A medical cyclotron radiation shielding performance detection method and device

Abstract

This invention relates to the field of radiation measurement technology, specifically to a method and apparatus for testing the radiation shielding performance of a medical cyclotron. The method includes: acquiring target radiation equivalent sequences corresponding to different preset regions in the medical cyclotron to be tested; determining the radiation index configuration for each preset region; selecting regions to be shielded; selecting location points representing corner positions; determining the geometric inertia contribution and nonlinear inertia contribution for each shielded region; and determining the radiation inertia level for each shielded region based on the geometric inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence. This invention, by analyzing the measured target radiation equivalent sequence, enables the testing of the radiation shielding performance of a medical cyclotron, improving the accuracy of radiation shielding performance testing for medical cyclotrons.

Description

Technical Field

[0001] This invention relates to the field of radiation measurement technology, specifically to a method and apparatus for testing the radiation shielding performance of a medical cyclotron. Background Technology

[0002] A medical cyclotron is an accelerator device used in the medical field, primarily for radiotherapy and medical imaging. Radiotherapy can include, but is not limited to, proton therapy and heavy ion therapy; medical imaging can include positron emission tomography (PET). Medical cyclotrons typically generate high-energy radiation by accelerating charged particles, used to treat diseases such as cancer. The accelerated charged particles can be, but are not limited to, protons, electrons, and ions. To protect patients, operators, and the environment, radiation shielding performance testing of medical cyclotrons is crucial. Currently, the common method for radiation shielding performance testing is based on the radiation dose equivalent rate. Specifically, a higher radiation dose equivalent rate indicates poorer radiation shielding performance. The radiation dose equivalent rate can be the X-ray radiation dose equivalent rate.

[0003] However, when testing the radiation shielding performance of medical cyclotrons based on radiation dose equivalent rate, the following technical problems often arise:

[0004] In the process of testing the radiation shielding performance of medical cyclotrons, if only the radiation dose equivalent rate is considered, the accuracy of the radiation shielding performance test may be poor due to the single factor being considered. Summary of the Invention

[0005] To address the technical problem of poor accuracy in testing the radiation shielding performance of medical cyclotrons, this invention proposes a method and apparatus for testing the radiation shielding performance of medical cyclotrons.

[0006] In a first aspect, the present invention provides a method for testing the radiation shielding performance of a medical cyclotron, the method comprising:

[0007] Obtain the target radiation equivalent sequence corresponding to different preset regions in the medical cyclotron to be tested;

[0008] Based on the differences between the target radiation equivalents in the target radiation equivalent sequence corresponding to each preset area, determine the radiation index allocation amount corresponding to each preset area;

[0009] Based on the radiation index configuration corresponding to the preset area, select the radiation shielding area from all preset areas;

[0010] From the medical cyclotron accelerators to be tested, select the position points that represent the corner positions as the target position points;

[0011] The geometric position inertia contribution of each radiation shielding area is determined based on the distance between each radiation shielding area and each target location point.

[0012] Based on the difference in radiation equivalent variation between each radiation shielding area and other radiation shielding areas with different preset radiation shielding materials, the nonlinear inertial contribution of each radiation shielding area is determined.

[0013] The radiation inertia level of each radiation shielding area is determined based on the geometric inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence corresponding to each radiation shielding area.

[0014] In conjunction with the first aspect above, in one possible implementation, obtaining the target radiation equivalent sequence corresponding to different preset regions in the medical cyclotron to be tested includes:

[0015] Obtain the X-ray dose equivalent rate, gamma radiation dose equivalent rate, and neutron dose equivalent rate for each preset region at each preset time within a preset start-up time period;

[0016] The average values ​​of the X-ray dose equivalent rate, gamma radiation dose equivalent rate, and neutron dose equivalent rate of each preset region at each preset time are used to determine the target radiation equivalent of each preset region at each preset time.

[0017] The target radiation equivalent of each preset region at all preset times is used to form a target radiation equivalent sequence for each preset region.

[0018] In conjunction with the first aspect above, in one possible implementation, determining the radiation index allocation amount for each preset region based on the differences between target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region includes:

[0019] The radiation variation difference for each preset region is determined based on the absolute value of the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region.

[0020] The radiation equivalent abrupt change factor corresponding to each preset region is determined based on the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region.

[0021] Based on the radiation variation differences and radiation equivalent abrupt change factors corresponding to each preset area, the radiation index allocation amount corresponding to each preset area is determined. Among them, the radiation variation differences and radiation equivalent abrupt change factors are positively correlated with the radiation index allocation amount.

[0022] In conjunction with the first aspect above, in one possible implementation, determining the radiation variation difference corresponding to each preset region based on the absolute value of the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region includes:

[0023] Any preset region is defined as a marked region, and the absolute value of the difference between each adjacent target radiation equivalent in the target radiation equivalent sequence corresponding to the marked region is defined as the target difference, thus obtaining the target difference set corresponding to the marked region;

[0024] The sum of all target differences in the target difference set corresponding to the marked region is determined as the radiation change difference corresponding to the marked region.

[0025] In conjunction with the first aspect above, in one possible implementation, determining the radiation equivalent abrupt change factor corresponding to each preset region based on the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region includes:

[0026] Any preset area is defined as a marked area, and the difference between each adjacent target radiation equivalent in the target radiation equivalent sequence corresponding to the marked area is defined as a reference difference, thus obtaining the reference difference set corresponding to the marked area;

[0027] The largest reference difference is selected from the set of reference differences corresponding to the marked region and used as the radiation equivalent abrupt change factor corresponding to the marked region.

[0028] In conjunction with the first aspect above, in one possible implementation, determining the geometric position inertia contribution of each radiation-shielded area based on the distance between each radiation-shielded area and each target location point includes:

[0029] Any area to be shielded from radiation is determined as a candidate area, and the distance between the centroid of the candidate area and each target location point is determined as the reference distance between the candidate area and each target location point.

[0030] The minimum value among the reference distances between the candidate region and all target location points is determined as the candidate radiation distance corresponding to the candidate region;

[0031] Based on the candidate radiation distance corresponding to the candidate region, the geometric position inertia contribution of the candidate region is determined, wherein the candidate radiation distance and the geometric position inertia contribution are negatively correlated.

[0032] In conjunction with the first aspect above, in one possible implementation, determining the nonlinear inertia contribution of each radiation-shielding region based on the difference in radiation equivalent variation between each radiation-shielding region and other radiation-shielding regions using different preset radiation shielding materials includes:

[0033] Obtain the target radiation equivalent sequence for each radiation shielding area after installing each preset radiation shielding material, and use it as the reference radiation equivalent sequence for each radiation shielding area under each preset radiation shielding material;

[0034] Based on the target radiation equivalent sequence corresponding to each radiation shielding area and its reference radiation equivalent sequence under all types of preset radiation shielding materials, and the target radiation equivalent sequence corresponding to each other radiation shielding area and its reference radiation equivalent sequence under all types of preset radiation shielding materials, the radiation shielding variation difference between each radiation shielding area and each other radiation shielding area is determined.

[0035] The largest difference in radiation shielding variation between each radiation shielding area and all other radiation shielding areas is selected as the nonlinear inertia contribution for each radiation shielding area.

[0036] In conjunction with the first aspect above, in one possible implementation, the formula corresponding to the difference in radiation shielding variation between the radiation-shielded area and other radiation-shielded areas is:

[0037] ;

[0038] ;

[0039] ;in, It is the first The radiation shielding area and the first Differences in radiation shielding variations between individual radiation shielding areas; ,and and These are the serial numbers of different radiation shielding areas; It is an absolute value function; Indicates the first The radiation shielding variation of an area to be shielded from radiation under different preset radiation shielding materials; Indicates the first The radiation shielding variation of an area to be shielded from radiation under different preset radiation shielding materials; This refers to the number of preset radiation shielding materials; It is the type number of the preset radiation shielding material; It is the first The radiation shielding area is in the first The mean of all elements in the reference radiation equivalent sequence under a preset radiation shielding material; It is the first The mean of all elements in the target radiation equivalent sequence corresponding to a radiation shielding area; It is the first The radiation shielding area is in the first The mean of all elements in the reference radiation equivalent sequence under a preset radiation shielding material; It is the first The mean of all elements in the target radiation equivalent sequence corresponding to a radiation shielding area.

[0040] In conjunction with the first aspect above, in one possible implementation, determining the radiation inertia level corresponding to each radiation-shielding area based on the geometrical inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence corresponding to each radiation-shielding area includes:

[0041] Based on the geometric position inertia contribution and nonlinear inertia contribution corresponding to each radiation shielding area, the target inertia value corresponding to each radiation shielding area is determined. The geometric position inertia contribution and nonlinear inertia contribution are both positively correlated with the target inertia value.

[0042] The radiation inertia level of each radiation shielding area is determined based on the maximum value and target inertia value in the target radiation equivalent sequence. The maximum value and target inertia value in the target radiation equivalent sequence are positively correlated with the radiation inertia level.

[0043] Secondly, the present invention provides a device for testing the radiation shielding performance of a medical cyclotron accelerator, the device comprising:

[0044] The data acquisition module is used to acquire the target radiation equivalent sequence corresponding to different preset regions in the medical cyclotron under test;

[0045] The radiation index allocation determination module is used to determine the radiation index allocation for each preset area based on the differences between the target radiation equivalents in the target radiation equivalent sequence corresponding to each preset area.

[0046] The area filtering module is used to filter out radiation shielding areas from all preset areas based on the radiation index configuration corresponding to the preset areas.

[0047] The location filtering module is used to filter out location points that represent the corner positions from the medical cyclotron to be tested, as target location points;

[0048] The geometric position inertia contribution determination module is used to determine the geometric position inertia contribution of each shielded area to be radiated based on the distance between each shielded area to be radiated and each target location point.

[0049] The nonlinear inertial contribution module is used to determine the nonlinear inertial contribution of each radiation shielding area based on the difference in radiation equivalent variation between each radiation shielding area and other radiation shielding areas with different preset radiation shielding materials.

[0050] The radiation inertia level determination module is used to determine the radiation inertia level of each area to be radiated based on the geometric inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence of each area to be radiated.

[0051] Thirdly, a server is provided, including a memory and a processor. The memory is used to store executable program code, and the processor is used to call and run the executable program code from the memory, causing the device to perform the methods of the first aspect or any possible implementation thereof.

[0052] Fourthly, a computer program product is provided, comprising: computer program code, which, when run on a computer, causes the computer to perform the methods described in the first aspect or any possible implementation thereof.

[0053] Fifthly, a computer-readable storage medium is provided that stores computer program code, which, when executed on a computer, causes the computer to perform the methods described in the first aspect or any possible implementation thereof.

[0054] The present invention has the following beneficial effects:

[0055] This invention discloses a method and apparatus for testing the radiation shielding performance of a medical cyclotron. By analyzing the measured target radiation equivalent sequence, it achieves radiation shielding performance testing of the medical cyclotron, solving the technical problem of poor accuracy in radiation shielding performance testing of medical cyclotrons and improving the accuracy of such testing. Compared to methods that only consider radiation dose equivalent rate in testing the radiation shielding performance of medical cyclotrons, this invention comprehensively considers multiple factors related to radiation shielding performance during the radiation shielding performance testing process. These factors include the target radiation equivalent sequence corresponding to different preset areas, the amount of radiation index configuration, the target location point, the geometric position inertia contribution, and the nonlinear inertia contribution. The relatively rich consideration of factors improves the accuracy of radiation shielding performance testing of medical cyclotrons. Attached Figure Description

[0056] To more clearly illustrate the technical solutions and advantages in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0057] Figure 1 This is a flowchart of a method for testing the radiation shielding performance of a medical cyclotron accelerator according to the present invention;

[0058] Figure 2 This is a schematic diagram of the composition and structure of a medical cyclotron radiation shielding performance testing device according to the present invention.

[0059] Figure 3 This is a schematic diagram of the structure of a computer device according to the present invention. Detailed Implementation

[0060] To further illustrate the technical means and effects adopted by the present invention to achieve its intended purpose, the specific implementation methods, structures, features, and effects of the technical solution proposed according to the present invention are described in detail below with reference to the accompanying drawings and preferred embodiments. In the following description, different "one embodiment" or "another embodiment" do not necessarily refer to the same embodiment. Furthermore, specific features, structures, or characteristics in one or more embodiments can be combined in any suitable form.

[0061] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains.

[0062] refer to Figure 1 This document illustrates the flowchart of some embodiments of a method for testing the radiation shielding performance of a medical cyclotron accelerator according to the present invention. The method for testing the radiation shielding performance of a medical cyclotron accelerator includes the following steps:

[0063] Step S1: Obtain the target radiation equivalent sequence corresponding to different preset regions in the medical cyclotron to be tested.

[0064] The medical cyclotron to be tested can be any medical cyclotron whose radiation shielding performance is to be tested. A medical cyclotron is a device used to produce radioactive isotopes, widely used in nuclear medicine and radiotherapy. It is a specific type of particle accelerator primarily used to produce radioactive isotopes for diagnostic and therapeutic purposes. The preset area can be a pre-defined, artificially divided region within the medical cyclotron to be tested. All preset areas can cover possible radiation sources and scattering areas. For example, the preset area can be a critical region of the medical cyclotron. The critical regions of a medical cyclotron mainly include: Region A, Region B, the operating room area, and the surrounding environment area. The target radiation equivalent sequence can be a time series. The target radiation equivalent in the target radiation equivalent sequence corresponding to the preset area can characterize the radiation situation of the preset area. The target radiation equivalent can be an X-ray dose equivalent rate, a gamma radiation dose equivalent rate, or a neutron dose equivalent rate, and the target radiation equivalent can also be the average of the X-ray dose equivalent rate, gamma radiation dose equivalent rate, and neutron dose equivalent rate.

[0065] It's important to note that Area A is often one of the most critical areas in a medical cyclotron, housing the main accelerator components, including the vacuum tube, electromagnets, and magnet structures. The actual particle acceleration operations, such as acceleration, focusing, and modulation, are typically performed in Area A. Area B represents the beamline path from the main body of the medical cyclotron to the laboratory or detector, including the beam pipe, beamline elements, and possible beam monitoring equipment. Beamline elements can be, but are not limited to, magnets and collimators. The design of Area B ensures the transmission and control of the particle beam to guide the accelerated particle beam to the target experimental apparatus or detector for physics experiments. The control room area represents the control center of the medical cyclotron, typically located in a safe location away from radiation hazards. The control room houses the console, computer control system, monitoring equipment, and safety systems. Operators monitor and control the accelerator's operation here, execute experimental plans, adjust parameters, and ensure the safe operation of the equipment. The surrounding environment area is the area surrounding the medical cyclotron. The environment surrounding a medical cyclotron accelerator includes all areas directly connected to or near the accelerator, potentially including auxiliary facilities, cooling systems, power supplies, radiation shielding, and protective equipment. These environmental facilities provide the various services and protections necessary for the accelerator's operation. X-ray dose equivalent rate refers to the X-ray dose equivalent per unit time; it is an indicator of the potential harm that X-rays or other electromagnetic radiation may cause to a living organism. Gamma radiation dose equivalent rate refers to the gamma-ray radiation dose received per unit time; it is commonly used to describe the radiation intensity within a given area. Neutron dose equivalent rate refers to the neutron radiation dose received per unit time; it is typically used to assess radiation safety in environments such as nuclear facilities and medical radiation therapy.

[0066] As an example, this step may include the following steps:

[0067] The first step is to obtain the X-ray dose equivalent rate, gamma radiation dose equivalent rate, and neutron dose equivalent rate for each preset region at each preset time within the preset start-up time period.

[0068] The preset start-up time period can be the time period corresponding to the start-up process of the medical cyclotron accelerator under test. The preset time can be the data acquisition time. The duration between adjacent preset times can be equal to 1 / 50 of the duration corresponding to the preset start-up time period. For example, if the duration corresponding to the preset start-up time period is 50 seconds, then the duration between adjacent preset times can be 1 second.

[0069] For example, the X-ray dose equivalent rate of each preset area at each preset time can be obtained by an X-ray detector, the gamma radiation dose equivalent rate of each preset area at each preset time can be obtained by a gamma-ray detector, and the neutron dose equivalent rate of each preset area at each preset time can be obtained by a thermoluminescent dosimeter (TLD) or a neutron detector.

[0070] It should be noted that an X-ray detector is a device that converts X-ray energy into a recordable electrical signal. It receives X-ray irradiation and then generates an electrical signal proportional to the radiation intensity. A neutron detector, on the other hand, detects neutrons by utilizing the ionization of gas caused by the interaction of neutrons with boron or uranium, or by the activation of materials themselves after neutron irradiation. Neutron detectors are widely used in reactor nuclear power measurement or core neutron flux distribution measurement.

[0071] The second step is to determine the average values ​​of the X-ray dose equivalent rate, gamma radiation dose equivalent rate, and neutron dose equivalent rate of each preset region at each preset time as the target radiation equivalent for each preset region at each preset time.

[0072] The third step is to construct a target radiation equivalent sequence for each preset region by taking the target radiation equivalent of each preset region at all preset times.

[0073] Step S2: Determine the radiation index allocation amount for each preset area based on the differences between the target radiation equivalents in the target radiation equivalent sequence corresponding to each preset area.

[0074] As an example, this step may include the following steps:

[0075] The first step, determining the radiation variation difference for each preset region based on the absolute value of the difference between adjacent target radiation equivalents in the target radiation equivalent sequence for each preset region, may include the following sub-steps:

[0076] The first sub-step involves determining any preset region as a marked region, and determining the absolute value of the difference between each adjacent target radiation equivalent in the target radiation equivalent sequence corresponding to the marked region as the target difference, thereby obtaining the target difference set corresponding to the marked region.

[0077] The second sub-step involves determining the cumulative value of all target differences in the target difference set corresponding to the marked region as the radiation change difference corresponding to the marked region.

[0078] For example, the formula for determining the difference in radiation variation corresponding to a preset area can be:

[0079] ;in, It is the first The differences in radiation variation corresponding to each preset area. It is the sequence number of the preset area. It is the number of target radiation equivalents in the target radiation equivalent sequence. It is an absolute value function. It is the first The target radiation equivalent sequence corresponding to the preset region is the first... The radiation equivalent of a target. It is the first The target radiation equivalent sequence corresponding to the preset region is the first... The radiation equivalent of a target. Indicates the first The target difference set corresponding to the preset region is the first Individual differences in objectives.

[0080] It should be noted that accelerator startup is often accompanied by continuous changes in radiation equivalent. This change is an inherent property. Generally speaking, areas with more significant changes tend to have higher radiation shielding inertia, and these areas often require further radiation shielding. Areas with higher radiation shielding inertia typically indicate areas with poorer radiation shielding effectiveness. A larger value often indicates that during the startup process of the medical cyclotron accelerator under test, the first... The greater the change in the target radiation equivalent within a preset area, the more likely it is that during the startup process of the medical cyclotron accelerator under test, the greater the change in the first... The greater the degree of radiation variation within a preset area, the more likely it is to indicate that the first... The more likely a pre-defined area is to require radiation shielding.

[0081] The second step, determining the radiation equivalent abrupt change factor for each preset region based on the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region, may include the following sub-steps:

[0082] The first sub-step involves determining any preset region as a marked region and determining the difference between each adjacent target radiation equivalent in the target radiation equivalent sequence corresponding to the marked region as a reference difference, thereby obtaining the reference difference set corresponding to the marked region.

[0083] For example, the formula for determining the reference difference in the reference difference set corresponding to the preset region can be:

[0084] ;in, It is the first The reference difference set corresponding to the preset region is the first One reference difference. It is the sequence number of the preset area. It is the first The target radiation equivalent sequence corresponding to the preset region is the first... The radiation equivalent of a target. It is the first The target radiation equivalent sequence corresponding to the preset region is the first... The radiation equivalent of a target.

[0085] It should be noted that during the startup process of a medical cyclotron accelerator, there is often a period of rapid increase in radiation equivalent; this period typically coincides with the particle beam focusing phase. A larger value often indicates that during the startup process of the medical cyclotron accelerator under test, the first... The greater the degree of sudden change in the target radiation equivalent within a preset area, the more likely it is to indicate that the first... The greater the degree of change in radiation equivalent within a preset region, the more likely it is to indicate that the first... The more likely a pre-defined area is to require radiation shielding.

[0086] The second sub-step involves selecting the largest reference difference from the set of reference differences corresponding to the marked region, and using it as the radiation equivalent abrupt change factor corresponding to the marked region.

[0087] For example, the formula for determining the radiation equivalent abrupt change factor corresponding to a preset region can be:

[0088] ;in, It is the first Radiation equivalent abrupt change factor corresponding to a preset region. It is the sequence number of the preset area. It is a function that takes the maximum value. It is the first The first reference difference in the set of reference differences corresponding to each preset region. It is the first The second reference difference in the set of reference differences corresponding to each preset region. It is the first The reference difference set corresponding to the preset region is the first One reference difference. It is the first The reference difference set corresponding to the preset region is the first One reference difference. It is the number of target radiation equivalents in the target radiation equivalent sequence. It is the number of reference differences in the reference difference set. Constituting the first A set of reference differences corresponding to each preset region.

[0089] It should be noted that when A larger value often indicates that during the startup process of the medical cyclotron accelerator under test, the first... The greater the degree of sudden change in the target radiation equivalent within a preset area, the more likely it is to indicate that the first... The more likely a pre-defined area is to require radiation shielding, the more likely it is to require radiation shielding. Therefore, when The larger the value, the more likely it is to indicate the first... The more likely a pre-defined area is to require radiation shielding.

[0090] The third step is to determine the radiation index allocation for each preset area based on the differences in radiation variation and the sudden change factor of radiation equivalent.

[0091] Among them, the difference in radiation variation and the sudden change factor of radiation equivalent can both be positively correlated with the amount of radiation index equipped.

[0092] For example, the formula for determining the radiation index allocation for a preset area can be:

[0093] ;in, It is the first The amount of radiation indicators allocated to each preset area. It is the sequence number of the preset area. It is a normalization function. It is the first The differences in radiation variation corresponding to each preset area. It is the first Radiation equivalent abrupt change factor corresponding to a preset region.

[0094] It should be noted that when The larger the value, the more likely it is to indicate the first... The more likely a pre-defined area is to require radiation shielding. A larger value often indicates that during the startup process of the medical cyclotron accelerator under test, the first... The greater the variation in the target radiation equivalent of a preset area, the more likely it is to indicate that the first... The more likely a pre-defined area is to require radiation shielding, the more likely it is to require radiation shielding. Therefore, when The larger the value, the more likely it is to indicate the first... The more likely a pre-defined area is to require radiation shielding.

[0095] Step S3: Select the radiation shielding area from all preset areas according to the radiation index configuration corresponding to the preset area.

[0096] As an example, if the radiation index level corresponding to a preset area is greater than or equal to a preset radiation threshold, then the preset area is determined as the radiation shielding area. The preset radiation threshold can be a pre-set threshold. For example, the preset radiation threshold could be 0.9.

[0097] It should be noted that the area to be radiation shielded can be an area that requires further radiation shielding.

[0098] Step S4: Select the location points representing the corner positions from the medical cyclotron to be tested as the target location points.

[0099] The corner position can be the endpoint position of the medical cyclotron to be tested. The endpoint position is also called the vertex position.

[0100] It should be noted that the corners and edges of medical cyclotrons often represent the edges or corners of materials, where the possibility of radiation leakage is relatively high.

[0101] As an example, a predetermined number of location points representing corner positions can be selected from the medical cyclotron to be tested as target location points. The predetermined number can be a pre-set quantity. For example, the predetermined number could be 4.

[0102] It should be noted that the larger the preset number and the farther the distance between the target locations, that is, the more dispersed the target locations are, the more reasonable the selection of target locations tends to be.

[0103] Step S5: Determine the geometric position inertia contribution of each radiation shielding area based on the distance between each radiation shielding area and each target location point.

[0104] As an example, this step may include the following steps:

[0105] The first step is to determine any area to be shielded from radiation as a candidate area, and to determine the distance between the centroid of the candidate area and each target location point as the reference distance between the candidate area and each target location point.

[0106] The centroid of a candidate region can be represented by the center point of that candidate region.

[0107] The second step is to determine the minimum value among the reference distances between the above candidate regions and all target location points as the candidate radiation distance corresponding to the above candidate regions.

[0108] For example, the formula for determining the candidate radiation distance corresponding to the area to be shielded can be:

[0109] ;in, It is the first The candidate radiation distance corresponding to each radiation shielding area. It is the serial number of the area to be shielded from radiation. It is a function that takes the minimum value. It is the first The reference distance between the radiation shielding area and the first target location. It is the first The reference distance between the radiation shielding area and the second target location. It is the first The radiation shielding area and the first Reference distance between target locations. It is the sequence number of the target location point. It is the first The radiation shielding area and the first Reference distance between target locations. It represents the number of target location points.

[0110] It should be noted that the target location is often a corner or edge location where the possibility of radiation leakage is relatively high. When The smaller the size, the more likely it is to indicate the first The closer the area to be shielded from radiation is to a corner or edge where radiation leakage is more likely to occur, the more likely it is that the first area is the most likely to be ... The higher the radiation shielding inertness of the area to be shielded, the more likely it is that the first area has a higher radiation shielding inertness. The more radiation shielding an area needs, the more likely it is to require a greater level of radiation shielding.

[0111] The third step is to determine the geometric position inertia contribution of the candidate regions based on the candidate radiation distances corresponding to the candidate regions.

[0112] Among them, the candidate radiation distance can be negatively correlated with the geometric location inertial contribution.

[0113] For example, the formula for determining the geometric inertia contribution of the area to be shielded from radiation can be:

[0114] ;in, It is the first The geometrical positional inertia contribution of each radiation shielding area. It is the serial number of the area to be shielded from radiation. It is a natural exponential function. It is the first The candidate radiation distance corresponding to each radiation shielding area.

[0115] It should be noted that when The smaller the size, the more likely it is to indicate the first The closer the area to be shielded from radiation is to a corner or edge where radiation leakage is more likely to occur, the more likely it is that the first area is the most likely to be ... The more radiation-shielded an area is, the more likely it is to require a greater level of radiation shielding. Therefore, when The larger the value, the more likely it is to indicate the first... The higher the radiation shielding inertness of the area to be shielded, the more likely it is that the first area has a higher radiation shielding inertness. The more radiation shielding an area needs, the more likely it is to require a greater level of radiation shielding.

[0116] Step S6: Based on the difference in radiation equivalent change between each radiation shielding area and other radiation shielding areas with different preset radiation shielding materials, determine the nonlinear inertial contribution amount corresponding to each radiation shielding area.

[0117] The preset radiation shielding material can be a pre-set material for shielding radiation. For example, different types of preset radiation shielding materials can be lead plates of different thicknesses.

[0118] As an example, this step may include the following steps:

[0119] The first step is to obtain the target radiation equivalent sequence for each radiation shielding area after installing each preset radiation shielding material, which serves as the reference radiation equivalent sequence for each radiation shielding area under each preset radiation shielding material.

[0120] Among them, the target radiation equivalent in the target radiation equivalent sequence corresponding to the radiation shielding area after the preset radiation shielding material is installed can characterize the radiation situation of the radiation shielding area after the preset radiation shielding material is installed.

[0121] For example, if different types of preset radiation shielding materials are lead plates of different thicknesses, and there are two preset radiation shielding materials, namely 2 mm lead plates and 5 mm lead plates, then firstly, a 2 mm lead plate can be installed in the area to be shielded, and the target radiation equivalent sequence corresponding to the area to be shielded with the 2 mm lead plate installed can be obtained as the reference radiation equivalent sequence of the area to be shielded under the 2 mm lead plate; then, the installed 2 mm lead plate can be removed to restore the area to be shielded, and a 5 mm lead plate can be installed in the restored area to be shielded, and the target radiation equivalent sequence corresponding to the area to be shielded with the 5 mm lead plate installed can be obtained as the reference radiation equivalent sequence of the area to be shielded under the 5 mm lead plate.

[0122] The second step is to determine the radiation shielding variation difference between each radiation shielding area and each other radiation shielding area based on the target radiation equivalent sequence corresponding to each radiation shielding area and its reference radiation equivalent sequence under all types of preset radiation shielding materials, as well as the target radiation equivalent sequence corresponding to each other radiation shielding area and its reference radiation equivalent sequence under all types of preset radiation shielding materials.

[0123] For example, the formula for determining the difference in radiation shielding variation between the area to be shielded and other areas to be shielded can be:

[0124] ;

[0125] ;

[0126] ;in, It is the first The radiation shielding area and the first Differences in radiation shielding variations between areas to be shielded from radiation. ,and and These are the serial numbers of different radiation shielding areas. It is an absolute value function. Indicates the first The radiation shielding variation of a region to be shielded from radiation under different preset radiation shielding materials. Indicates the first The radiation shielding variation of a region to be shielded from radiation under different preset radiation shielding materials. This refers to the number of preset radiation shielding materials. It is the type number of the preset radiation shielding material, and the preset radiation shielding materials can be sorted according to their thickness. It is the first The radiation shielding area is in the first The mean of all elements in the reference radiation equivalent sequence under a preset radiation shielding material. It is the first The mean of all elements in the target radiation equivalent sequence corresponding to a radiation shielding area. It is the first The radiation shielding area is in the first The mean of all elements in the reference radiation equivalent sequence under a preset radiation shielding material. It is the first The mean of all elements in the target radiation equivalent sequence corresponding to a radiation shielding area.

[0127] It should be noted that selecting and filling shielding materials based on the radiation characteristics of different local regions within a cyclotron can significantly mitigate the adverse effects of accelerator radiation. During this process, the radiation characteristics in different regions often exhibit nonlinear changes depending on the material, leading to the formation of inert radiation domains. The causes of these nonlinear changes can include the interaction between the radiation type and the shielding material, and the influence of the shielding material's distribution and geometry on the shielding effect. Therefore, to reduce errors in the selection and filling of radiation shielding materials caused by nonlinear changes, thereby improving shielding performance and saving on material costs, it is often necessary to analyze the radiation inertia situation and implement multi-composite shielding at different levels. Generally, the higher the degree of nonlinearity, the greater its contribution to the inertia value. When an area, due to its interaction with the shielding material, does not experience a significant reduction in radiation equivalent even with increasing material thickness, composite material shielding is often required to improve the shielding effect. The nonlinearity caused by this interaction is often manifested in the fact that, with varying material thicknesses, the reduction in radiation equivalent in this area differs from the reduction in other areas, and the greater the difference, the higher the nonlinearity. and This can characterize the radiation equivalent in different regions under the addition of shielding materials. When The larger the value, the more likely it is to indicate the first... The greater the difference in radiation shielding variation between the first radiation-shielding area and other radiation-shielding areas, the more likely it is that the first... The greater the difference in radiation equivalent between the shielded area and other areas, the more effective the shielding will be, given the same material, indicating that the shielding effect is different. The greater the difference in shielding effectiveness between one radiation-shielding area and other radiation-shielding areas, the more pronounced the nonlinearity tends to be, and the more likely it is that the shielding effect of the first radiation-shielding area differs from that of other radiation-shielding areas. The higher the radiation shielding inertness of the area to be shielded from radiation, the better.

[0128] The third step is to select the largest difference in radiation shielding change from the differences between each radiation shielding area and all other radiation shielding areas, and use it as the nonlinear inertia contribution amount corresponding to each radiation shielding area.

[0129] For example, any region to be shielded from radiation can be designated as a candidate region, and each region to be shielded from radiation other than the candidate region can be designated as a reference region. The largest difference in radiation shielding change between the candidate region and all reference regions can be selected as the nonlinear inertial contribution of the candidate region.

[0130] Step S7: Determine the radiation inertia level of each radiation shielding area based on the geometric inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence corresponding to each radiation shielding area.

[0131] As an example, this step may include the following steps:

[0132] The first step is to determine the target inertia value for each radiation shielding area based on the geometric inertia contribution and nonlinear inertia contribution of each area.

[0133] Among them, both the geometric positional inertia contribution and the nonlinear inertia contribution can be positively correlated with the target inertia value.

[0134] For example, the formula for determining the target inertia value corresponding to the radiation shielding area can be:

[0135] ;in, It is the first The target inertia value corresponding to the radiation shielding area. It is the serial number of the area to be shielded from radiation. and These are pre-set weights. The value range of can be (0, 1). For example, It can be 0.5. It is the first The numerical value corresponding to the nonlinear inertial contribution of each radiation shielding area. It is the first The geometrical positional inertia contribution of each radiation shielding area.

[0136] It should be noted that when The larger the value, the more likely it is to indicate the first... The higher the radiation shielding inertness of the area to be shielded, the more likely it is that the first area has a higher radiation shielding inertness. The more radiation shielding a region requires, the more likely it is to need stronger shielding measures. Multiple composite shielding is applied to the radiation-to-shield area. When The larger the value, the more likely it is to indicate the first... The higher the radiation shielding inertness of the area to be shielded, the better. Therefore, when The larger the value, the more likely it is to indicate the first... The more likely the area to be shielded from radiation is to be a highly inert area, the more necessary it is to shield the second area. Multiple composite shielding methods are used to shield the radiation-to-be-shielded areas.

[0137] The second step is to determine the radiation inertia level of each radiation shielding area based on the maximum value and target inertia value in the target radiation equivalent sequence corresponding to each radiation shielding area.

[0138] Among them, the maximum value and the target inertia value in the target radiation equivalent sequence are both positively correlated with the radiation inertia level.

[0139] For example, the formula for determining the radiation inertia level corresponding to the area to be shielded can be:

[0140] ;in, It is the first The radiation inertia level corresponding to the radiation shielding area. It is the serial number of the area to be shielded from radiation. It is a normalization function. It is the first The target inertia value corresponding to the radiation shielding area. It is the first The maximum value in the sequence of target radiation equivalents corresponding to each radiation shielding area.

[0141] It should be noted that when The larger the value, the more likely it is to indicate the first... The more likely the area to be shielded from radiation is to be a highly inert area, the more necessary it is to shield the second area. Multiple composite shielding is applied to the radiation-to-shield area. When The larger the value, the more likely it is to indicate the first... The radiation intensity is relatively higher within each area to be shielded from radiation. Therefore, when The larger the value, the more likely it is to indicate the first... The more likely the area to be shielded from radiation is to be a highly inert area, the more necessary it is to shield the second area. Multiple composite shielding methods are used to shield the radiation-to-be-shielded areas.

[0142] Optionally, determine the first The radiation inertia level corresponding to each radiation shielding area. The corresponding formula can also be:

[0143] .

[0144] Optionally, if the radiation inertia level of the area to be shielded is greater than the preset inertia level threshold, the area to be shielded is defined as a high-inertia area. The preset inertia level threshold can be a pre-set threshold, for example, the preset inertia level threshold can be 0.6. For such high-inertia areas, a multi-layer shielding structure can be designed. For example, the outer layer uses lead plates to shield X-rays and gamma rays, the middle layer uses boron polyethylene to shield neutrons, and the inner layer uses high-density concrete to provide additional shielding, so as to achieve multi-composite shielding.

[0145] Optionally, if the radiation inertia level of the area to be shielded is less than or equal to a preset inertia level threshold, the area to be shielded is designated as a low-inertia area, allowing for precise replenishment of shielding material in this area. For example, a lead plate of a preset thickness can be added to the low-inertia area. The preset thickness can be a pre-defined thickness, such as 5 millimeters.

[0146] refer to Figure 2 Based on the same inventive concept as the above-described method embodiments, this invention provides a medical cyclotron radiation shielding performance testing device. This device includes a memory, a processor, and a computer program stored in the memory and executable on the processor. When the computer program is executed by the processor, it implements the steps of a medical cyclotron radiation shielding performance testing method, specifically including:

[0147] Data acquisition module 201 is used to acquire the target radiation equivalent sequence corresponding to different preset regions in the medical cyclotron to be tested;

[0148] The radiation index allocation determination module 202 is used to determine the radiation index allocation for each preset area based on the difference between the target radiation equivalents in the target radiation equivalent sequence corresponding to each preset area.

[0149] The area filtering module 203 is used to filter out the radiation shielding area from all preset areas according to the radiation index configuration corresponding to the preset area;

[0150] The location filtering module 204 is used to filter out the location points that represent the corner positions from the above-mentioned medical cyclotron accelerator to be tested, as target location points;

[0151] The geometric position inertia contribution determination module 205 is used to determine the geometric position inertia contribution of each radiation shielding area based on the distance between each radiation shielding area and each target location point.

[0152] The nonlinear inertial contribution module 206 is used to determine the nonlinear inertial contribution of each radiation shielding area based on the difference in radiation equivalent change between each radiation shielding area and other radiation shielding areas in different preset radiation shielding materials.

[0153] The radiation inertia level determination module 207 is used to determine the radiation inertia level of each radiation shielding area based on the geometric position inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence corresponding to each radiation shielding area.

[0154] Figure 3 This is a schematic diagram of the structure of a computer device provided in an embodiment of the present invention. For example, as shown... Figure 3 As shown, the computer device 300 includes: a memory 301, a processor 302, and a computer program 303 stored in the memory 301 and running on the processor 302. When the processor 302 executes the computer program 303, the computer device can execute any of the aforementioned methods for testing the radiation shielding performance of a medical cyclotron accelerator.

[0155] Based on the same inventive concept as the above-described method embodiments, the present invention provides a server, including a memory and a processor. The memory is used to store executable program code, and the processor is used to call and run the executable program code from the memory, causing the device to execute any of the above-described methods for testing the radiation shielding performance of a medical cyclotron accelerator.

[0156] Based on the same inventive concept as the above-described method embodiments, the present invention provides a computer program product comprising: computer program code, which, when run on a computer, causes the computer to execute any of the above-described methods for testing the radiation shielding performance of a medical cyclotron accelerator.

[0157] Based on the same inventive concept as the above-described method embodiments, the present invention provides a computer-readable storage medium storing computer program code, which, when executed on a computer, causes the computer to perform any of the above-described methods for testing the radiation shielding performance of a medical cyclotron.

[0158] In summary, compared to considering only the radiation dose equivalent rate when testing the radiation shielding performance of medical cyclotrons, this invention comprehensively considers multiple factors related to radiation shielding performance during the radiation shielding performance testing process. These factors include the target radiation equivalent sequence corresponding to different preset areas, the amount of radiation index configuration, the target location point, the geometric position inertia contribution, and the nonlinear inertia contribution. The consideration of these factors is relatively rich, thereby improving the accuracy of radiation shielding performance testing of medical cyclotrons.

[0159] The above embodiments are only used to illustrate the technical solutions of the present invention, and are not intended to limit it. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention, and should all be included within the protection scope of the present invention.

Claims

1. A method of detecting the performance of a medical cyclotron radiation shield, characterized by, Includes the following steps: Obtain the target radiation equivalent sequence corresponding to different preset regions in the medical cyclotron to be tested; Based on the differences between the target radiation equivalents in the target radiation equivalent sequence corresponding to each preset area, determine the radiation index allocation amount corresponding to each preset area; Based on the radiation index configuration corresponding to the preset area, select the radiation shielding area from all preset areas; From the medical cyclotron accelerator to be tested, select the position points that represent the corner positions as the target position points; The geometric position inertia contribution of each radiation shielding area is determined based on the distance between each radiation shielding area and each target location point. Based on the difference in radiation equivalent variation between each radiation shielding area and other radiation shielding areas with different preset radiation shielding materials, the nonlinear inertial contribution of each radiation shielding area is determined. The radiation inertia level corresponding to each radiation shielding area is determined based on the geometric inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence corresponding to each radiation shielding area. The step of obtaining the target radiation equivalent sequence corresponding to different preset regions in the medical cyclotron to be tested includes: obtaining the X-ray dose equivalent rate, gamma radiation dose equivalent rate, and neutron dose equivalent rate of each preset region at each preset time within a preset start-up time period; determining the average of the X-ray dose equivalent rate, gamma radiation dose equivalent rate, and neutron dose equivalent rate of each preset region at each preset time as the target radiation equivalent of each preset region at each preset time; and constructing the target radiation equivalent sequence of each preset region at all preset times. The step of determining the radiation index allocation amount for each preset region based on the difference between target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region includes: determining the radiation change difference for each preset region based on the absolute value of the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region; determining the radiation equivalent abrupt change factor for each preset region based on the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region; and determining the radiation index allocation amount for each preset region based on the radiation change difference and the radiation equivalent abrupt change factor, wherein both the radiation change difference and the radiation equivalent abrupt change factor are positively correlated with the radiation index allocation amount. The step of determining the geometric position inertia contribution of each radiation-shielding area based on the distance between each radiation-shielding area and each target location point includes: determining any radiation-shielding area as a candidate area; determining the distance between the centroid of the candidate area and each target location point as the reference distance between the candidate area and each target location point; determining the minimum value among the reference distances between the candidate area and all target location points as the candidate radiation distance corresponding to the candidate area; and determining the geometric position inertia contribution of the candidate area based on the candidate radiation distance, wherein the candidate radiation distance and the geometric position inertia contribution are negatively correlated. The step of determining the nonlinear inertial contribution of each radiation-shielding area based on the difference in radiation equivalent variation between each radiation-shielding area and other radiation-shielding areas under different preset radiation shielding materials includes: obtaining the target radiation equivalent sequence for each radiation-shielding area after installing each preset radiation shielding material, as a reference radiation equivalent sequence for each radiation-shielding area under each preset radiation shielding material; determining the radiation shielding variation difference between each radiation-shielding area and each other radiation-shielding area based on the target radiation equivalent sequence for each radiation-shielding area and its reference radiation equivalent sequence under all types of preset radiation shielding materials, and the target radiation equivalent sequence for each other radiation-shielding area and its reference radiation equivalent sequence under all types of preset radiation shielding materials; and selecting the largest radiation shielding variation difference from the radiation shielding variation differences between each radiation-shielding area and all other radiation-shielding areas, as the nonlinear inertial contribution of each radiation-shielding area. The step of determining the radiation inertia level of each radiation-shielding area based on the geometric position inertia contribution, nonlinear inertia contribution, and target radiation equivalent sequence for each radiation-shielding area includes: determining the target inertia value for each radiation-shielding area based on the geometric position inertia contribution and nonlinear inertia contribution, wherein both the geometric position inertia contribution and the nonlinear inertia contribution are positively correlated with the target inertia value; and determining the radiation inertia level for each radiation-shielding area based on the maximum value in the target radiation equivalent sequence and the target inertia value, wherein both the maximum value in the target radiation equivalent sequence and the target inertia value are positively correlated with the radiation inertia level.

2. The method for testing the radiation shielding performance of a medical cyclotron accelerator according to claim 1, characterized in that, The step of determining the radiation variation difference corresponding to each preset region based on the absolute value of the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region includes: Any preset region is defined as a marked region, and the absolute value of the difference between each adjacent target radiation equivalent in the target radiation equivalent sequence corresponding to the marked region is defined as the target difference, thus obtaining the target difference set corresponding to the marked region; The sum of all target differences in the target difference set corresponding to the marked region is determined as the radiation change difference corresponding to the marked region.

3. The method for testing the radiation shielding performance of a medical cyclotron accelerator according to claim 1, characterized in that, The step of determining the radiation equivalent abrupt change factor corresponding to each preset region based on the difference between adjacent target radiation equivalents in the target radiation equivalent sequence corresponding to each preset region includes: Any preset area is defined as a marked area, and the difference between each adjacent target radiation equivalent in the target radiation equivalent sequence corresponding to the marked area is defined as a reference difference, thus obtaining the reference difference set corresponding to the marked area; The largest reference difference is selected from the set of reference differences corresponding to the marked region and used as the radiation equivalent abrupt change factor corresponding to the marked region.

4. The method for testing the radiation shielding performance of a medical cyclotron accelerator according to claim 1, characterized in that, The formula corresponding to the difference in radiation shielding variation between the radiation-shielding area and other radiation-shielding areas is: ； ； ;in, It is the first The radiation shielding area and the first Differences in radiation shielding variations between individual radiation shielding areas; ,and and These are the serial numbers of different radiation shielding areas; It is an absolute value function; Indicates the first The radiation shielding variation of an area to be shielded from radiation under different preset radiation shielding materials; Indicates the first The radiation shielding variation of an area to be shielded from radiation under different preset radiation shielding materials; This refers to the number of preset radiation shielding materials; It is the type number of the preset radiation shielding material; It is the first The radiation shielding area is in the first The mean of all elements in the reference radiation equivalent sequence under a preset radiation shielding material; It is the first The mean of all elements in the target radiation equivalent sequence corresponding to a radiation shielding area; It is the first The radiation shielding area is in the first The mean of all elements in the reference radiation equivalent sequence under a preset radiation shielding material; It is the first The mean of all elements in the target radiation equivalent sequence corresponding to a radiation shielding area.

5. A device for testing the radiation shielding performance of a medical cyclotron accelerator, characterized in that, It includes a processor and a memory, the processor being used to process instructions stored in the memory to implement a method for testing the radiation shielding performance of a medical cyclotron accelerator according to any one of claims 1-4.

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