CN118203773B - Assembling method of adjustable space division radiotherapy collimator - Google Patents
Assembling method of adjustable space division radiotherapy collimator Download PDFInfo
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- CN118203773B CN118203773B CN202410617967.8A CN202410617967A CN118203773B CN 118203773 B CN118203773 B CN 118203773B CN 202410617967 A CN202410617967 A CN 202410617967A CN 118203773 B CN118203773 B CN 118203773B
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- 238000001959 radiotherapy Methods 0.000 title claims abstract description 38
- 238000000034 method Methods 0.000 title claims abstract description 19
- 230000000149 penetrating effect Effects 0.000 claims abstract description 91
- 230000005855 radiation Effects 0.000 claims abstract description 47
- 230000000903 blocking effect Effects 0.000 claims abstract description 4
- 230000035515 penetration Effects 0.000 claims description 23
- 229920000747 poly(lactic acid) Polymers 0.000 claims description 11
- 239000004626 polylactic acid Substances 0.000 claims description 11
- 238000003825 pressing Methods 0.000 claims description 11
- 238000007906 compression Methods 0.000 claims description 10
- 230000006835 compression Effects 0.000 claims description 8
- 238000010146 3D printing Methods 0.000 claims description 5
- 230000000694 effects Effects 0.000 abstract description 4
- 238000010586 diagram Methods 0.000 description 5
- 239000000463 material Substances 0.000 description 4
- WFKWXMTUELFFGS-UHFFFAOYSA-N tungsten Chemical compound [W] WFKWXMTUELFFGS-UHFFFAOYSA-N 0.000 description 4
- 229910052721 tungsten Inorganic materials 0.000 description 4
- 239000010937 tungsten Substances 0.000 description 4
- 238000004519 manufacturing process Methods 0.000 description 3
- XECAHXYUAAWDEL-UHFFFAOYSA-N acrylonitrile butadiene styrene Chemical compound C=CC=C.C=CC#N.C=CC1=CC=CC=C1 XECAHXYUAAWDEL-UHFFFAOYSA-N 0.000 description 2
- 229920000122 acrylonitrile butadiene styrene Polymers 0.000 description 2
- 239000004676 acrylonitrile butadiene styrene Substances 0.000 description 2
- 238000010009 beating Methods 0.000 description 2
- 239000004417 polycarbonate Substances 0.000 description 2
- ZSLUVFAKFWKJRC-IGMARMGPSA-N 232Th Chemical compound [232Th] ZSLUVFAKFWKJRC-IGMARMGPSA-N 0.000 description 1
- 244000271437 Bambusa arundinacea Species 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- 229910052776 Thorium Inorganic materials 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 229910052797 bismuth Inorganic materials 0.000 description 1
- JCXGWMGPZLAOME-UHFFFAOYSA-N bismuth atom Chemical compound [Bi] JCXGWMGPZLAOME-UHFFFAOYSA-N 0.000 description 1
- 238000005520 cutting process Methods 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 230000001788 irregular Effects 0.000 description 1
- 239000010812 mixed waste Substances 0.000 description 1
- 231100000252 nontoxic Toxicity 0.000 description 1
- 230000003000 nontoxic effect Effects 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 239000002245 particle Substances 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- -1 polyethylene terephthalate Polymers 0.000 description 1
- 239000005020 polyethylene terephthalate Substances 0.000 description 1
- 229920000139 polyethylene terephthalate Polymers 0.000 description 1
- 229920005644 polyethylene terephthalate glycol copolymer Polymers 0.000 description 1
- 238000007639 printing Methods 0.000 description 1
- 229910052702 rhenium Inorganic materials 0.000 description 1
- WUAPFZMCVAUBPE-UHFFFAOYSA-N rhenium atom Chemical compound [Re] WUAPFZMCVAUBPE-UHFFFAOYSA-N 0.000 description 1
- 230000011218 segmentation Effects 0.000 description 1
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- 238000002560 therapeutic procedure Methods 0.000 description 1
- 231100000331 toxic Toxicity 0.000 description 1
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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
- A61N5/1042—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head
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Abstract
The invention discloses an assembly method of an adjustable space division radiotherapy collimator, and relates to the technical field of radiotherapy. In the step S2, penetrating pieces capable of penetrating rays are overlapped to form penetrating parts, the number of the penetrating pieces is calculated, the thickness of each penetrating part corresponds to the width of each radiation area, shielding pieces capable of blocking rays are overlapped to form shielding parts, the number of the shielding pieces is calculated, and the thickness of each shielding part corresponds to the interval of each radiation area; in S3, the penetrating parts and the shielding parts are sequentially overlapped to form a collimation module, and shielding parts are respectively arranged at two sides of the collimation module. According to the invention, the penetrating parts and the shielding parts with different thicknesses are assembled according to the radiation treatment range and the space between the radiation treatment ranges, and then the penetrating parts and the shielding parts are overlapped to form the collimation module, and the collimation module is pressed to form the collimator. The thicknesses of the penetrating part and the shielding part can be assembled and adjusted according to the needs, so that the device can be suitable for space division radiotherapy with different requirements, and the effect of reducing the cost is achieved.
Description
Technical Field
The invention relates to the technical field of radiotherapy, and particularly provides an assembly method of an adjustable space division radiotherapy collimator.
Background
Spatially segmented radiotherapy (SFRT) is a radiation therapy technique that allows relatively high but different radiation doses to be provided on large tumors while protecting surrounding healthy organs. Lead plates with holes machined are commonly used as collimators for spatial cutting therapy.
However, since spatial segmentation radiation therapy requires frequent adjustment of the radiation range, the radiation range needs to be adjusted and the scope of protection needs to be adjusted at different studies. However, because the beam width of the MBRT is less than 1000 mu m, a finishing instrument is required for manufacturing the collimator, a plurality of micron-sized holes are required to be formed in the lead plate, and the micron-sized holes are difficult to process, so that the production cost of the collimator is high. In addition, the distance between holes is also in the micron level, so that the processing difficulty is further increased, and the production cost of the collimator is further increased. Therefore, the existing space division radiotherapy has the problem of high cost because of high processing difficulty of the collimator.
Disclosure of Invention
The invention provides an assembling method of an adjustable space division radiotherapy collimator, which is used for solving the problem that the existing space division radiotherapy has high cost because of high processing difficulty of the collimator.
The technical scheme of the invention is as follows:
An assembly method of an adjustable space division radiotherapy collimator, comprising the following steps:
s1, counting the width of each radiation area and the interval between each radiation area;
S2, overlapping penetrating pieces capable of penetrating rays to form penetrating parts, calculating the number of the penetrating pieces, wherein the thickness of each penetrating part corresponds to the width of each radiation area, overlapping shielding pieces capable of blocking rays to form shielding parts, and calculating the number of the shielding pieces, wherein the thickness of each shielding part corresponds to the interval of each radiation area;
S3, sequentially superposing each penetrating part and the shielding part to form a collimation module, wherein shielding parts are respectively arranged at two sides of the collimation module;
s4, compressing the collimation modules from two sides, eliminating gaps among the penetrating parts, enabling the ray range transmitted by the penetrating parts to be accurate and reliable, and enabling the distance among the radiation ranges to be accurate and reliable.
In the scheme, before space division radiotherapy is performed each time, the penetrating parts and the shielding parts are assembled in a superposition mode according to different radiation ranges and the intervals of the radiation ranges, the thickness of each penetrating part is the same as the width of the corresponding radiation range, and the thickness of each shielding part is the same as the interval between the corresponding reflection range. After each penetrating part and each shielding part are formed by superposition, the penetrating parts and the shielding parts can be sequentially superposed, so that collimators which can be suitable for different radiotherapy ranges are obtained, and independent collimators are not required to be prepared for each space division radiotherapy, thereby reducing the cost of space division radiotherapy.
When the width of the radiotherapy range is large, in order to solve the problems that the number of the penetrating pieces to be overlapped is large, the number of the penetrating pieces is easy to be wrong and the error is large during the overlapping, and for this reason, the penetrating parts comprise penetrating pieces with the same thickness and/or the penetrating parts comprise penetrating pieces with different thicknesses.
In this scheme, the penetrating part can adopt the penetrating piece stack of different thickness to form, also can adopt the penetrating piece stack that the thickness is the same to form. Therefore, when the width of the radiotherapy range is larger, the penetrating piece with larger thickness and the penetrating piece with smaller thickness can be adopted to be overlapped, so that the number of penetrating pieces needing to be overlapped is reduced, and the probability of errors is reduced. The smaller the number of the penetrating sheets is, the smaller the error generated during superposition is, and the problem of large error caused by the large number of the penetrating sheets is solved.
When the interval of radiotherapy area is great, in order to solve the shielding piece quantity that needs the stack and big problem of quantity mistake and error big easily appears when the stack, for this reason, shielding portion includes the shielding piece that the thickness is the same and/or shielding portion includes the shielding piece that the thickness is different.
In this scheme, the shielding portion can adopt the shielding piece stack of different thickness to form, also can adopt the shielding piece stack that the thickness is the same to form. Therefore, when the width of the radiotherapy range is larger, the shielding sheets with larger thickness can be overlapped with the shielding sheets with smaller thickness, so that the number of shielding sheets needing to be overlapped is reduced, and the error probability is reduced. The smaller the number of the shielding sheets is, the smaller the error generated during superposition is, and the problem of large error caused by the large number of the shielding sheets is solved.
In order to solve the problem that the alignment module is difficult to fix due to irregular shape of the formed alignment module caused by the position deviation of each penetrating sheet or shielding sheet during superposition, in step S3, the alignment module is installed by adopting a fixing structure provided with a positioning groove, the width of the positioning groove is the same as that of the penetrating sheet, and the width of the penetrating sheet is the same as that of the shielding sheet.
In this scheme, each penetrates the width of piece and shielding piece the same, then can fix a position through a constant head tank, can overlap completely when guaranteeing to penetrate portion and shielding portion stack, when compressing tightly the collimation module from both sides, ensure that the collimation module everywhere atress is even, avoid the collimation module to appear the gap because of the atress is uneven, ensure the precision of collimation module.
When the length of radiotherapy scope is different, need adopt penetration piece and the shielding piece of different length to assemble the collimator, fixed knot constructs this moment and also needs to be applicable to penetration piece and the shielding piece of corresponding length, for solving fixed knot structure and not general and cause the problem with high costs, for this, fixed knot constructs including two fixed plates, and two fixed plates are provided with the constant head tank respectively, and two fixed plates are connected with the both sides of collimation module through the constant head tank respectively.
In this scheme, fixed knot constructs including two fixed plates, the both sides of fixed collimation module respectively, can be applicable to the penetration piece and the shielding piece of various length to reduce cost.
Preferably, in step S3, one end of the positioning slot is provided with a positioning structure, the end face of one shielding part at the end of the collimation module abuts against the positioning structure, then the penetrating part and the shielding part are alternately overlapped, and the shielding part is the last overlapped part in the positioning slot.
In this scheme, support the shielding portion from the downside by location structure, location structure can separate workstation and shielding portion, is convenient for take. And in the process of compacting the collimation module, support can be provided for the collimation module.
In order to solve the problem that the collimation module is easy to be damaged by compression in the compression process, in step S4, a compression structure which can slide with a fixed structure is adopted to compress the collimation module, and the compression structure is in interference fit with the fixed structure.
In this scheme, compress tightly structure and fixed knot structure interference fit, when compressing tightly through compressing tightly structure, then make compressing tightly structure remove through the mode of beating compressing tightly structure gently, interference fit's mode then can produce the resistance to compressing tightly structure's removal, reduces compressing tightly structure to the pressure of collimation module when beating, avoids the collimation module to damage when guaranteeing to compress tightly the collimation module. Meanwhile, the interference fit can also prevent the compression structure from moving when in use, and also avoid backing in the compression process, so that the alignment module is ensured to keep stable compression effect.
When the radiation ranges are different, the thicknesses of the collimation modules formed by superposition are also different. When the thickness of the stacked collimation module is smaller, the penetrating piece and the shielding piece still need to be moved to the positioning structure from one end of the positioning groove, the moving distance of the penetrating piece and the shielding piece is long, and the distance that the pressing structure needs to be moved is longer when the pressing and fastening are performed. Therefore, when the thickness of the collimation module is smaller, the problem that the operation is more time-consuming and inconvenient exists, and for this reason, the positioning structure is in sliding connection with the fixing structure, and the positioning structure is in interference fit with the fixing structure.
In this scheme, location structure's position is adjustable, consequently can be before the stack collimation module, adjust location structure's position earlier, shorten the travel distance who pierces through piece and shielding piece, also can reach the travel distance who reduces the compact structure, make the equipment operation more convenient. And the positioning structure can move before the collimation module is overlapped and assembled, so the positioning structure can be knocked by a large force to move, the collimation module cannot be damaged at the moment, and the operation of knocking the movement of the positioning structure is easier compared with lightly knocking the compression structure. Therefore, although the total stroke of the positioning structure and the pressing structure is unchanged, the operation difficulty can be reduced, and the operation is easier and more convenient. And the positioning structure is in interference fit with the fixing structure, so that the positioning structure can move when receiving a certain acting force, and the damage caused by overlarge pressure received by the collimation module is avoided.
Preferably, the positioning structure and the pressing structure are both buckles, the buckles are provided with sliding grooves, and the buckles are in sliding connection with the fixing structure through the sliding grooves.
Preferably, the thickness of the penetration sheet ranges from 200 to 1000 μm; the thickness of the shielding sheet ranges from 200 mu m to 1000 mu m; the penetrating sheet is a polylactic acid sheet formed by 3D printing.
In the scheme, the polylactic acid sheet is prepared by adopting 3D printing, so that the cost can be reduced under the condition of ensuring the precision.
The invention has the beneficial effects that:
According to the invention, the penetrating parts and the shielding parts with different thicknesses are assembled according to the radiation treatment range and the space between the radiation treatment ranges, and then the penetrating parts and the shielding parts are overlapped to form the collimation module, and the collimation module is pressed to form the collimator. The thickness of the penetrating part and the thickness of the shielding part can be assembled and adjusted according to the requirements, so that the device can be suitable for space division radiotherapy with different radiotherapy requirements, and the effect of reducing the cost is achieved.
Drawings
In order to more clearly illustrate the technical solutions of the present invention, the drawings that are needed for the description of the embodiments will be briefly described below, it being obvious that the drawings in the following description are only some embodiments of the present invention, and that other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic diagram of a collimator according to a first embodiment;
FIG. 2 is a schematic view of the structure of a U-shaped board in the first embodiment;
FIG. 3 is a schematic diagram of a collimating module according to a first embodiment;
FIG. 4 is a schematic view of another implementation of the collimator in the first embodiment;
FIG. 5 is a graph showing the effect of radiation beam irradiation in accordance with the first embodiment;
FIG. 6 is a schematic structural diagram of a buckle in the first embodiment;
fig. 7 is a schematic structural diagram of a collimator in the second embodiment;
Fig. 8 is a schematic structural diagram of a fixing plate in the second embodiment.
In the above figures, corresponding reference numerals are as follows:
1. A collimation module; 2. a fixing plate; 3. a buckle; 4. a positioning groove; 5. a positioning block; 6. a groove structure; 7. a chute; 8. a U-shaped plate; 11. a penetration sheet; 12. and a shielding sheet.
Detailed Description
The technical scheme of the invention is clearly and completely described through the specific implementation mode of the embodiment of the invention with the aid of the attached drawings.
Embodiment one.
As shown in fig. 3, a first embodiment provides an assembling method of an adjustable space division radiotherapy collimator, which includes the following steps:
S1, counting the width of each radiation area and the interval between each radiation area; the width of each radiation region is taken as the thickness of each penetration part, and the interval between each radiation region is taken as the thickness of each shielding part. Because the width and the interval of each radiation area in space division radiation treatment may be different, the width of each radiation area and the interval between each radiation area need to be counted separately, and the sequence of each radiation area is counted, so that the assembly is convenient;
S2, overlapping penetrating pieces capable of penetrating rays to form penetrating parts, calculating the number of the penetrating pieces, wherein the thickness of each penetrating part corresponds to the width of each radiation area, overlapping shielding pieces capable of blocking rays to form shielding parts, and calculating the number of the shielding pieces, wherein the thickness of each shielding part corresponds to the interval of each radiation area; for example, when the width of the first radiation region is 600 μm, the penetration part may be formed by overlapping three penetration pieces of 200 μm, and when the width of the second radiation region is 700 μm, the penetration part may be formed by overlapping one penetration piece of 500 μm and one penetration piece of 200 μm;
S3, sequentially superposing each penetrating part and the shielding part to form a collimation module, wherein shielding parts are respectively arranged at two sides of the collimation module;
S4, compressing the collimation modules from two sides, eliminating gaps among the penetrating parts, enabling the ray range transmitted by the penetrating parts to be accurate and reliable, and enabling the distance among the radiation ranges to be accurate and reliable. The operation of compacting the collimation module can improve the precision of the collimator and avoid inaccurate precision caused by gaps among penetrating sheets or shielding sheets in the collimator.
As shown in fig. 5, when the radiation beam irradiates the collimation module, the radiation beam can pass through the penetration part, so that spaced strip irradiation areas are formed at the positions where radiation treatment is required, and transverse heterogeneous dose distribution, namely a radiotherapy peak area and a radiotherapy valley area, is realized.
As shown in fig. 1, the alignment module is fixed by a fixing structure, a positioning structure and a pressing structure. The device is used for preventing the collimating module from loosening, and ensuring that the shielding part is tightly pressed on the penetrating part, so that the accurate and reliable size of the radiotherapy beam transmitted by the penetrating part is ensured.
When the number of the penetrating parts is two or more, the thickness of the penetrating parts can be different so as to be suitable for different radiotherapy requirements.
As shown in fig. 2, the fixing structure may be a U-shaped board, and two parallel inner side surfaces of the U-shaped board are provided with positioning grooves, the width of each positioning groove is the same as the width of the penetrating piece and the width of the shielding piece, and the width of each shielding piece is the same as the width of the penetrating piece, so that the penetrating piece and the shielding piece can be completely overlapped when being overlapped.
The horizontal portion in the middle of the U-shaped plate can be used as a positioning structure for supporting the collimation module from the lower side.
As shown in fig. 4, a positioning structure can be separately arranged on the U-shaped plate, and the collimation module is supported from the lower side through the positioning structure. When the independent positioning structure is arranged, the positioning structure and the pressing structure can adopt the same structure, so that the positioning structure and the pressing structure are universal, and the cost is reduced.
As shown in fig. 6, the positioning structure and the pressing structure may be buckle, the buckle is a cuboid structure, one surface of the cuboid structure is provided with a chute, the width of the chute is the same as the thickness of the U-shaped board, and the fixing plate is inserted into the chute, so that the buckle can slide along the length direction of the positioning slot. Four buckles are respectively arranged on each U-shaped plate, and the four buckles are respectively positioned at two sides of the alignment module, namely two buckles are respectively arranged at two sides of the alignment module. The end face of the collimation module is pressed by the buckle, so that the shielding part and the penetrating part in the collimation module are kept in a tightly attached state, no gap is reserved between the shielding part and the penetrating part, and the dimensional accuracy of the radiation beam current is ensured.
The U-shaped plate is characterized in that a positioning block is arranged in the sliding groove, the width of the positioning block is the same as that of the positioning groove, and when the U-shaped plate is connected with the sliding groove, the positioning block is also inserted into the positioning groove. Under the positioning action of the positioning block, the inclination of the buckling angle can be prevented. After the locating block is arranged in the middle of the chute, the chute is divided into two independent groove structures.
The buckle and the U-shaped plate can be in interference fit.
That is, the positioning structure and the pressing structure are slidably connected with the fixing structure, and the positioning structure and the pressing structure are in interference fit with the fixing structure.
Tungsten can be adopted as the material of the shielding part, the density of the tungsten is higher than that of the lead, the tungsten is not easy to deform, the tungsten and particles do not react and are nontoxic, the defect of the lead can be overcome well, and the accompanying toxic hazard and the mixed waste treatment cost are eliminated. The shielding may also be of a material that blocks the radiation beam current, such as bismuth, rhenium, thorium, etc.
The material of the penetrating part can adopt polylactic acid, and the radiation beam has good trafficability on the penetrating part made of the polylactic acid, so that the influence of the penetrating part on the intensity of the radiation beam can be avoided. The material of the penetration portion may also be PETG polyethylene terephthalate, ABS acrylonitrile butadiene styrene copolymer, PC polycarbonate, etc. which allows radiation beam flow.
The shield sheets stacked to form the shield portion may include shield sheets having the same thickness, or may include shield sheets having different thicknesses.
For example, the thicknesses of the shield sheets that are superimposed to form the shield portion are all the same.
For another example, the thicknesses of the shield sheets stacked to form the shield portion are all different.
For another example, the thicknesses of the shield sheets overlapping to form the shield portion are the same, and the thicknesses of the remaining shield sheets are different.
The penetrating pieces stacked to form the penetrating portions may include penetrating pieces having the same thickness, or may include penetrating pieces having different thicknesses.
For example, the thickness of the penetration pieces that are superimposed to form the penetration portion are all the same.
For another example, the thickness of the penetration pieces that are superimposed to form the penetration portions are all different.
For another example, the thickness of the partially penetrated sheet overlapping to form the penetrated portion is the same, and the thicknesses of the remaining penetrated sheets are different.
The thickness of the shielding sheet is in the range of 200-1000 μm. The thickness of the penetration sheet 11 ranges from 200 to 1000 μm.
In the above steps, the polylactic acid sheet may be produced by 3D printing.
For example, a rectangular parallelepiped polylactic acid sheet model is drawn by design software, and the thickness of the polylactic acid sheet ranges from 200 μm to 1000 μm. The STL format file is exported and the polylactic acid sheet model is sliced by the Bambu Studio software. Selecting a nozzle model of the printer: 0.2mm.
Then set 3D printing parameters, including: first layer speed: 40mm/s; first layer filling: 70mm/s; speed of the outer wall: 120mm/s; speed of inner wall: 150mm/s; sparse filling: 100mm/s; and (3) filling the inner part with solid: 150mm/s. Polylactic acid is selected as printing consumable yarn, the diameter is 1.75mm, the density is 1.26g/cm < 3 >, the nozzle setting temperature is 190-240 ℃, and the hot bed temperature is 35 ℃. And taking the printed polylactic acid sheet out of the hot bed.
Embodiment two:
the second embodiment provides an assembling method of an adjustable space division radiotherapy collimator, which is different from the first embodiment in the fixed structure in the second embodiment.
As shown in fig. 7 and 8, the fixing result includes two fixing plates, which are rectangular plates, and a positioning slot is provided on one side of each rectangular plate, wherein the width of the positioning slot is the same as that of the collimating module, and both sides of the collimating module can be inserted into the positioning slot. The width of the shielding part is the same as that of the penetrating part, so that the positioning groove can simultaneously form constraint on the shielding part and the penetrating part. When two fixing components are respectively inserted into two sides of the collimation module, the collimation module is restrained by the positioning groove, so that the collimation module can only move along the length direction of the positioning groove. The shielding part and the penetrating part are both plate-shaped structures, and the shielding part and the penetrating part are perpendicular to the fixed plate.
The width of the sliding groove is the same as the thickness of the fixing plate, and the fixing plate is inserted into the sliding groove, so that the buckle can slide along the length direction of the fixing plate. Two buckles are respectively arranged on each fixing plate and are respectively positioned on two sides of the collimation module, and the two buckles respectively compress the collimation module from two sides, so that a shielding part and a penetrating part in the collimation module are kept in a tightly-attached state, no gap is reserved between the shielding part and the penetrating part, and the dimensional accuracy of the radiation beam current is ensured to meet the requirement.
When the lengths of the radiotherapy ranges are different, the collimating module is formed by overlapping penetrating pieces with different lengths and shielding pieces with the same length as the penetrating pieces. At this time, since the two fixing plates fix the collimation module from two sides respectively, the technical scheme of the second embodiment can be applied to penetrating pieces and shielding pieces with different lengths, thereby reducing the cost of the fixing structure.
Claims (8)
1. An assembly method of an adjustable space division radiotherapy collimator is characterized by comprising the following steps:
s1, counting the width of each radiation area and the interval between each radiation area;
S2, overlapping penetrating pieces capable of penetrating rays to form penetrating parts, calculating the number of the penetrating pieces, wherein the thickness of each penetrating part corresponds to the width of each radiation area, overlapping shielding pieces capable of blocking rays to form shielding parts, and calculating the number of the shielding pieces, wherein the thickness of each shielding part corresponds to the interval of each radiation area;
S3, sequentially superposing each penetrating part and the shielding part to form a collimation module, wherein shielding parts are respectively arranged at two sides of the collimation module;
s4, compacting the collimation module from two sides, eliminating gaps among the penetrating parts, enabling the ray range transmitted by the penetrating parts to be accurate and reliable, enabling the interval among the radiation ranges to be accurate and reliable,
In step S3, a collimation module is installed by adopting a fixed structure provided with a positioning groove, the width of the positioning groove is the same as the width of a penetrating piece, the width of the penetrating piece is the same as the width of a shielding piece,
In step S3, one end of the positioning slot is provided with a positioning structure, the end face of one shielding part at the end of the collimation module abuts against the positioning structure, then the penetrating part and the shielding part are alternately overlapped, and the shielding part is the last overlapped part in the positioning slot.
2. The method of assembling an adjustable spatial division radiotherapy collimator according to claim 1, wherein the penetration portions comprise penetration pieces of the same thickness and/or the penetration portions comprise penetration pieces of different thicknesses.
3. The method of assembling an adjustable spatial division radiotherapy collimator according to claim 1, wherein the shielding parts comprise shielding sheets of the same thickness and/or the shielding parts comprise shielding sheets of different thicknesses.
4. The method for assembling the space-adjustable split radiotherapy collimator according to claim 1, wherein the fixing structure comprises two fixing plates, the two fixing plates are respectively provided with a positioning groove, and the two fixing plates are respectively connected with two sides of the collimation module through the positioning grooves.
5. The method of assembling an adjustable spatial division radiotherapy collimator according to claim 1, wherein in step S4, a compression structure slidable with a fixing structure is used to compress the collimation module, and the compression structure is in interference fit with the fixing structure.
6. The method of claim 5, wherein the positioning structure is slidably coupled to the fixed structure, and wherein the positioning structure is in an interference fit with the fixed structure.
7. The method of claim 6, wherein the positioning structure and the pressing structure are both buckles, the buckles are provided with sliding grooves, and the buckles are slidably connected with the fixing structure through the sliding grooves.
8. The method of assembling an adjustable spatial division radiotherapy collimator of claim 1, wherein the thickness of the penetration piece is in the range of 200-1000 μm;
the thickness of the shielding sheet ranges from 200 mu m to 1000 mu m;
The penetrating sheet is a polylactic acid sheet formed by 3D printing.
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Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112891761A (en) * | 2021-02-10 | 2021-06-04 | 戴建荣 | Multi-leaf collimator for radiotherapy machine and radiotherapy machine |
| CN113368413A (en) * | 2021-07-13 | 2021-09-10 | 山东第一医科大学附属肿瘤医院(山东省肿瘤防治研究院、山东省肿瘤医院) | Blade group, linkage type multi-blade collimator and linkage method thereof |
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| JPS61249452A (en) * | 1985-04-30 | 1986-11-06 | 株式会社東芝 | X-ray diagnostic apparatus |
| KR200365827Y1 (en) * | 2004-07-27 | 2004-10-26 | 주식회사 핵광산업 | Radioactive ray shelter and shelter wall structure using the radioactive ray shelter |
| JP2011189115A (en) * | 2010-02-19 | 2011-09-29 | Fujifilm Corp | Radiographic apparatus |
| CN202221663U (en) * | 2011-08-13 | 2012-05-16 | 四川瑞迪医疗科技有限公司 | Physical compensator for radiation therapy and its special mounting plate |
| JP2013088265A (en) * | 2011-10-18 | 2013-05-13 | Katsuhiro Dobashi | Radiation collimator and method for manufacturing the radiation collimator |
| KR101424112B1 (en) * | 2012-09-19 | 2014-08-06 | 고려대학교 산학협력단 | Collimator assembly |
| GB201703785D0 (en) * | 2017-03-09 | 2017-04-26 | Univ Bristol | Radiation detector |
| CN212394940U (en) * | 2019-12-31 | 2021-01-26 | 杭州美诺瓦医疗科技股份有限公司 | X-ray shielding device based on light field of beam light device and X-ray inspection device |
| CN213760249U (en) * | 2020-11-26 | 2021-07-23 | 四川大学华西第四医院 | Radiotherapy lead protective tool |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN112891761A (en) * | 2021-02-10 | 2021-06-04 | 戴建荣 | Multi-leaf collimator for radiotherapy machine and radiotherapy machine |
| CN113368413A (en) * | 2021-07-13 | 2021-09-10 | 山东第一医科大学附属肿瘤医院(山东省肿瘤防治研究院、山东省肿瘤医院) | Blade group, linkage type multi-blade collimator and linkage method thereof |
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