CN109381802A - Neutron capture treatment system and target for particle beam generating apparatus - Google Patents
Neutron capture treatment system and target for particle beam generating apparatus Download PDFInfo
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Abstract
The present invention provides a kind of neutron capture treatment system and the target for particle beam generating apparatus, can promote the heat dissipation performance of target, reduces blistering, increases target life.Neutron capture treatment system of the invention, including neutron generation device and beam-shaping body, neutron generation device includes accelerator and target, accelerator accelerates sub-line in the charged particle line generated and target effect generation, target includes active layer, pedestal layer and heat dissipating layer, sub-line in active layer and the effect generation of charged particle line, pedestal layer supporting role layer, heat dissipating layer includes the cooling duct of meander-like.
Description
Technical Field
The invention relates to a radiation irradiation system, in particular to a neutron capture treatment system; another aspect of the present invention relates to a target for a radiation irradiation system, and more particularly, to a target for a particle beam generating apparatus.
Background
With the development of atomic science, radiation therapy such as cobalt sixty, linacs, electron beams, etc. has become one of the main means of cancer treatment. However, the traditional photon or electron therapy is limited by the physical conditions of the radiation, and can kill tumor cells and damage a large amount of normal tissues in the beam path; in addition, due to the difference in the sensitivity of tumor cells to radiation, conventional radiotherapy is often ineffective in treating malignant tumors with relatively high radiation resistance, such as multiple glioblastoma multiforme (glioblastoma multiforme) and melanoma (melanoma).
In order to reduce the radiation damage of normal tissues around tumor, the target therapy concept in chemotherapy (chemotherapy) is applied to radiotherapy; for tumor cells with high radiation resistance, radiation sources with high Relative Biological Effect (RBE) are also actively developed, such as proton therapy, heavy particle therapy, neutron capture therapy, etc. Wherein, 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 the specific accumulation of boron-containing drugs in tumor cells and the precise neutron beam regulation.
In accelerator boron neutron capture therapy, a proton beam is accelerated by an accelerator in the accelerator boron neutron capture therapy, the proton beam is accelerated to energy enough to overcome coulomb repulsion of target atomic nuclei and generates a nuclear reaction with a target to generate neutrons, so that the target is irradiated by the accelerated proton beam with a very high energy level in the process of generating the neutrons, the temperature of the target is greatly increased, and meanwhile, a metal part of the target is easy to blister, so that the service life of the target is influenced.
Therefore, a new technical solution is needed to solve the above problems.
Disclosure of Invention
In order to solve the above problems, the present invention provides a neutron capture treatment system, including a neutron generating device and a beam shaper, wherein the neutron generating device includes an accelerator and a target, the charged particle beam generated by acceleration of the accelerator acts on the target to generate neutron rays, the beam shaper includes a reflector, a retarder, a thermal neutron absorber, a radiation shield, and a beam outlet, the retarder decelerates neutrons generated from the target to a super-thermal neutron energy region, the reflector surrounds the retarder and guides off-neutrons back to the retarder to increase the intensity of the super-thermal neutron beam, the thermal neutron absorber absorbs thermal neutrons to avoid excessive dose with normal tissue of a shallow layer during treatment, the radiation shield is disposed around the beam outlet at the rear of the reflector to shield the leaked neutrons and photons to reduce the normal tissue dose of a non-irradiation region, the target comprises an action layer, a base layer and a heat dissipation layer, wherein the action layer and the charged particle beam act to generate a neutron line, the base layer supports the action layer, and the heat dissipation layer comprises a zigzag cooling channel. The zigzag channel prolongs the circulation path, can increase the contact area of the heat transfer wall surface and the cooling medium, thereby increasing the heat dissipation surface, simultaneously forming secondary flow, increasing the mixing effect, improving the heat transfer capacity and the heat dissipation effect, and being beneficial to prolonging the service life of the target material.
Preferably, the neutron capture treatment system further comprises a treatment table and a collimator, the neutron line generated by the neutron generating device is 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 to shield the radiation of the beam coming out of the beam outlet to the normal tissue of the patient, the collimator is arranged at the rear part of the beam outlet to converge the neutron line, a first cooling pipe and a second cooling pipe are arranged in the beam shaping body, the target is provided with a cooling inlet and a cooling outlet, the cooling channel is arranged between the cooling inlet and the cooling outlet, one end of the first cooling pipe and one end of the second cooling pipe are respectively connected with the cooling inlet and the cooling outlet of the target, the other end of the first cooling pipe and the second cooling pipe are connected to an external cooling source, the bending geometry of the zigzag cooling channel is a continuously bent smooth curve or a curve segment or a straight segment which is connected end to end in sequence, the continuously curved smooth curve is a sine wave function.
Furthermore, the target is positioned in the beam shaping body, the accelerator is provided with an accelerating tube for accelerating charged particle lines, the accelerating tube extends into the beam shaping body along the direction of the charged particle lines and sequentially passes through the reflector and the retarder, the target is arranged in the retarder and positioned at the end part of the accelerating tube, and the first cooling tube and the second cooling tube are arranged between the accelerating tube and the reflector and the retarder.
In another aspect, the present invention provides a target for a particle beam generating apparatus, where the target includes an active layer, a base layer, and a heat dissipation layer, the active layer is used for generating the particle beam, the base layer supports the active layer, and the heat dissipation layer includes a zigzag cooling channel. The zigzag channel prolongs the circulation path, can increase the contact area of the heat transfer wall surface and the cooling medium, thereby increasing the heat dissipation surface, simultaneously forming secondary flow, increasing the mixing effect, improving the heat transfer capacity and the heat dissipation effect, and being beneficial to prolonging the service life of the target material.
Preferably, the curved geometry of the zigzag cooling channel is a continuously curved smooth curve or a series of end-to-end curved or straight segments, the continuously curved smooth curve being a sine wave function. The cooling channel uses a continuously curved smooth curve, such as a sine wave function, to further reduce the flow resistance caused by the flow path.
As another preferable mode, the zigzag cooling passage includes a plurality of sub-parallel zigzag passages formed by arranging a plurality of zigzag walls in parallel or a plurality of sub-spiral zigzag passages formed by spreading one or more zigzag walls in a spiral line, and the cooling medium flowing directions in at least 2 adjacent sub-parallel zigzag passages or sub-spiral zigzag passages are different. The cooling medium in the adjacent sub parallel tortuous channels or the sub spiral tortuous channels has different circulation directions, so that the heat dissipation efficiency is further increased.
As another preference, the heat dissipation layer comprises a first plate having a first side facing the active layer and a second side opposite the first side, and the meander-like cooling channels are formed on the second side or on the second plate on the side opposite the first plate.
Further, the heat dissipation layer is provided with a cooling inlet and a cooling outlet, the zigzag cooling channel is communicated with the cooling inlet and the cooling outlet, and the cooling inlet and the cooling outlet are both arranged on one of the first plate and the second plate or are respectively arranged on the first plate and the second plate. The material of the first plate and/or the second plate is Ta or Ta-W alloy or Cu, and the cross section of the zigzag cooling channel is rectangular, circular, polygonal or elliptical.
Furthermore, a circumferential wall is arranged at the periphery of the cooling inlet and/or the cooling outlet, the second plate is in close contact with the surface of the circumferential wall facing the second plate, and a cavity is formed between the first plate and the second plate, so that the cooling medium entering from the cooling inlet can only exit through the cooling outlet.
Drawings
FIG. 1 is a schematic view of a neutron capture therapy system in an embodiment of the invention;
FIG. 2 is a schematic view of a target according to an embodiment of the present invention;
FIG. 3 is a schematic view of a first embodiment of a heat sink layer of the target of FIG. 2;
FIG. 4 is a schematic view of the first plate of the heat spreading layer of FIG. 3;
FIG. 5 is a schematic view of a second embodiment of a heat sink layer of the target of FIG. 2;
FIG. 6 is a schematic view of the first plate of the heat spreading layer of FIG. 5.
Detailed Description
Embodiments of the present invention will be described in further detail below with reference to the accompanying drawings so that those skilled in the art can implement the embodiments with reference to the description.
Referring to FIG. 1, the neutron capture treatment system in this embodiment is preferably a boron neutron capture treatment system 100, including neutron productionA generating device 10, a beam shaper 20, a collimator 30 and a treatment table 40. The neutron generating apparatus 10 includes an accelerator 11 and a target T, and the accelerator 11 accelerates charged particles (such as protons, deuterons, and the like) to generate a charged particle beam C such as a proton beam, and the charged particle beam C irradiates the target T and reacts with the target T to generate a neutron beam (neutron beam) N, and the target T is preferably a metal target. The appropriate nuclear reactions are selected based on the desired neutron yield and energy, the available energy and current for accelerating charged particles, the physical properties of the metal target, and the like, and the nuclear reactions in question include7Li(p,n)7Be and9Be(p,n)9b, both reactions are endothermic. The energy thresholds of the two nuclear reactions are 1.881MeV and 2.055MeV respectively, because the ideal neutron source for boron neutron capture treatment is epithermal neutrons with keV energy level, theoretically if a metallic lithium target is bombarded by protons with energy only slightly higher than the threshold, neutrons with relatively low energy can Be generated, and can Be used clinically without too much slowing treatment, however, the proton interaction cross section of the two targets of lithium metal (Li) and beryllium metal (Be) and the threshold energy is not high, and in order to generate enough neutron flux, protons with higher energy are usually selected to initiate the nuclear reaction. An ideal target should have the characteristics of high neutron yield, neutron energy distribution generated close to the hyperthermic neutron energy region (described in detail below), not too much intense penetrating radiation generation, safety, cheapness, easy operation, and high temperature resistance, but practically no nuclear reaction meeting all the requirements can be found. As is well known to those skilled in the art, the target T may Be made of a metal material other than Li and Be, for example, Ta or W, an alloy thereof, or the like. The accelerator 11 may be a linear accelerator, a cyclotron, a synchrotron, 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 shaper 20 and the collimator 30 in this order. The beam shaper 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 high targeting performance in the treatment process. The beam shaper 20 further comprises a reflector 21, a retarder 22, a thermal neutron absorber 23, a radiation shield24 and a beam outlet 25, wherein neutrons generated by the neutron generating device 10 have a wide energy spectrum, and besides epithermal neutrons meeting therapeutic requirements, the content of neutrons and photons of other types needs to be reduced as much as possible to avoid damage to operators or patients, so that neutrons from the neutron generating device 10 need to pass through the retarder 22 to adjust fast neutron energy therein to an epithermal neutron energy region, the retarder 22 is made of a material having a large fast neutron acting section and a small epithermal neutron acting section, in this embodiment, the retarder 22 is made of a material having a large fast neutron acting section and a small epithermal neutron acting section, and the retarder 22 is made of a material having a D-shaped structure2O、AlF3、Fluental、CaF2、Li2CO3、MgF2And Al2O3At least one of (a); the reflector 21 surrounds the retarder 22, reflects neutrons diffused to the periphery through the retarder 22 back to the neutron beam N to improve the utilization rate of the neutrons, and is made of a material with strong neutron reflection capability, in the embodiment, the reflector 21 is made of at least one of Pb or Ni; the thermal neutron absorber 23 is arranged at the rear part of the retarder 22 and is made of a material with a large cross section with the thermal neutron, 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 the thermal neutrons in the neutron beam N and avoid causing excessive dose with 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 a portion outside the beam outlet 25, the material of the radiation shield 24 includes at least one of a photon shielding material and a neutron shielding material, and in the present embodiment, the material of the radiation shield 24 includes lead (Pb) and Polyethylene (PE) which are photon shielding materials. It will be appreciated that the beam shaper 20 may have other configurations as long as the desired hyperthermal neutron beam for the treatment is obtained. The collimator 30 is disposed behind the beam outlet 25, and the hyperthermo neutron beam emitted from the collimator 30 irradiates the patient 200, and is slowed down to be thermal neutrons to reach the tumor cells M after passing through the shallow normal tissue, it is understood that the collimator 30 may be eliminated or replaced by other structures, and the neutron beam is emitted from the beam outlet 25 to directly irradiate the patient 200. In this embodiment, a radiation shield 50 is also provided between the patient 200 and the beam outlet 25 to shield the secondary beam from the radiation beamThe beam exiting the port 25 radiates normal tissue of the patient, and it will be appreciated that the radiation shield 50 may or may not be provided.
After the patient 200 takes or injects the boron-containing (B-10) drug, the boron-containing drug selectively accumulates in the tumor cells M, and then the characteristic of high capture cross section of the boron-containing (B-10) drug to thermal neutrons is utilized10B(n,α)7Li neutron capture and nuclear fission reaction generation4He and7the average Energy of the two charged particles is about 2.33MeV, the two charged particles have high Linear Energy Transfer (LET) and short-range characteristics, and the Linear Energy Transfer and the range of the α short particles are 150 keV/mum and 8μm respectively7The Li-heavily-charged particles are 175 keV/mum and 5μm, and the total range of the two particles is about equal to the size of a cell, so that the radiation damage to organisms can be limited at the cell level, and the aim of locally killing tumor cells can be achieved on the premise of not causing too much damage to normal tissues.
The structure of the target T will be described in detail with reference to fig. 2.
The target T is disposed between the accelerator 11 and the beam shaper 20, the accelerator 11 has an accelerating tube 111 for accelerating the charged particle beam C, in this embodiment, the accelerating tube 111 extends into the beam shaper 20 along the charged particle beam C and sequentially passes through the reflector 21 and the retarder 22, and the target T is disposed in the retarder 22 and at an end of the accelerating tube 111 to obtain better neutron beam quality.
The target T comprises a heat dissipation layer 12, a base layer 13 and an action layer 14, the action layer 14 and the charged particle beam C act to generate a neutron line, and the base layer 13 supports the action layer 14. The heat dissipation layer 12 is made of a heat conductive material (e.g., a material with good heat conductivity such as Cu, Fe, Al, etc.) or a material that can conduct heat and inhibit foaming; the base layer 13 is made of a material that suppresses foaming; the material that inhibits foaming or a material that is both thermally conductive and inhibits foaming includes at least one of Fe, Ta, or V. In this embodiment, the active layer 14 is made of Li or an alloy thereof, the charged particle beam C is a proton beam, and the target T further includes a material for positioning on one side of the active layer 14In the antioxidation layer 15 for preventing oxidation of the active layer, the base layer 13 can simultaneously suppress foaming caused by incident proton rays, and the charged particle rays C pass through the antioxidation layer 15, the active layer 14, and the base layer 13 in this order along the incident direction. The material of the oxidation resistant layer 15 simultaneously considers that it is not easily corroded by the active layer and can reduce the loss of the incident proton beam and the heat generation caused by the proton beam, such as at least one of Al, Ti and alloy thereof, or stainless steel. In this embodiment, the oxidation-resistant layer 15 is a material capable of nuclear reaction with protons, and can further increase the neutron yield while performing the above-mentioned functions, at this time, the oxidation-resistant layer is a part of the active layer, for example, Be or its alloy is used, the energy of the incident proton beam is higher than the energy threshold for nuclear reaction with Li and Be, two different nuclear reactions are generated respectively,7Li(p,n)7be and9Be(p,n)9b; in addition, Be has high melting point and good heat conduction property, the melting point is 1287 ℃, the heat conductivity is 201W/(m K), the high temperature resistance and the heat dissipation performance of Li (the melting point is 181 ℃, the heat conductivity is 71W/(m K)) have great advantages, the service life of the target material is further prolonged, the reaction threshold of (p, n) nuclear reaction with proton is about 2.055MeV, most accelerator neutron sources adopting proton beams have energy higher than the reaction threshold, and beryllium targets are also the best choice besides lithium targets. The neutron yield is improved due to the presence of Be compared to using an oxidation resistant layer of other materials, such as Al. In the embodiment, the energy of the proton line is 2.5MeV-5MeV, a higher action section can be generated with the lithium target, excessive fast neutrons cannot be generated, and better beam quality is obtained; the thickness of the action layer 14 is 80-240 μm, and the action layer can fully react with protons and cannot be too thick to cause energy deposition and influence the heat dissipation performance of the target material; the effect is achieved while the lower manufacturing cost is ensured, and the thickness of the oxidation resistant layer 15 is 5-25 μm. In a comparative test, Monte Carlo software is adopted to respectively simulate proton beams of 2.5MeV, 3MeV, 3.5MeV, 4MeV, 4.5MeV and 5MeV to Be sequentially injected into an antioxidation layer 15, an action layer 14(Li) and a base layer 13(Ta, which will Be described in detail later) from a direction vertical to the action surface of a target T, the material of the antioxidation layer 15 is compared with Be by Al, and the antioxidation layer 15 is thickThe degrees were 5 μm, 10 μm, 15 μm, 20 μm, and 25 μm, respectively, the thicknesses of the active layer 14 were 80 μm, 120 μm, 160 μm, 200 μm, and 240 μm, respectively, the thickness of the base layer 12 had almost no effect on the neutron yield, and the results of the obtained neutron yields (i.e., the number of neutrons generated per proton) were as shown in tables 1 and 2. The results of calculating the neutron yield improvement ratio of the lithium target oxidation resistant layer to Al using Be are shown in table 3, and it is known that when Be is used as the oxidation resistant layer material, the neutron yield is significantly improved relative to Al, and the neutron yield can Be obtained to Be 7.31E-05n/proton-5.61E-04 n/proton.
TABLE 1 neutron yield (n/proton) using Al as lithium target oxidation resistant layer E incident proton line energy
TABLE 2 neutron yield (n/proton) using Be as the lithium target oxidation resistant layer E as the incident proton line energy
TABLE 3 neutron yield enhancement ratio relative to Al using Be as the lithium target oxidation resistant layer E incident proton line energy
When the base layer 13 is made of Ta, the base layer has a certain heat dissipation effect, can reduce bubbling, inhibits the protons and Li from generating inelastic scattering to release gamma, and prevents the redundant protons from passing through the target material; in this embodiment, the base layer 13 is made of Ta — W alloy, which can significantly improve the disadvantages of low strength and poor thermal conductivity of pure tantalum while maintaining the excellent performance of Ta, so that the heat generated by the nuclear reaction of the active layer 14 can be conducted away from the base layer in time. The weight percentage of W in the Ta-W alloy is 2.5% -20% so as to ensure the characteristic of inhibiting foaming of the base layer, and meanwhile, the base layer has higher strength and thermal conductivity, and the service life of the target material is further prolonged. Ta-W alloys (e.g., Ta-2.5 wt% W, Ta-5.0 wt% W, Ta-7.5 wt% W, Ta-10 wt% W, Ta-12 wt% W, Ta-20 wt% W, etc.) are formed into a plate-like base layer 13 by powder metallurgy, forging, pressing, etc., the base layer having a thickness of at least 50 μm at a proton linear energy of 1.881MeV-10MeV to sufficiently absorb excess protons.
The heat dissipation layer may have a variety of configurations, such as a heat pipe. In the first embodiment of the heat dissipation layer shown in fig. 3 and 4, the heat dissipation layer 12 is plate-shaped and includes a first plate 121 and a second plate 122, the first plate 121 has a first side 1211 facing the active layer 14 and a second side 1212 opposite to the first side 1211, the second side 1212 is formed with a cooling channel P for circulating a cooling medium, and the second plate 122 is in close contact with the second side 1212 of the first plate 121, it being understood that the cooling channel P may also be disposed on the second plate 122 on the side opposite to the first plate 121. The cooling passage P is zigzag-shaped, and the zigzag-shaped cooling passage P includes a plurality of sub-parallel zigzag passages P1, i.e., a plurality of zigzag walls W arranged in parallel, with zigzag grooves S (i.e., sub-parallel zigzag passages P1) formed between adjacent walls W. The bending geometry of the sub-parallel tortuous path P1 is a sine wave function:
wherein,the phase angle, x the coordinate of the cooling medium flow direction (described in detail below), k the amplitude, and T the period.
It can be understood that the cooling channel P may also be in other zigzag shapes, such as a continuously curved smooth curve or a curve segment or a straight segment which is sequentially connected end to end, the zigzag channel prolongs the flow path, the contact area between the heat transfer wall surface and the cooling medium can be increased, so as to increase the heat dissipation surface, and at the same time, a secondary flow is formed, thereby increasing the mixing effect, improving the heat transfer capability and the heat dissipation effect, and contributing to prolonging the service life of the target material. The cooling passageway P can further reduce the flow resistance caused by the flow path by using a continuously curved smooth curve, such as a sine wave function. Other arrangements of the serpentine cooling passages P are possible.
The heat dissipation layer 12 also has a cooling inlet IN and a cooling outlet OUT, and a cooling passage P communicates the cooling inlet IN and the cooling outlet OUT, and a cooling medium enters from the cooling inlet IN, passes through the cooling passage P, and then exits from the cooling outlet OUT. The target T is heated by the irradiation temperature rise of the accelerated proton beam with high energy level, the heat is led out by the base layer and the heat dissipation layer, and is taken out by the cooling medium circulating in the cooling channel, so that the target T is cooled. The number of the cooling inlets IN and the cooling outlets OUT is 3, the cooling inlets IN and the cooling outlets OUT are symmetrically arranged at two ends of the cooling channel P on the first plate 121, and extend through IN the direction from the first side 1211 to the second side 1212, an inlet groove S1 and an outlet groove S2 are further formed on the second side 1212, the inlet groove S1 and the outlet groove S2 are respectively communicated with the cooling inlets IN and the cooling outlets OUT and the sub parallel zigzag channels P1, so that the cooling medium entering from the cooling inlets IN enters the sub parallel zigzag channels P1 from the inlet grooves S1 and then exits from the cooling outlets OUT through the outlet grooves S2. It will be appreciated that the cooling inlets IN and the cooling outlets OUT can be provided IN other numbers or IN other forms, and can also be provided on the second plate simultaneously or on the first plate and on the second plate, respectively. The peripheries of the cooling inlet IN and the cooling outlet OUT are also provided with a circumferential wall W1, the second plate 122 is IN close contact with the surface of the circumferential wall W1 facing the second plate 122, a cavity is formed between the first plate 121 and the second plate 122, so that the cooling medium entering from the cooling inlet IN can only exit through the cooling outlet OUT, the contact surface of the second plate 122 and the first plate 121 is a plane, and the height of the zigzag-shaped wall W is the same as that of the circumferential wall W1; it will be appreciated that a stepped surface or other configuration is also possible, in which case the height of the zigzag wall W and the height of the circumferential wall W1 may be different, so long as the individual sub-parallel tortuous paths P1 are independent of one another. The cooling medium flow direction D (the flow direction of the entire cooling medium in the cooling passage) in the adjacent sub parallel meandering passages P1 may be different, and the heat radiation efficiency is further increased. The inlet tank S1 and the outlet tank S2 may be arranged in other ways, such as by passing the cooling medium through each of the sub-parallel serpentine paths P1 in sequence. In this embodiment, the first plate and the second plate are both made of Cu, which has good heat dissipation performance and low cost. The number and size of the grooves S forming the cooling passages P are determined according to the size of the actual target, the cross-sectional shape of the grooves may be various, such as rectangular, circular, polygonal, oval, etc., and different cross-sections may have different shapes.
The first plate 121 and the second plate 122 are fixed together by a bolt, a screw, or other fixing structure, such as welding, to the inside of the speed reducing body 22 or the end of the acceleration pipe 111, or the first plate 121 and the second plate 122 are connected and then one of them is fixed to the inside of the speed reducing body 22 or the end of the acceleration pipe 111. It can be understood that the heat dissipation layer can be fixed or installed by adopting other detachable connections, so that the target material can be conveniently replaced; the heat dissipation layer 12 may further have a support (not shown) by which the first plate 121 and/or the second plate 122 are fixed, and the cooling inlet IN and the cooling outlet OUT may be provided on the support. IN this embodiment, the first and second cooling tubes D1 and D2 are disposed between the accelerating tube 111 and the reflector 21 and the decelerating body 22, one ends of the first and second cooling tubes 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 otherwise disposed within the beam shaper and may be eliminated when the target material is disposed outside of the beam shaper.
As shown in fig. 5 and 6, a second embodiment of the heat dissipation layer, and only the differences from the first embodiment will be described below. In the second embodiment of the heat dissipation layer, the zigzag-shaped cooling passage P ' includes a plurality of sub-spiral zigzag passages P1 ', i.e., a plurality of zigzag-shaped walls W ' that are spirally spread around the same center, each wall W ' is formed in a plurality of layers in the radial direction, the layers formed by the respective walls W ' are alternately arranged in the radial direction, and a groove S ' is formed between adjacent layers (i.e., the sub-spiral zigzag passages P1 '). The trajectory function of the sub-spiral tortuous path P1' is:
wherein R isinIs a central radius, RoutIs the outer radius, theta is the polar angle, K is the amplitude, and T is the period.
The cooling inlets IN 'are arranged IN the center of the second plate 122' and penetrate the center of each of the sub-spiral zigzag channels P1 ', and the number of cooling outlets OUT' is 4, and are circumferentially arranged on the first plate 121 'on the periphery of the cooling channels P' and extend through IN the direction from the first side 1211 'to the second side 1212', it being understood that other arrangements are possible. The center of the cooling passage P ', i.e., the center of each sub-spiral meandering passage P1', is formed as an inlet groove S1 'on the second side 1212' of the first plate 121 ', and an outlet groove S2' is further formed on the outlet groove S2 'to communicate the cooling outlet OUT' with each sub-spiral meandering passage P1 ', so that the cooling medium entering from the cooling inlet IN' enters each sub-spiral meandering passage P1 'from the center of the cooling passage P', passes through the outlet groove S2 ', and exits from the cooling outlet OUT'. The periphery of the cooling outlet OUT ' is provided with a circumferential wall W1 ', the second plate 122 ' is IN close contact with the surface of the circumferential wall W1 ' facing the second plate 122 ', a cavity is formed between the first plate 121 ' and the second plate 122 ', so that the cooling medium entering from the cooling inlet IN ' can only exit through the cooling outlet OUT ', the surface of the second plate 122 ' IN contact with the first plate 121 ' is a plane, and the height of the zigzag-shaped wall W ' is the same as that of the circumferential wall W1 '; it will be appreciated that a stepped surface or other configuration is also possible, in which case the height of the zigzag wall W ' and the height of the circumferential wall W1 ' may be different, so long as the individual sub-spiral zigzag channels P1 ' are independent of each other. The cooling medium flowing directions in the adjacent sub-spiral zigzag channels P1' can also be different, further increasing the heat dissipation efficiency. Protrusions 1213 'may also be provided at the center of the first plate 121' to rectify and increase the heat transfer area and reduce the central hot spot temperature. The height of the projection 1213 'may be higher than the height of the wall W' and the circumferential wall W1 'and extend into the cooling inlet IN' on the second plate; the shape of the protrusions 1213' may be solid cones, hollow cones, sheets, etc.
In this embodiment, the manufacturing process of the target T is as follows:
s1: pouring liquid lithium metal or its alloy on the base layer 13 to form the action layer 14, or adopting the treatment of vapor deposition or sputtering, etc., and arranging an extremely thin adhesion layer 16 between the base layer and the action layer, wherein the material of the adhesion layer 16 comprises at least one of Cu, Al, Mg or Zn, and the treatment of vapor deposition or sputtering, etc. can be also adopted to improve the adhesion between the base layer and the action layer;
s2: the base layer 13 and the heat sink layer 12 are subjected to HIP (Hot Isostatic Pressing) treatment or other processes for connection;
s3: the oxidation resistant layer 15 is simultaneously HIP treated or by other processes enclosing the base layer 13 to form a cavity and/or surrounding the active layer 14.
The steps S1, S2, and S3 are not in sequence, for example, the antioxidation layer 15 and the base layer 13 may be subjected to HIP treatment or the base layer 13 may be sealed by other processes to form a cavity, and then the liquid lithium metal or its alloy is poured into the cavity to form the active layer 14. The heat dissipation layer may also be made of at least partially the same material or be of a unitary construction as the base layer, for example, a first plate made of Ta or a Ta — W alloy may be used as both the heat dissipation layer 12 and the base layer 13, in which case the second plate may be made of the same material as the first plate or may still be made of Cu, and step S2 may be omitted, and the active layer 14 may be connected to the first plate by casting, evaporation, or sputtering.
In this embodiment, the target T is a circular plate as a whole; it is understood that the target T may also have a rectangular plate shape; the target T can also be in other solid shapes; the target T may also be movable relative to the accelerator or beam shaper to facilitate target exchange or to homogenize the particle beam with the target. The active layer 14 may be a liquid substance (liquid metal).
It is understood 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 neutron production is based on nuclear reaction of the particle beam and the target material, the material of the target material is also distinguished based on different nuclear reactions; but also to other particle beam generating devices.
Although illustrative embodiments of the invention have been described above to facilitate the understanding of the invention by those skilled in the art, it should be understood that the invention is not limited to the scope of the embodiments, and that various changes will become apparent to those skilled in the art within the spirit and scope of the invention as defined and defined in the appended claims.
Claims (10)
1. A neutron capture therapy system, comprising a neutron generating device and a beam shaper, wherein the neutron generating device comprises an accelerator and a target, charged particle rays generated by acceleration of the accelerator and the target act to generate neutron rays, the beam shaper comprises a reflector, a retarder, a thermal neutron absorber, a radiation shield and a beam outlet, the retarder decelerates neutrons generated from the target to a super-thermal neutron energy region, the reflector surrounds the retarder and guides deviated neutrons back to the retarder to improve the intensity of the super-thermal neutron beam, the thermal neutron absorber is used for absorbing thermal neutrons to avoid excessive dose with shallow normal tissues during therapy, the radiation shield is arranged around the beam outlet at the rear part of the reflector and used for shielding leaked neutrons and photons to reduce the dose of normal tissues in a non-irradiation region, the target comprises an action layer, a base layer and a heat dissipation layer, wherein the action layer and the charged particle beam act to generate a neutron line, the base layer supports the action layer, and the heat dissipation layer comprises a zigzag cooling channel.
2. The neutron capture therapy system of claim 1, further comprising 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 shaper, a radiation shielding device is disposed between the patient and a beam outlet to shield the radiation of the beams from the beam outlet to the normal tissues of the patient, the collimator is disposed behind the beam outlet to converge the neutron rays, a first cooling tube and a second cooling tube are disposed in the beam shaper, the target has a cooling inlet and a cooling outlet, the cooling channel is disposed between the cooling inlet and the cooling outlet, one end of the first cooling tube and one end of the second cooling tube are respectively connected to the cooling inlet and the cooling outlet of the target, the other end of the first cooling tube and the other end of the second cooling tube are connected to an external cooling source, and the curved geometry of the curved cooling channel is a continuous curved smooth curve or a curve that is connected end to end in sequence A segment or a straight line segment, the continuously curved smooth curve being a sine wave function.
3. The neutron capture therapy system of claim 2, wherein the target is positioned within the beam shaper, the accelerator has an accelerating tube for accelerating charged particle rays, the accelerating tube extends into the beam shaper along the charged particle rays and sequentially passes through the reflector and the retarder, the target is disposed within the retarder and at an end of the accelerating tube, and the first and second cooling tubes are disposed between the accelerating tube and the reflector and retarder.
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, and the heat dissipation layer comprises a zigzag cooling channel.
5. A target for a particle beam generating apparatus according to claim 4, wherein the curved geometry of the zigzag cooling channel is a continuously curved smooth curve or a series of end-to-end curved or straight segments, and the continuously curved smooth curve is a sine wave function.
6. A target for a particle beam generating apparatus according to claim 4, wherein the zigzag cooling channel comprises a plurality of sub-parallel zigzag channels formed by arranging a plurality of zigzag walls in parallel or a plurality of sub-spiral zigzag channels formed by spreading one or more zigzag walls in a spiral line, and the flow directions of the cooling medium in at least 2 adjacent sub-parallel zigzag channels or sub-spiral zigzag channels are different.
7. A target for a particle beam generating device according to claim 4, wherein the heat dissipation layer comprises a first plate having a first side facing the active layer and a second side opposite to the first side, and a second plate, and the zigzag-shaped cooling channel is formed on the second side or on a side of the second plate opposite to the first plate.
8. A target for a particle beam generating apparatus according to claim 7, wherein the heat dissipating layer has a cooling inlet and a cooling outlet, the zigzag cooling channel communicates with the cooling inlet and the cooling outlet, and the cooling inlet and the cooling outlet are provided on one of the first plate and the second plate or on the first plate and the second plate, respectively.
9. A target for a particle beam generating apparatus according to claim 7, wherein the material of the first plate and/or the second plate is Ta or a Ta-W alloy or Cu, and the cross-sectional shape of the zigzag cooling channel is rectangular, circular, polygonal, or elliptical.
10. A target for a particle beam generating apparatus as defined in claim 8, wherein the periphery of the cooling inlet and/or the cooling outlet is further provided with a circumferential wall, the second plate is in close contact with a surface of the circumferential wall facing the second plate, and a cavity is formed between the first plate and the second plate, so that the cooling medium entering from the cooling inlet can only exit through the cooling outlet.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710670326.9A CN109381802A (en) | 2017-08-08 | 2017-08-08 | Neutron capture treatment system and target for particle beam generating apparatus |
| PCT/CN2018/098985 WO2019029483A1 (en) | 2017-08-08 | 2018-08-06 | Neutron capture therapy system and target material for use with particle beam production device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710670326.9A CN109381802A (en) | 2017-08-08 | 2017-08-08 | Neutron capture treatment system and target for particle beam generating apparatus |
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| CN109381802A true CN109381802A (en) | 2019-02-26 |
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| CN201710670326.9A Pending CN109381802A (en) | 2017-08-08 | 2017-08-08 | Neutron capture treatment system and target for particle beam generating apparatus |
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| CN111093314A (en) * | 2019-12-02 | 2020-05-01 | 广东太微加速器有限公司 | A neutron generating target and a target chamber using the neutron generating target |
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| US11198023B2 (en) * | 2017-08-30 | 2021-12-14 | Neuboron Medtech Ltd. | Neutron capture therapy system |
| CN114225232A (en) * | 2021-09-26 | 2022-03-25 | 散裂中子源科学中心 | Beam shaping body with rotary target body |
| WO2023284772A1 (en) * | 2021-07-16 | 2023-01-19 | 中硼(厦门)医疗器械有限公司 | Target material for particle beam generation apparatus |
| US11678430B2 (en) | 2019-08-30 | 2023-06-13 | Tae Technologies, Inc. | Neutron generating target for neutron beam systems |
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| TWI813380B (en) * | 2021-07-16 | 2023-08-21 | 大陸商中硼（廈門）醫療器械有限公司 | Target material and base material for particle beam generating device |
| TWI818625B (en) * | 2021-07-16 | 2023-10-11 | 大陸商中硼（廈門）醫療器械有限公司 | Target material for particle beam generating device and processing equipment and processing method thereof |
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