the two concepts, such as boron neutron capture treatment, and provides better cancer treatment selection than the traditional radioactive rays by means of the specific aggregation of boron-containing medicaments in tumor cells and the accurate neutron beam regulation.
In the accelerator boron neutron capture treatment, the accelerator boron neutron capture treatment accelerates a proton beam through an accelerator, the proton beam accelerates to energy enough to overcome coulomb repulsion of a target atomic nucleus, and nuclear reaction occurs to the target to generate neutrons, so that the target can be irradiated by the accelerated proton beam with very high energy level in the neutron generation process, the temperature of the target can be greatly increased, and meanwhile, the metal part of the target is easy to foam, so that the service life of the target is influenced.
Therefore, a new solution is needed to solve the above-mentioned problems.
Disclosure of Invention
In order to solve the above problems, the present invention provides a neutron capture therapy system, including a neutron generating device and a beam shaping body, the neutron generating device including an accelerator and a target, the accelerator accelerating charged particle beams generated to act with the target to generate neutron beams, the beam shaping body including a reflector, a retarder, a thermal neutron absorber, a radiation shield and a beam outlet, the retarder decelerating neutrons generated from the target to an epithermal neutron energy region, the reflector surrounding the retarder and guiding deflected neutrons back to the retarder to increase epithermal neutron beam intensity, the thermal neutron absorber for absorbing thermal neutrons to avoid excessive dose with shallow normal tissues during therapy, the radiation shield surrounding the beam outlet disposed at the rear of the reflector for shielding leaked neutrons and photons to reduce normal tissue dose of non-irradiated regions, the target including an action layer, a base layer and a heat dissipation layer, the action layer acting with the charged particle beams to generate neutron beams, the base layer supporting the action layer, the base layer including a plurality of tubular heat dissipation layers side by side. The heat dissipation structure of the tubular piece is adopted, so that the heat dissipation surface is increased, the heat dissipation effect is improved, and the service life of the target is prolonged.
Preferably, the neutron capture treatment system further comprises a treatment table and a collimator, wherein the neutron rays generated by the neutron generating device are irradiated to a patient on the treatment table through the beam shaping body, a radiation shielding device is arranged between the patient and the beam outlet so as to shield radiation of the beam coming out of the beam outlet to normal tissues of the patient, and the collimator is arranged at the rear part of the beam outlet so as to converge the neutron rays. The beam shaping body is internally provided with a first cooling pipe and a second cooling pipe, the target is provided with a cooling inlet, a cooling outlet and a cooling channel arranged between the cooling inlet and the cooling outlet, one ends of the first cooling pipe and the second cooling pipe are respectively connected with the cooling inlet and the cooling outlet of the target, the other ends of the first cooling pipe and the second cooling pipe are connected to an external cooling source, and at least one part of the cooling channel is formed inside each pipe of the tubular piece, so that the heat dissipation effect is further enhanced, and the service life of the target is prolonged.
Further, the target is located in the beam shaping body, the accelerator is provided with an accelerating tube for accelerating the charged particle rays, the accelerating tube stretches into the beam shaping body along the charged particle rays and sequentially penetrates through the reflector and the buffer body, the target is located in the buffer body and at the end of the accelerating tube so as to obtain better neutron beam quality, and the first cooling tube and the second cooling tube are arranged between the accelerating tube and the reflector and the buffer body.
In another aspect, the present invention provides a target for a particle beam generating apparatus, the target comprising an active layer for generating the particle beam, a base layer supporting the active layer, and a heat dissipation layer comprising a tubular member composed of a plurality of tubes side by side. The heat dissipation structure of the tubular piece is adopted, so that the heat dissipation surface is increased, the heat dissipation effect is improved, and the service life of the target is prolonged.
Preferably, the particle beam generating device is a neutron beam generating device, the material of the action layer is Li or an alloy thereof, and the action layer generates an incident proton beam 7 Li(p,n) 7 Be nuclear reactions to produce neutrons; or the material of the action layer is Be or alloy thereof, and the action layer and the incident proton beam generate 9 Be(p,n) 9 The B nuclei react to produce neutrons.
Preferably, the target further comprises an oxidation-resistant layer, wherein the oxidation-resistant layer is used for preventing oxidation of the acting layer, and the material of the oxidation-resistant layer comprises at least one of Al, ti, be and alloys thereof or stainless steel, is not easy to corrode by the acting layer, and can reduce loss of incident proton beams and heat caused by the proton beams; an adhesion layer is arranged between the acting layer and the base layer, and the adhesion layer is made of at least one of Cu, al, mg or Zn, so that the adhesion between the base layer and the acting layer is improved; the heat dissipation layer is made of a heat conduction material or a material capable of conducting heat and inhibiting foaming; the base layer is made of a foaming-inhibiting material; the foaming-inhibiting material or the material capable of conducting heat and inhibiting foaming comprises at least one of Fe, ta or V, the heat conducting material comprises at least one of Cu, fe and Al, the heat dissipation layer and the base layer are connected through a HIP process, and the acting layer and the base layer are connected through a casting, evaporation or sputtering process.
As another preferred feature, the tubular member is simultaneously used as the base layer, the material of the tubular member is Ta, and the active layer is connected to the tubular member by vapor deposition or sputtering.
Preferably, the action layer on each tube of the tubular member covers at least 1/4 of the outer circumference of the tube, the action layer forming an angle of at least 45 degrees with the center line of the tube in the circumferential direction, the tubular member forming a connection between adjacent tubes, the connection being composed of a base layer, an action layer and an oxidation resistant layer.
Preferably, the heat dissipation layer further comprises a support piece, wherein the support piece is made of Cu, and plays an additional heat dissipation role while supporting and positioning; the tubular piece is welded, press-fitted or detachably connected with the support piece, and the target material can be partially replaced by adopting the detachable connection, so that the service life of the target material is prolonged, and the treatment cost of a patient is reduced; the support and/or the tubular member are provided with cooling channels, so that the heat dissipation effect is further enhanced, and the service life of the target is prolonged.
Further, the support member includes a first support portion and a second support portion provided at both ends of the tubular member, the first support portion having a cooling inlet and a first cooling passage, the second support portion having a cooling outlet and a second cooling passage, a cooling medium entering from the cooling inlet through the first cooling passage into each tube interior of the tubular member and then exiting from the cooling outlet through the second cooling passage, the cooling medium being water, the support member includes a third support portion connecting the first and second support portions, the third support portion being in contact with one side of the tubular member opposite to the side on which the acting layer is connected, the third support portion having a cooling passage, the cooling medium passing through only the support member or through both the tube interior and the third support portion of the support member or through both the tube interior and the first, second and third support portions of the support member.
The target radiating part adopts the tubular piece, so that the radiating area can be increased, the target radiating effect is improved, the service life of the target is prolonged, and the treatment cost of patients is reduced; ta is used as the material of the base layer, so that foaming can be reduced; the inside of the tubular member serves as a cooling passage, so that the heat dissipation effect can be further increased.
Drawings
FIG. 1 is a schematic diagram of a neutron capture therapy system according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a target in an embodiment of the invention;
FIG. 3 is an enlarged schematic view of a portion of the target of FIG. 2;
FIG. 4 is a schematic view of the heat dissipation layer of the target in FIG. 2 from the direction A;
FIG. 5a is a schematic view of a first embodiment of the inner wall of the heat dissipation channel of the target in FIG. 2;
FIG. 5B is a schematic view along the axis B-B of a first embodiment of the inner wall of the heat dissipation channel of the target of FIG. 2;
FIG. 6a is a schematic diagram of a second embodiment of the inner wall of the heat dissipation channel of the target in FIG. 2;
FIG. 6b is a schematic view along the axis C-C of a second embodiment of the inner wall of the heat dissipation channel of the target of FIG. 2;
fig. 7 is a schematic diagram of a third embodiment of the inner wall of the heat dissipation channel of the target in fig. 2.
Detailed Description
The present invention is described in further detail below with reference to the drawings to enable those skilled in the art to practice the invention by referring to the description.
As shown in fig. 1, the neutron capture treatment system in this embodiment is preferably a boron neutron capture treatment system 100 that includes a neutron production device 10, a beam shaper 20, a collimator 30, and a treatment table 40. The neutron production device 10 includes an accelerator11 and a target T, the accelerator 11 accelerates charged particles (such as protons, deuterons, etc.) to produce a charged particle beam P such as a proton wire, the charged particle beam P irradiates the target T and reacts with the target T to produce a neutron beam (neutron beam) N, and the target T is preferably a metal target. Suitable nuclear reactions are selected according to the required neutron yield and energy, the available energy and current of the accelerated charged particles, the physicochemical properties of the metal target, etc., and are usually discussed as 7 Li(p,n) 7 Be and Be 9 Be(p,n) 9 And B, performing an endothermic reaction. The energy threshold values of the two nuclear reactions are respectively 1.881MeV and 2.055MeV, because the ideal neutron source for boron neutron capture treatment is epithermal neutrons with the energy level of keV, in theory, if protons with the energy only slightly higher than the threshold value are used for bombarding a metal lithium target material, relatively low-energy neutrons can Be generated, the clinical application can Be realized without too much retarding treatment, however, the proton action cross sections of the two targets of lithium metal (Li) and beryllium metal (Be) and the threshold energy are not high, and in order to generate enough neutron flux, protons with higher energy are generally selected to trigger the nuclear reactions. The ideal target should have high neutron yield, a neutron energy distribution close to that of the epithermal neutron energy region (described in detail below), no too much intense penetrating radiation, safety, low cost, easy operation, and high temperature resistance, but practically no nuclear reaction meeting all the requirements can be found. The target T may also Be made of a metallic material other than Li, be, such as Ta or W, an alloy thereof, or the like, as is well known to those skilled in the art. The accelerator 11 may be a linear accelerator, a cyclotron, a synchrotron, or a synchrocyclotron.
The neutron beam N generated by the neutron generator 10 is irradiated to the patient 200 on the treatment table 40 through the beam shaping body 20 and the collimator 30 in this order. The beam shaping body 20 can adjust the beam quality of the neutron beam N generated by the neutron generating device 10, and the collimator 30 is used for converging the neutron beam N, so that the neutron beam N has higher targeting property in the treatment process. The beam shaping body 20 further comprises a reflector 21, a retarder 22, a thermal neutron absorber 23, a radiation shield 24 and a beam outlet 25, and neutrons generated by the neutron generating device 10 can meet therapeutic requirements except epithermal neutrons due to a wide energy spectrumThe neutron and photon content of other kinds needs to be reduced as much as possible to avoid hurting operators or patients, so the neutrons from the neutron generator 10 need to adjust the fast neutron energy thereof to the epithermal neutron energy region through the retarder 22, the retarder 22 is made of a material with a large fast neutron action cross section and a small epithermal neutron action cross section, in this embodiment, the retarder 22 is made of D 2 O、AlF 3 、Fluental、CaF 2 、Li 2 CO 3 、MgF 2 And Al 2 O 3 At least one of them; the reflector 21 surrounds the retarder 22 and reflects neutrons diffused around through the retarder 22 back to the neutron beam N to improve neutron utilization, and is made of a material having strong neutron reflection capability, in this embodiment, the reflector 21 is made of at least one of Pb or Ni; the rear part of the retarder 22 is provided with a thermal neutron absorber 23 which is made of a material with a large cross section for reacting with thermal neutrons, in the embodiment, the thermal neutron absorber 23 is made of Li-6, and the thermal neutron absorber 23 is used for absorbing the thermal neutrons passing through the retarder 22 so as to reduce the content of thermal neutrons in a neutron beam N and avoid excessive dosage caused by shallow normal tissues during treatment; a radiation shield 24 is arranged at the rear of the reflector around the beam outlet 25 for shielding neutrons and photons leaking from parts outside the beam outlet 25, the material of the radiation shield 24 comprising at least one of photon shielding material and neutron shielding material, in this embodiment the material of the radiation shield 24 comprising photon shielding material lead (Pb) and neutron shielding material Polyethylene (PE). It will be appreciated that other configurations of the beam shaping body 20 are possible, as long as the epithermal neutron beam required for treatment is obtained. The collimator 30 is disposed at the rear of the beam outlet 25, and the epithermal neutron beam exiting from the collimator 30 irradiates the patient 200, is retarded to thermal neutrons after passing through the shallow normal tissue, and reaches the tumor cells M, it will be appreciated that the collimator 30 may be omitted or replaced by other structures, and the neutron beam exits from the beam outlet 25 to directly irradiate the patient 200. In this embodiment, the radiation shielding device 50 is further disposed between the patient 200 and the beam outlet 25 to shield the normal tissue of the patient from the beam exiting from the beam outlet 25, and it is understood that the radiation shielding device 50 may not be disposed.
After the patient 200 takes or injects the boron-containing (B-10) drug, the boron-containing drug is selectively accumulated in the tumor cells M, and then the boron-containing (B-10) drug is utilized to have the characteristic of high capture section for thermal neutrons, by 10 B(n,α) 7 Li neutron capture and nuclear fission reaction generation 4 He (He) 7 Li two heavy charged particles. The average energy of the two charged particles is about 2.33MeV, the particles have high linear transfer (Linear Energy Transfer, LET) and short range characteristics, and the linear energy transfer and range of the alpha short particles are 150keV/μm and 8 μm respectively 7 The Li heavy-load particles are 175 keV/mum and 5 μm, and the total range of the two particles is approximately equal to one cell size, so that the radiation injury to organisms can be limited at the cell level, and the aim of killing tumor cells locally can be fulfilled on the premise of not causing too great injury to normal tissues.
The structure of the target T will be described in detail with reference to fig. 2, 3 and 4.
The target T is disposed between the accelerator 11 and the beam shaping body 20, the accelerator 11 has an accelerating tube 111 for accelerating the charged particle beam P, in this embodiment, the accelerating tube 111 extends into the beam shaping body 20 along the direction of the charged particle beam P and sequentially passes through the reflector 21 and the retarder 22, and the target T is disposed in the retarder 22 and is located at an end of the accelerating tube 111, so as to obtain better neutron beam quality.
The target T includes a heat dissipation layer 12, a base layer 13, and an action layer 14, the action layer 14 reacting with the charged particle rays P to generate neutron rays, the base layer 13 supporting the action layer 14. In this embodiment, the material of the active layer 14 is Li or an alloy thereof, the charged particle beam P is a proton wire, and the target T further includes an antioxidation layer 15 located on one side of the active layer 14 for preventing oxidation of the active layer, and the base layer 13 can simultaneously inhibit foaming caused by the incident proton wire, and the charged particle beam P sequentially passes through the antioxidation layer 15, the active layer 14 and the base layer 13 along the incident direction. The material of the oxidation-resistant layer 15 is considered to be less susceptible to corrosion by the active layer and is capable of reducing loss of the incident proton beam and heat generation caused by the proton beam, such as at least one of Al, ti, and alloys thereof, or stainless steel. In this embodiment, the antioxidation layer 15 is capable of being simultaneously nuclear-reversed with proton generationThe material can further increase neutron yield while playing the role, at the moment, the oxidation-resistant layer is a part of the active layer, for example, be or the alloy thereof is adopted, the energy of the incident proton beam is higher than the energy threshold value of nuclear reaction with Li and Be, two different nuclear reactions are respectively generated, 7 Li(p,n) 7 be and Be 9 Be(p,n) 9 B, a step of preparing a composite material; in addition, be has high melting point and good heat conduction property, the melting point is 1287 ℃, the thermal conductivity is 201W/(m K), the high temperature resistance and heat dissipation performance relative to Li (the melting point is 181 ℃, the thermal conductivity is 71W/(m K)) are greatly advantageous, the service life of the target material is further prolonged, the reaction threshold value of the reaction with the (p, n) nuclear reaction of protons is about 2.055MeV, most accelerator neutron sources adopting proton beams are higher than the reaction threshold value, and beryllium targets are the best choice besides lithium targets. Neutron yield is improved due to the presence of Be compared to oxidation resistant layers using other materials, such as Al. In the embodiment, the energy of the proton line is 2.5MeV-5MeV, which can generate a higher action cross section with a lithium target, and meanwhile, excessive fast neutrons can not be generated, so that better beam quality is obtained; the thickness of the acting layer 14 is 80-240 mu m, and the acting layer can fully react with protons, so that energy deposition caused by excessive thickness can not be caused, and the heat dissipation performance of the target is not affected; the thickness of the oxidation-resistant layer 15 is 5 μm to 25 μm while ensuring a low manufacturing cost while achieving the above-described effects. In the comparative experiments, proton beams of 2.5MeV, 3MeV, 3.5MeV, 4MeV, 4.5MeV, 5MeV were respectively simulated by using monte carlo software, and the antioxidant layer 15, the active layer 14 (Li), and the base layer 13 (Ta, which will Be described later) were sequentially injected from a direction perpendicular to the active surface of the target T, the material of the antioxidant layer 15 was compared with Be by Al, the thicknesses of the antioxidant layer 15 were respectively 5 μm, 10 μm, 15 μm, 20 μm, 25 μm, and the active layer 14 were respectively 80 μm, 120 μm, 160 μm, 200 μm, 240 μm, and the thicknesses of the base layer 12 had little influence on the neutron yield, and the obtained neutron yield (i.e., the number of neutrons generated per proton) was as shown in table 1, table 2. The calculation results of neutron yield improvement ratio of the use of Be as the lithium target oxidation-resistant layer relative to Al are shown in Table 3, from which it is known that the neutron yield phase when Be is used as the oxidation-resistant layer materialWith a significant increase in Al, a neutron yield of 7.31E-05n/proton-5.61E-04n/proton can be obtained.
TABLE 1 neutron yield (n/proton) E as incident proton line energy using Al as the lithium target oxidation barrier
TABLE 2 neutron yield (n/proton) E as incident proton line energy using Be as the lithium target oxidation barrier
TABLE 3 neutron yield improvement ratio relative to Al using Be as the lithium target oxidation barrier E is the incident proton line energy
The heat dissipation layer 12 is made of a heat conduction material (such as a material with good heat conduction performance such as Cu, fe, al and the like) or a material capable of conducting heat and inhibiting foaming; the base layer 13 is made of a foaming-suppressing material; the foaming-inhibiting material or the material capable of both heat conduction and foaming inhibition includes at least one of Fe, ta or V. The heat dissipation layer may have various structures, such as a flat plate, in this embodiment, the heat dissipation layer 12 includes a tubular member 121 and a supporting member 122, the materials of the tubular member 121 and the supporting member 122 are all Cu, which has better heat dissipation performance and lower cost, the tubular member 121 is composed of a plurality of tubes side by side and is positioned and installed by the supporting member 122, the supporting member 122 is fixed in the retarder 22 or at the end of the accelerating tube 111 by a connecting member such as a bolt or a screw, etc., it can be understood that other detachable connection may be adopted, so that the target material can be replaced conveniently. The heat dissipation area is increased by the structure of the tube, the heat dissipation effect is improved, and the service life of the target material is prolonged. The heat dissipation layer 12 further has a cooling channel P through which a cooling medium flows, in this embodiment, the cooling medium is water, the inside of the tube forming the tubular member 121 forms at least partially the cooling channel P, the cooling medium flows through the inside of the tube to take away heat, and the inside of the tube serves as the cooling channel, so that the heat dissipation effect is further enhanced, and the service life of the target is prolonged. The shape, number and size of the tubes are determined according to the size of the actual target, and only 4 circular tubes are schematically drawn in the figure, and it can be understood that the tubes can also be square tubes, polygonal tubes, elliptical tubes and the like and combinations thereof; adjacent tubes may be immediately adjacent with their outer surfaces in contact with each other or may be spaced apart; the cross-sectional shape of the inner bore of the tube may also be varied, such as circular, polygonal, elliptical, etc., and different cross-sections may also have different shapes. Because the diameter of each pipe is smaller in the actual manufacturing of the tubular member, and the cooling channel is arranged in the tubular member, the conventional production process has higher difficulty, and the tubular member is obtained by adopting additive manufacturing in the embodiment, so that the forming of a micro structure and a complex structure is facilitated. Firstly, three-dimensional modeling is carried out on a tubular member, three-dimensional model data of the tubular member are input into a computer system and layered into two-dimensional slice data, raw materials (such as copper powder) are manufactured layer by layer through a computer-controlled additive manufacturing system, and a three-dimensional product is finally obtained after superposition.
When the base layer 13 is made of Ta, the heat dissipation effect is achieved, bubbling can be reduced, inelastic scattering of protons and Li is restrained to release gamma, and excessive protons are prevented from passing through the target; in this embodiment, the material of the base layer 13 is Ta-W alloy, which can obviously improve the disadvantages of low pure tantalum strength and poor thermal conductivity while maintaining the excellent performance of Ta, so that the heat generated by the nuclear reaction of the acting layer 14 can be timely conducted away from the base layer, and at this time, the heat dissipation layer may also be at least partially made of the same material or integrally constructed with the base layer. The weight percentage of W in the Ta-W alloy is 2.5% -20%, so that the foaming inhibition characteristic of the base layer is ensured, and meanwhile, the base layer has higher strength and heat conductivity, and the service life of the target is further prolonged. Ta-W alloy (e.g., ta-2.5wt% W, ta-5.0wt% W, ta-7.5wt% W, ta-10wt% W, ta-12wt% W, ta-20wt% W, etc.) is formed into a plate-like base layer 13 using powder metallurgy, forging, pressing, etc., the base layer having a thickness of at least 50 μm at a proton line energy of 1.881MeV-10MeV to sufficiently absorb excess protons.
In this embodiment, the manufacturing process of the target T is as follows:
s1: pouring liquid lithium metal onto the base layer 13 to form an action layer 14, or adopting evaporation or sputtering and other treatments, wherein an extremely thin adhesion layer 16 can be arranged between the lithium and the tantalum, the adhesion layer 16 comprises at least one of Cu, al, mg or Zn, and the adhesion between the base layer and the action layer can be improved by adopting the evaporation or sputtering and other treatments;
s2: subjecting the base layer 13 and the tubular part 121 of the heat dissipation layer 12 to a HIP (Hot Isostatic Pressing: hot isostatic pressing) treatment;
s3: the antioxidation layer 15 is simultaneously subjected to HIP treatment or by other processes to seal the base layer 13 to form a cavity and/or to enclose the active layer 14;
s4: the support 122 is connected to the tubular member 121 by welding, press fitting, or the like.
The steps S1, S2, S3 and S4 are not sequential, for example, the antioxidation layer 15 and the base layer 13 may be HIP treated first or the base layer 13 may be closed by other processes to form a cavity, and then the liquid lithium metal is poured into the cavity to form the active layer 14. It will be appreciated that the support 122 may be omitted, and a plurality of tubes may be welded or otherwise connected and fixed in sequence. The base layer 13, the acting layer 14 and the oxidation resistant layer 15 on each tube are respectively molded, the tubular piece is connected with the supporting piece 122 in a positioning way, the whole of the base layer 13, the acting layer 14 and the oxidation resistant layer 15 formed on each tube after connection is possibly discontinuous, the connecting part 17 is required to be formed between the adjacent tubes, the connecting part 17 is also composed of the base layer 13, the acting layer 14 and the oxidation resistant layer 15, the whole target is divided into a plurality of independent acting parts, the bubbling phenomenon of the metal oxidation resistant layer is further reduced, at the moment, the supporting piece 122 and the tubular piece 121 are connected in a detachable way, the target T can be partially replaced, the service life of the target is prolonged, and the treatment cost of a patient is reduced; it will be appreciated that the base layer 13, the active layer 14 and the oxidation resistant layer 15 on each tube may also be integrally formed and then connected to the tubular member, so that the active layer of the target T is integrally continuous after connection, which is advantageous for the charged particle beam P to act on the target T, and the support 122 and the tubular member 121 may also be integrally obtained by additive manufacturing, thereby reducing the processing and assembly difficulties. The shape of the cross section of the whole formed by the base layer 13, the acting layer 14 and the oxidation resistant layer 15 perpendicular to the central line of the pipe can be various, for example, the outline of the outer surface of the side, which is connected with the base layer 13, the acting layer 14 and the oxidation resistant layer 15, of the tubular piece is consistent, in the embodiment, the outer surface is arc-shaped, so that the acting area of the target T and the charged particle rays P and the contact area of the heat dissipation layer 12 and the base layer 13 are increased, and the heat conduction area is increased; the active layer 14 on each tube covers at least 1/4 of the outer circumference of the tube, i.e. the active layer has an angle alpha of at least 45 degrees in the circumferential direction with the centre line of the tube.
IN this embodiment, the supporting member 122 includes a first supporting portion 1221 and a second supporting portion 1222 symmetrically disposed at both ends of the tubular member 121, having a cooling inlet IN and a cooling outlet OUT, respectively, and the cooling passage P communicates with the cooling inlet IN and the cooling outlet OUT. The cooling passages P include a first cooling passage P1 on the first support portion, a second cooling passage P2 on the second support portion, and a third cooling passage P3 formed inside the tube constituting the tubular member 121. The cooling medium enters from the cooling inlet IN on the first support 1221, enters the inside of each tube constituting the tubular member 121 through the first cooling passage P1 at the same time, and then exits from the cooling outlet OUT through the second cooling passage P2 on the second support. The target T is heated by the high-energy-level accelerated proton beam irradiation temperature rise, and the base layer and the heat dissipation layer conduct heat out and carry the heat out through the cooling medium flowing in the tubular member and the supporting member, thereby cooling the target T.
It will be appreciated that other arrangements of the first cooling passage P1 and the second cooling passage P2 are possible, such as a cooling medium entering from the cooling inlet IN on the first support 1221 sequentially passing through the inside of the respective tubes constituting the tubular member 121 and finally exiting from the cooling outlet OUT on the second support; the cooling medium may be directly introduced into or withdrawn from the tubular member instead of passing through the support member, and at this time, the cooling inlet IN and the cooling outlet OUT may be provided at the tubular member 121, and the respective pipes may be sequentially connected to form the cooling passage P, and the cooling medium may be sequentially flowed through the inside of the respective pipes.
The support 122 may further include a third support 1223 connecting the first and second support 1221 and 1222, the third support 1223 contacting the tubular member 121 on the opposite side to the side where the active layer 14 is connected, the third support 1223 may also have a fourth cooling passage constituting the cooling passage P, in which case the cooling medium may pass through only the support 122 without passing through the inside of each tube of the tubular member 121, which is not in communication with the cooling passage in the support 122, and the cooling passage in the support 122 may have various arrangements, such as a spiral shape, to pass through as many areas as possible of the contact with the tube; the cooling medium may also pass through both the tube interior and the third support portion of the support or through both the tube interior and the first, second and third support portions of the support.
IN this embodiment, first and second cooling pipes D1 and D2 are disposed between the acceleration tube 111 and the reflector 21 and the retarder 22, one ends of the first and second cooling pipes D1 and D2 are respectively connected to the cooling inlet IN and the cooling outlet OUT of the target T, and the other ends are connected to an external cooling source. It will be appreciated that the first and second cooling tubes may be arranged in other ways within the beam shaper body, and may be omitted when the target is placed outside the beam shaper body.
With continued reference to fig. 5-7, 1 or more protrusions 123 having cooling surfaces S may be provided in the cooling passage P to increase the heat dissipation surface and/or form a vortex, to increase the heat dissipation effect, the cooling surfaces S being surfaces with which the cooling medium can contact with the protrusions 123 when flowing in the cooling passage P, the protrusions 123 protruding from the inner wall W of the cooling passage P in a direction perpendicular or oblique to the cooling medium flowing direction D, it being understood that the protrusions 123 may also protrude from the inner wall W of the cooling passage P in other forms. In a direction perpendicular to the direction of flow D of the cooling medium, the maximum distance L1 that the projection 123 extends from the inner wall W of the cooling channel P is smaller than half the distance L2 that the projection 123 extends to the opposite inner wall W in this direction of extension, and the projection 123 does not influence the free flow of the cooling medium in this cooling channel P, i.e. it does not function to divide one cooling channel into several substantially independent cooling channels (the cooling mediums do not influence each other).
In the first embodiment of the cooling channel shown in fig. 5a and 5b, the protruding portion 123 protrudes from the inner wall W of the cooling channel P in a direction perpendicular to the cooling medium flowing direction D, the inner wall W of the cooling channel P is a cylindrical surface, the protruding portion 123 is a bar extending in the cooling medium flowing direction D in a straight line shape, it is understood that the inner wall W of the cooling channel P may have other shapes, and the protruding portion 123 may also extend in a spiral shape or other shapes from the inner wall W of the cooling channel P in the cooling medium flowing direction. The number of projections is 10 and the projections are evenly distributed along the circumference of the inner wall W, it will be appreciated that the projections may be other numbers or may be merely provided on the inner wall W of the cooling channel in contact with the active layer or the base layer, and the shape and/or the projection length of at least 2 adjacent projections may be different. The cross-sectional shape of the protruding portion 123 in the direction perpendicular to the cooling medium circulation direction D may be rectangular, trapezoidal, triangular, or the like; the cross-sectional shape or size may also be different, such as pulsed, zigzag or wavy in the direction of flow of the cooling medium. The cooling surface S of the protrusion 123 is provided with a sub-protrusion 1231, in this embodiment, the sub-protrusion 1231 has a saw-tooth shape in a cross section perpendicular to the cooling medium flowing direction D and extends along the cooling medium flowing direction D, and it is understood that the sub-protrusion may have various configurations as long as the heat dissipation surface can be increased; in the present embodiment, the sub-protrusion 1231 is schematically provided on only one of the cooling surfaces of the protrusion 123, and it is understood that the sub-protrusion 1231 may be provided on any other cooling surface of the protrusion 123.
Fig. 6a and 6b show a second embodiment of a cooling channel, which only differs from the first embodiment in that the protrusions 123 are rings distributed at intervals in the direction of the flow of the cooling medium, it being understood that at least a part of the rings may also be present. The number of rings and the length of the cooling channels in the figure are only schematic and can be adjusted according to practical conditions. In the present embodiment, the end surface of the ring is a plane perpendicular to the cooling medium flowing direction D, and it is understood that the end surface may be a plane inclined to the cooling medium flowing direction D, a tapered surface, a curved surface, or the like.
Referring to fig. 7, in the third embodiment of the cooling channel, at least one second wall 124 is disposed in the cooling channel P to divide the cooling channel P into at least 2 mutually independent sub-channels P' and P ", and the cooling medium flowing directions in at least 2 adjacent sub-channels are different, so as to increase the heat dissipation efficiency. In this embodiment, the second wall 124 is cylindrical and passes through each protrusion 123 on the basis of the first embodiment, the sub-channel P ' is formed inside the cylindrical second wall 124, and 1 sub-channel p″ is formed between each 2 adjacent protrusions 123 and the second wall 124, so that 10 sub-channels p″ are formed around the sub-channel P ', the cooling medium flowing directions in the sub-channel P ' and at least one sub-channel p″ are different, and the cooling medium flowing directions in at least 2 adjacent sub-channels p″ may also be different. It will be appreciated that the second wall may be arranged in other ways depending on the arrangement of the protrusions. The projections in the cooling channels and the sub-projections thereon further increase the difficulty of manufacture, and therefore the projections and/or the second wall may be formed separately and then inserted into the tube for positioning or be integrally obtained with the tube by additive manufacturing.
It will be appreciated that the heat dissipation layer 12 may also be used as the base layer 13, in which case the heat dissipation layer 12 is at least partially made of a material that can conduct heat and suppress foaming, such as a tubular member 121 made of Ta or Ta-W alloy and a support member 122 made of Cu, and the active layer 14 is connected to the Ta or Ta-W alloy tube by a process such as evaporation or sputtering, and the Ta or Ta-W alloy tube serves as both the base layer 12 and the heat dissipation layer 13. In this embodiment, the target T is in a rectangular plate shape as a whole; it will be appreciated that the target T may also be disc-shaped, the first support and the second support forming the whole circumference or a part of the circumference, in which case the lengths of the tubes may be different; the target T can also be in other solid shapes; the target T may also be movable relative to the accelerator or beam shaping body to facilitate changing targets or to allow the particle beam to act uniformly with the target. The active layer 14 may be a liquid (liquid metal).
It will be appreciated that the target of the present invention may also be applied to neutron production devices in other medical and non-medical fields, as long as the production of neutrons is based on nuclear reactions of the particle beam with the target, the materials of the target also being distinguished based on different nuclear reactions; but also to other particle beam generating apparatus.
The term "tubular member" as used herein refers to a whole of a plurality of individual tubes arranged and connected by a connecting member or a connecting process, and a hollow-provided object formed by forming or combining one or more plate-like members to form a hollow portion is not to be construed as a tubular member of the present invention.
While the foregoing describes illustrative embodiments of the present invention to facilitate an understanding of the present invention by those skilled in the art, it should be understood that the present invention is not limited to the scope of the embodiments, but rather that various changes can be made within the spirit and scope of the present invention as defined and defined by the appended claims as would be apparent to those skilled in the art.
Claims (10)
1. A neutron capture therapy system, comprising a neutron generating device and a beam shaping body, wherein the neutron generating device comprises an accelerator and a target, charged particle rays generated by acceleration of the accelerator act with the target to generate neutron rays, the beam shaping body comprises a reflector, a retarder, a thermal neutron absorber, a radiation shielding body and a beam outlet, the retarder decelerates neutrons generated by the target to an epithermal neutron energy region, the reflector surrounds the retarder and guides deviated neutrons back to the retarder to improve the epithermal neutron beam intensity, the thermal neutron absorber is used for absorbing thermal neutrons to avoid excessive doses caused by shallow normal tissues during therapy, the radiation shielding body surrounds the beam outlet, is arranged at the rear of the reflector and is used for shielding leaked neutrons and photons to reduce normal tissue doses of non-irradiated regions, the beam shaping body comprises an action layer, a base layer and a heat dissipation layer, the action layer and the charged particle rays act to generate neutron rays, the base layer supports the action layer, the thermal neutron absorber is used for absorbing thermal neutrons to avoid excessive doses caused by shallow normal tissues, the radiation shielding layer surrounds the beam outlet, the radiation shielding layer is arranged at the rear of the reflector, and the radiation shielding layer is perpendicular to the base layer, and the base layer is formed by a tubular profile and the tubular profile.
2. The neutron capture therapy system of claim 1, further comprising a therapy table and a collimator, the neutron lines produced by the neutron producing device being irradiated by the beam shaping body toward a patient on the therapy table, a radiation shielding device being disposed between the patient and the beam outlet to shield radiation from the beam exiting the beam outlet toward normal tissue of the patient, the collimator being disposed rearward of the beam outlet to focus the neutron lines, first and second cooling tubes being disposed within the beam shaping body, the target having a cooling inlet, a cooling outlet, and a cooling channel disposed between the cooling inlet and the cooling outlet, one ends of the first and second cooling tubes being connected to the cooling inlet and the cooling outlet of the target, respectively, the other ends being connected to an external cooling source, the respective tube interiors of the tubular members constituting at least a portion of the cooling channel.
3. The neutron capture therapy system of claim 2, wherein the target is located within the beam shaping body, the accelerator has an accelerating tube for accelerating the charged particle beam, the accelerating tube extends into the beam shaping body in the direction of the charged particle beam and sequentially passes through the reflector and the buffer body, the target is located within the buffer body and at an end of the accelerating tube, and the first and second cooling tubes are located between the accelerating tube and the reflector and buffer body.
4. The target for the particle beam generating device is characterized by comprising an action layer, a base layer and a heat dissipation layer, wherein the action layer is used for generating the particle beam, the base layer supports the action layer, the heat dissipation layer comprises a tubular member formed by a plurality of tubes side by side, the action layer and the base layer form a whole in a shape of a section perpendicular to a central line of the tubes, and the outline of the outer surface of one side, connected with the base layer and the action layer, of the tubular member is consistent and is arc-shaped.
5. The target for a particle beam generator according to claim 4, wherein the particle beam generator is a neutron beam generator, the active layer is made of Li or an alloy thereof, and the active layer is formed with an incident proton beam 7 Li(p,n) 7 Be nuclear reactions to produce neutrons; or the material of the action layer is Be or alloy thereof, and the action layer and the incident proton beam generate 9 Be(p,n) 9 The B nuclei react to produce neutrons.
6. The target for a particle beam generating apparatus according to claim 4, further comprising an oxidation-resistant layer, wherein a material of the oxidation-resistant layer comprises at least one of Al, ti, be, and alloys thereof, or stainless steel, an adhesion layer is provided between the active layer and the base layer, a material of the adhesion layer comprises at least one of Cu, al, mg, or Zn, the heat dissipation layer is made of a heat conductive material or a heat conductive and foaming-inhibiting material, the base layer is made of a foaming-inhibiting material or a heat conductive and foaming-inhibiting material comprises at least one of Fe, ta, or V, a heat conductive material comprises at least one of Cu, fe, al, and the heat dissipation layer and the base layer are connected by a HIP process, and the active layer and the base layer are connected by a casting, evaporation, or sputtering process.
7. The target for a particle beam generating apparatus according to claim 4, wherein the tubular member simultaneously serves as the base layer, the material of the tubular member is Ta, and the active layer is connected to the tubular member by an evaporation or sputtering process.
8. A target for a particle beam generating apparatus as defined in any one of claims 4 to 7, wherein the active layer on each tube of the tubular member covers at least 1/4 of the outer circumference of the tube, the active layer forming an angle of at least 45 degrees with the center line of the tube in the circumferential direction, the tubular member forming a connection between adjacent tubes, the connection being composed of a base layer, an active layer and an oxidation resistant layer.
9. Target for a particle beam generating apparatus according to any of claims 4-7, wherein the heat dissipation layer further comprises a support, the material of the support being Cu, the tubular member being welded or detachably connected to the support, the support and/or tubular member having cooling channels.
10. A target for a particle beam generating apparatus according to claim 9, wherein the support member includes a first support portion and a second support portion provided at both ends of the tubular member, the first support portion having a cooling inlet and a first cooling passage, the second support portion having a cooling outlet and a second cooling passage, a cooling medium entering from the cooling inlet into each tube interior of the tubular member through the first cooling passage and then exiting from the cooling outlet through the second cooling passage, the cooling medium being water, the support member further including a third support portion connecting the first and second support portions, the third support portion being in contact with the other side of the tubular member opposite to the side on which the tubular member connects the active layer, the third support portion having a cooling passage, the cooling medium passing through only the support member or through the third support portion of the support member or through both the tube interior and the first, second and third support portions of the support member.
Priority Applications (12)
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| CN201710389070.4A CN108926784B (en) | 2017-05-26 | 2017-05-26 | Neutron capture treatment system and target for particle beam generating device |
| EP17885357.8A EP3530316B1 (en) | 2016-12-23 | 2017-07-13 | Neutron capturing therapy system and target material for use in particle beam generating device |
| RU2019121849A RU2727576C1 (en) | 2016-12-23 | 2017-07-13 | Neutron capture therapy system and target for beam particle generation device |
| PCT/CN2017/092742 WO2018113274A1 (en) | 2016-12-23 | 2017-07-13 | Neutron capturing therapy system and target material for use in particle beam generating device |
| EP20197643.8A EP3777976A1 (en) | 2016-12-23 | 2017-07-13 | Neutron capture therapy system and target for particle beam generating device |
| JP2019533000A JP2020513885A (en) | 2016-12-23 | 2017-07-13 | Targets for neutron capture therapy systems and particle beam generators |
| TW106128753A TWI632933B (en) | 2016-12-23 | 2017-08-24 | Neutron capture therapy system and target for particle beam generating device |
| US16/412,762 US20190262632A1 (en) | 2016-12-23 | 2019-05-15 | Neutron capture therapy system and target for particle beam generating device |
| US16/513,956 US11224766B2 (en) | 2016-12-23 | 2019-07-17 | Neutron capture therapy system and target for particle beam generating device |
| US17/539,358 US20220088416A1 (en) | 2016-12-23 | 2021-12-01 | Neutron capture therapy system and target for particle beam generating device |
| JP2022038857A JP7332736B2 (en) | 2016-12-23 | 2022-03-14 | Targets for neutron capture therapy systems and particle beam generators |
| JP2023130566A JP2023162248A (en) | 2016-12-23 | 2023-08-10 | Neutron capture care system and target for particle beam generator |
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| CN108934120B (en) * | 2017-05-26 | 2024-04-12 | 南京中硼联康医疗科技有限公司 | Target for neutron ray generating device and neutron capturing treatment system |
| WO2020211581A1 (en) * | 2019-04-17 | 2020-10-22 | 中硼(厦门)医疗器械有限公司 | Neutron capture therapy system |
| CN111821580A (en) * | 2019-04-17 | 2020-10-27 | 中硼(厦门)医疗器械有限公司 | Neutron capture therapy system and beam shaper for neutron capture therapy system |
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