Method, device and system for detecting radiation dose distribution when rays pass through human body

Abstract

The invention belongs to the technical field of radiation detection, and particularly relates to a radiation dose distribution detection device and method when rays pass through a human body, a liquid conveying device conveys a human tissue density simulation liquid to a set liquid level of a detection chamber, and a ray beam passes through the simulation liquid in the detection chamber; a semiconductor detector array with X-ray and proton beam dual-mode detection capability is emitted, the intensity of ray beams emitted from a detection chamber is converted into corresponding output electric signals, then radiation dose distribution conditions when rays enter a human body at different depths are obtained, and visual display is carried out through a three-dimensional gray level image. Based on the same inventive concept, the invention also provides a medium and a system which store a program of the method, and also provides a method for tracking a focus during precise treatment of the proton beam, and the method realizes X-ray real-time monitoring and linkage proton beam parameter regulation and control by utilizing radiation dose distribution of rays extracted by the device in human tissues. The method has the advantages of accurate irradiation positioning, efficient detection, stability, reliability and the like.

Description

Technical Field

[0001] The present invention belongs to the field of radiation detection technology and discloses a method, device, system and recording medium storing a program capable of executing the method for detecting radiation dose distribution when rays pass through the human body. In addition, a method for tracking lesions during proton beam precision therapy is also disclosed. Background Art

[0002] Proton therapy is an advanced radiotherapy technology. The energy transferred to human tissue by the proton beam during its travel (proton energy loss) is inversely proportional to the square of the proton's speed, and the energy loss is greatest near the end of the range, presenting a typical Bragg peak in terms of dosimetry. Therefore, the use of proton beams can accurately target and treat tumors while significantly reducing damage to surrounding normal tissues, providing more accurate treatment plans for patients with complex tumors, children with tumors, etc. During proton beam therapy, a CT scan that combines X-rays and computer technology before treatment can provide detailed cross-sectional images of the patient's body, helping doctors accurately locate the tumor's position, shape, size, and relationship to surrounding normal tissues, ensuring that the treatment equipment is correctly aligned with the target area to avoid deviations, etc.

[0003] This poses two problems:

[0004] First, how to obtain the relationship between the Bragg peak depth of a proton beam passing through human tissue and the proton beam output intensity, so that the depth of the Bragg peak can be adjusted to match the depth of the lesion by adjusting the proton beam output intensity, thereby achieving precise elimination of the lesion. The current technology for Bragg peak detection, which uses a stepper motor to adjust the position of the proton detector, requires the detector to move along the proton beam irradiation direction in a liquid simulating human tissue to find the position of the proton Bragg peak in the depth direction. The detection system has problems such as liquid turbulence, mechanical vibration, electromagnetic field disturbance, and difficulty in deriving the detection signal in the liquid. In addition, the detector and the output line need to be treated with anti-liquid seepage liquid. The system structure is complex, the detection efficiency is low, it is easy to wear and tear during use, and the system stability is poor. For example, the proton Bragg peak detection technology using multiple detectors arranged longitudinally requires multiple detectors to be deployed in the proton beam irradiation direction. The system is complex and expensive. Moreover, due to the discrete arrangement of the detectors, it is impossible to continuously detect the change of proton beam energy with proton range, and the obtained Bragg peak position is not accurate. In addition, it is necessary to correct the interference of the electromagnetic fields of the multiple proton detectors on the proton Bragg peak signal.

[0005] Secondly, during treatment, as the patient breathes or moves, the lesion may shift. How can the proton Bragg peak accurately track the target lesion in real time? Those skilled in the art can easily think of using X-rays for real-time lesion localization during proton therapy. However, because X-rays are electromagnetic waves (high-energy photons) rather than proton beams (physical particles), those skilled in the art have no motivation to conceive of using proton systems to detect the intensity of incident X-rays. Therefore, there are currently no reports mentioning detectors and systems that combine X-rays, CT scans, and proton beam Bragg peaks to meet the detection needs of proton therapy. Hospital radiology departments often use multiple systems with different principles to complete non-real-time detection of different radiation doses. Summary of the Invention

[0006] To solve the problems raised in the background art, the present invention provides a device for detecting radiation dose distribution when radiation passes through a human body, comprising: a radiation generator, a movable bracket, a detection chamber capable of displaying a liquid level, a liquid storage chamber filled with a liquid simulating human tissue density, a liquid transport device, a semiconductor detector array, and a data acquisition and analysis module;

[0007] Among them, the ray generator includes an X-ray generator and a proton beam generator; the ray generator is fixed on a mobile bracket, and the mobile bracket can make the ray generator to be detected be located directly above the detection chamber, with the emission port facing downward; the detection chamber is made of a material that does not block the passage of rays and has uniform density, and the bottom is horizontal and close to the semiconductor detector array; the detection chamber is connected to the liquid storage chamber through a liquid transport device; the semiconductor detector array is electrically connected to the data acquisition and analysis module; each detector chip in the semiconductor detector array can convert the intensity of the rays received at that position into an electrical signal; the data acquisition and analysis module collects the electrical signals output by the detectors at each position, and obtains the radiation dose distribution when the rays enter the human body at different depths by controlling the liquid level height, and visualizes it by establishing a three-dimensional grayscale image.

[0008] Preferably, the liquid transport device comprises a water pump connected to an inlet and outlet hose, for transporting the human tissue density simulation liquid to a set liquid level in the detection chamber.

[0009] Preferably, the semiconductor band gap width of the semiconductor detector array is ≥3.26 eV.

[0010] Preferably, the semiconductor material of the semiconductor detector array is ZnO or Ga2O3, and it has dual-mode detection capabilities of X-rays and proton beams, and is used to apply voltage through an energy supply device to convert the intensity of the rays it contacts into a corresponding output electrical signal.

[0011] Preferably, the semiconductor units in the semiconductor detector array are of a metal-semiconductor-metal structure, the metal electrodes on the semiconductor surface are silver electrodes or platinum electrodes, and the structural type is a bulk electrode structure or an interdigitated electrode structure.

[0012] Preferably, the interdigital electrode structure has an interdigital spacing of 0.001 to 0.5 mm, an interdigital length of 0.01 to 12 mm, an interdigital width of 0.001 to 0.5 mm, and the number of interdigits in each electrode is 5 to 100.

[0013] Based on the same inventive concept, the present application also provides a method for detecting radiation dose distribution when rays pass through a human body, using the above-mentioned device for detecting radiation dose distribution when rays pass through a human body, comprising the following steps:

[0014] S1. Transport the human tissue density simulation liquid to the set liquid level of the detection chamber through the liquid transport device and let it stand for 1 to 5 minutes;

[0015] S2. If X-ray detection is required, move the bracket so that the X-ray generator is directly above the detection room, with the emission port facing downward.

[0016] S3. transmitting an X-ray beam through a human tissue density simulating fluid in the detection chamber and into a semiconductor detector array;

[0017] S4. Each semiconductor in the semiconductor detector array converts the intensity of the X-rays it receives into a corresponding output electrical signal.

[0018] S5. The data acquisition and analysis module collects the output electrical signals of each semiconductor at the same liquid level. By controlling the liquid level, it obtains the radiation dose distribution when the X-ray enters the human body at different depths and creates a three-dimensional grayscale image for visualization.

[0019] S6. If proton beam detection is required, move the bracket so that the proton beam generator is directly above the detection chamber, with the emission port facing downward.

[0020] S7. emitting a proton beam through a human tissue density simulating fluid in the detection chamber and into a semiconductor detector array;

[0021] S8. Each semiconductor in the semiconductor detector array converts the strength of the proton beam into a corresponding output electrical signal.

[0022] S9. The data acquisition and analysis module collects the magnitude of the electrical signals output by each semiconductor at the same liquid level. By controlling the liquid level, it obtains the radiation dose distribution when the proton beam enters the human body at different depths and creates a three-dimensional grayscale image for visualization.

[0023] S10. Adjust the intensity of the output radiation of the proton beam generator and repeat steps S6-S9 to measure the relationship between the depth position distribution of the proton beam Bragg peak and the proton beam intensity.

[0024] Another embodiment of the present invention is to provide a non-transitory readable recording medium for storing one or more programs containing multiple instructions. When the instructions are executed, the processor will execute the method for detecting radiation dose distribution when rays pass through the human body.

[0025] The present invention also provides a radiation dose distribution detection system when rays pass through the human body, comprising a processing circuit and a memory electrically coupled thereto, characterized in that the memory is configured to store at least one program, the program comprising a plurality of instructions, and the processing circuit runs the program to execute the method for detecting the radiation dose distribution when rays pass through the human body.

[0026] In order to solve the problem that lesions shift in the depth direction with the patient's breathing during proton beam tumor therapy and are difficult to track in real time, the present invention also provides a method for tracking lesions during proton beam tumor therapy, comprising the following steps:

[0027] During tumor treatment, X-rays are continuously used to irradiate the lesion area, and signals are collected in real time using a semiconductor detector array and a data acquisition and analysis module placed at corresponding positions. The signals are compared with the electrical signals obtained in step S5 of the radiation dose distribution detection method when the rays pass through the human body to determine the real-time human tissue thickness corresponding to the section where the lesion is located.

[0028] Calculate in real time the depth of the lesion center from the epidermis during tumor treatment based on the ratio of the distances between the lesion center and the front and back walls of the human tissue as shown in the CT scan and the real-time human tissue thickness;

[0029] Based on the relationship between the depth position distribution of the proton beam Bragg peak and the proton beam intensity obtained in step S10 of the aforementioned radiation dose distribution detection method when the radiation passes through the human body, the intensity of the radiation output by the tumor treatment proton beam generator is adjusted in real time so that the depth position of its Bragg peak is the same as the depth of the lesion center from the epidermis.

[0030] Compared with the existing technology, the semiconductor detector array in the present invention is arranged outside the liquid storage room, and detection begins after the human tissue density simulation liquid is left to stand. There are no problems such as liquid turbulence, mechanical vibration, electromagnetic field disturbance, and difficulty in deriving detection signals in the liquid. There is no need to perform anti-liquid treatment on the detector and the export line; only a single system is needed to complete the detection of X-rays and proton beams. The system has a simple structure, high detection efficiency, no wear in use, and good system stability; it realizes the real-time adjustment of the intensity of the output rays of the proton beam generator during tumor treatment, so that the depth position of its Bragg peak tracks the center of the lesion. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] Figure 1 This is a structural diagram of a device for detecting radiation dose distribution when radiation passes through a human body according to an embodiment of the present invention;

[0032] Figure 2 This is the detection result under the embodiment of the present invention with a proton energy of 70 MeV, an output beam current of 200 nA, and a liquid level of 50 mm;

[0033] Figure 3 for Figure 2 The detection result within the first hexagram in the embodiment;

[0034] Figure 4 This is the detection result under the embodiment of the present invention with a proton energy of 100 MeV, an output beam current of 200 nA, and a liquid level of 80 mm;

[0035] Figure 5 for Figure 4 The detection result within the first hexagram in the embodiment;

[0036] Figure 6 This is the three-dimensional detection result at a liquid level of 20 cm with an X-ray energy of 6 MV, a dose of 100 mGy / s, and a liquid level of 20 cm in an embodiment of the present invention.

[0037] Figure 7 for Figure 6 The detection result within the first hexagram in the embodiment;

[0038] In the figure, 01-high-energy ray detection room; 02-liquid storage room; 03-liquid transport device; 04-wide bandgap semiconductor array detector; 05-data acquisition and analysis device. DETAILED DESCRIPTION

[0039] To make the objectives, technical solutions, and advantages of the embodiments of the present invention more clear, the technical solutions in the embodiments of the present invention will be described below in conjunction with the accompanying drawings. The described embodiments are part of the embodiments of the present invention, but not all of them. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without making any innovative efforts shall fall within the scope of protection of the present invention.

[0040] The following technical solutions and attached Figure 1-7 , specifically describes the implementation process of the present invention, including a device for detecting radiation dose distribution when rays pass through the human body and a method for detecting radiation dose distribution when rays pass through the human body using the device.

[0041] Example 1

[0042] This embodiment provides an X-ray and proton beam Bragg peak detection system based on wide bandgap semiconductors. The system controls the proton beam incident path depth by adjusting the liquid level above the wide bandgap semiconductor array detector, and detects the variation of the proton beam intensity with the incident path depth, thereby obtaining the three-dimensional distribution of the proton beam Bragg peak. Figure 1As shown, the high-energy ray detection chamber 01 is made of a 4mm thick acrylic glass plate with an opening at the top and a closed bottom and sides. It is 7cm long, 7cm wide, and 20cm high. In particular, it has an opening at the bottom for connecting a hose. The liquid storage chamber 02 is separated from the high-energy ray detection chamber 01 and is a closed container made of plastic material. It has an opening at the bottom for connecting a hose. The liquid stored is water (with a density similar to that of human tissue fluid, only used for feasibility testing; liquids with a closer density will be prepared in actual applications). The liquid transport device 03 is a water pump, which connects the high-energy ray detection chamber 01 and the liquid storage chamber 02 via a hose with a liquid buffering function. The flow rate of the water pump can be controlled by a computer. Wide-bandgap semiconductor array detector 04 is a ZnO-based MSM-type 14×14 array detector. Its substrate is quartz glass, and its metal electrodes are silver electrodes in the form of interdigitated electrodes. The interdigitated electrodes are spaced 0.01 mm apart, with a length of 0.1 mm and a width of 0.01 mm. Each electrode has six interdigitated electrodes. The detector is located below high-energy radiation detection chamber 01 and is connected to data acquisition and analysis device 05 via wires.

[0043] The experimental conditions are set as a proton beam with an energy of 70MeV and an output beam current of 200nA, and a 10V bias is applied to the detector. The proton beam emission end is aligned with the wide bandgap semiconductor array detector located below the high-energy ray detection chamber. After the proton beam begins to irradiate, while the proton beam lasts, the water pump switch is controlled by a computer to transport the water in the liquid storage chamber to the high-energy ray detection chamber, and the water level in the high-energy ray detection chamber can be observed to rise slowly. During this period, the data acquisition and analysis device can continuously collect the changes in current intensity on the ZnO-based array detector by applying a -10V bias, and analyze the distribution of the proton beam Bragg peak. The relationship between the density and thickness of the bottom material of the high-energy ray detection chamber is converted into a water-equivalent depth, and ultimately the precise measurement of the Bragg peak position in the water can be achieved. For example Figure 2-3 Figure 2 shows the three-dimensional detection results of the proton beam Bragg peak detection system of this embodiment at a proton energy of 70 MeV and an output beam current of 200 nA. The figure demonstrates the detection system's precise display of the three-dimensional Bragg peak dose distribution in proton water. The X and Y axes represent the lateral distribution of the proton beam, while the Z axis represents the water equivalent depth. Color depth indicates dose distribution weighting: darker colors indicate a greater percentage of proton beam dose, with the maximum dose occurring at 42 mm on the Z axis. Lighter colors indicate a smaller percentage of proton beam dose.

[0044] Example 2

[0045] This embodiment provides a wide-bandgap semiconductor-based X-ray and proton beam Bragg peak detection device. This device controls the proton beam's incident path depth by adjusting the liquid level above the wide-bandgap semiconductor array detector. This device detects how the proton beam intensity changes with the incident path depth, thereby obtaining the three-dimensional distribution of the proton beam's Bragg peak. The high-energy ray detection chamber 01 is made of a 4mm-thick acrylic glass plate, open at the top and closed at the bottom and sides. It is 7cm long, 7cm wide, and 20cm high. Specifically, it has an opening at the bottom for connecting a hose. The liquid storage chamber 02, separated from the high-energy ray detection chamber 01, is a sealed plastic container with an opening at the bottom for connecting a hose. The stored liquid is water. The liquid transport device 03 is a water pump, connecting the high-energy ray detection chamber 01 and the liquid storage chamber 02 via a hose that acts as a liquid buffer. The water pump's flow rate can be controlled by a computer. Wide-bandgap semiconductor array detector 04 is a 14×14 Ga2O3-based MSM array detector. Its substrate is sapphire, and its metal electrodes are silver electrodes in the form of interdigitated electrodes. The interdigitated electrodes are spaced 0.01 mm apart, with a length of 0.1 mm and a width of 0.01 mm. Each electrode has six interdigitated electrodes. The detector is located below high-energy radiation detection chamber 01 and is connected to data acquisition and analysis device 05 via wires.

[0046] The experimental conditions are set as a proton beam with an energy of 100MeV, an outgoing beam current of 200nA, and a 10V bias applied to the detector. The proton beam emission end is aligned with the wide bandgap semiconductor array detector located below the high-energy ray detection chamber. After the proton beam begins to irradiate, while the proton beam lasts, the water pump switch is controlled by a computer to transport the water in the liquid storage chamber to the high-energy ray detection chamber, and the water level in the high-energy ray detection chamber can be observed to rise slowly. During this period, the data acquisition and analysis device can continuously collect the changes in current intensity on the Ga2O3-based array detector by applying a -10V bias, and analyze the distribution of the proton beam Bragg peak. The relationship between the density and thickness of the bottom material of the high-energy ray detection chamber is converted into a water-equivalent depth, and ultimately the precise measurement of the Bragg peak position in the water can be achieved. As Figure 4-5 The following figure shows the three-dimensional detection results of the proton beam Bragg peak detection system of this embodiment at a proton energy of 100 MeV and an output beam current of 200 nA. The figure demonstrates the detection system's accurate representation of the three-dimensional dose distribution of the Bragg peak in proton water. The X and Y axes represent the lateral distribution of the proton beam, while the Z axis represents the water equivalent depth. The color depth indicates the dose distribution weight. Darker colors indicate a greater percentage of proton beam dose distribution, with the maximum dose occurring at 76 mm on the Z axis. Lighter colors indicate a smaller percentage of proton beam dose distribution.

[0047] Example 3

[0048] This embodiment provides an X-ray and proton beam Bragg peak detection system based on wide-bandgap semiconductors. The system controls the depth of the X-ray incident path by adjusting the liquid level above the wide-bandgap semiconductor array detector. It detects how X-ray intensity changes with incident path depth, thereby obtaining the three-dimensional distribution of X-rays. High-energy ray detection chamber 01 is made of a 4mm-thick acrylic glass plate, open at the top and closed at the bottom and sides. It is 7cm long, 7cm wide, and 20cm high. Specifically, it has an opening at the bottom for connecting a hose. Liquid storage chamber 02, separated from high-energy ray detection chamber 01, is a sealed plastic container with an opening at the bottom for connecting a hose. It stores water. Liquid transport device 03 is a water pump, connecting high-energy ray detection chamber 01 and liquid storage chamber 02 via a hose that acts as a liquid buffer. The pump's flow rate can be controlled by a computer. Wide-bandgap semiconductor array detector 04 is an 8×8 ZnO-based MSM array detector with a sapphire substrate and platinum electrodes in the form of interdigitated electrodes. The interdigitated electrodes are 0.01 mm apart, with a length of 0.1 mm and a width of 0.01 mm. Each electrode has six interdigitated electrodes. The detector is located below high-energy radiation detection chamber 01 and is connected to data acquisition and analysis device 05 via wires.

[0049] The experimental conditions are set as X-ray energy of 6MV, dose of 100mGy / s, and 10V bias applied to the detector. The X-ray emission end is aligned with the wide bandgap semiconductor array detector located below the high-energy ray detection chamber. After the X-ray irradiation begins, while the X-rays last, the water pump switch is controlled by a computer to transport the water in the liquid storage chamber to the high-energy ray detection chamber, and the water level in the high-energy ray detection chamber can be observed to rise slowly. During this period, the data acquisition and analysis device can continuously collect the changes in current intensity on the ZnO-based array detector by applying a -10V bias, and analyze the X-ray dose distribution. The relationship between the density and thickness of the bottom material of the high-energy ray detection chamber is converted into water equivalent depth, and ultimately the accurate measurement of the X-ray dose distribution in water can be achieved. As Figure 6-7 The following figure shows the 3D detection results of the X-ray detection system of this embodiment in water at an X-ray energy of 6 MV. The figure demonstrates the detection system's accurate representation of the 3D X-ray dose distribution in water. The X and Y axes represent the lateral X-ray distribution data, while the Z axis represents the water equivalent depth. Color depth indicates dose distribution weighting: darker colors indicate a greater percentage of X-ray dose distribution, with the maximum dose occurring at 45 mm on the Z axis. Lighter colors indicate a smaller percentage of X-ray dose distribution.

[0050] Example 4

[0051] This embodiment provides a method for tracking lesions during proton beam therapy. The method combines X-ray fluoroscopy signals used for monitoring during treatment with Figure 7 The signals obtained are compared to determine the real-time human tissue thickness corresponding to the section where the lesion is located; at a certain moment during treatment, the thickness of a certain section of the patient's chest at the center of the lesion is 126mm;

[0052] Early CT scans of this section showed that the distance ratio between the center of the lesion and the anterior and posterior walls of the human tissue was 1:2. During the treatment, the depth of the lesion center from the epidermis was calculated to be 42 mm in real time.

[0053] according to Figure 2-5 The relationship between the depth position distribution of the proton beam Bragg peak and the proton beam intensity was calculated. The proton beam generator parameters were adjusted in real time to make the emitted proton energy 70MeV, the emitted beam current 200nA and the output ray intensity. The depth position of the Bragg peak and the depth of the lesion center from the epidermis were both adjusted to 42mm.

[0054] It will be understood by those skilled in the art that embodiments of the present invention may be provided as methods, systems, or computer program products. Thus, the present invention may take the form of an entirely hardware embodiment, an entirely software embodiment, or an embodiment combining software and hardware. Furthermore, the present invention may take the form of a computer program product implemented on one or more computers containing computer-usable program code, or on available storage media (including but not limited to magnetic disk storage, CD-ROM, optical storage, etc.).

[0055] The present invention is described with reference to flowcharts and / or block diagrams of methods, devices (systems), and computer program products according to embodiments of the present invention. It should be understood that each process and / or block in the flowcharts and / or block diagrams, as well as combinations of processes and / or blocks in the flowcharts and / or block diagrams, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing device to produce a machine, so that the instructions executed by the processor of the computer or other programmable data processing device generate instructions for implementing the processes in the flowcharts and / or block diagrams. Figure 1 a process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0056] These computer program instructions may also be stored in a computer readable memory that can direct a computer or other programmable data processing device to work in a specific manner, so that the instructions stored in the computer readable memory produce an article of manufacture comprising an instruction device, which implements the process Figure 1 a process or multiple processes and / or boxes Figure 1 The function specified in one or more boxes.

[0057] These computer program instructions can also be loaded onto a computer or other programmable data processing device so that a series of operational steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing the instructions executed on the computer or other programmable device for implementing the process. Figure 1 a process or multiple processes and / or boxes Figure 1 A step that specifies a function in one or more boxes.

[0058] Compiling the above-mentioned method steps into a program and then storing it on a hard disk or other non-transitory storage medium constitutes an embodiment of the present invention's "a non-transitory readable recording medium"; and electrically connecting the storage medium to a computer processor and completing the detection of the radiation dose distribution when the rays pass through the human body through data processing constitutes an embodiment of the present invention's "a radiation dose distribution detection system when the rays pass through the human body".

[0059] Finally, it should be noted that the above descriptions are merely preferred embodiments of the present invention and are not intended to limit the present invention. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art will be able to modify the technical solutions described in the aforementioned embodiments or substitute equivalents for some of the technical features. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present invention shall be included within the scope of protection of the present invention.

Claims

1. A device for detecting radiation dose distribution when radiation passes through a human body, comprising: Radiation generator, mobile bracket, detection chamber capable of displaying liquid level, liquid storage chamber filled with human tissue density simulation liquid, liquid transport device, semiconductor detector array, data acquisition and analysis module; Among them, the ray generator includes an X-ray generator and a proton beam generator; the ray generator is fixed on a mobile bracket, and the mobile bracket can make the ray generator to be detected be located directly above the detection chamber, with the emission port facing downward; the detection chamber is made of a material that does not block the passage of rays and has uniform density, and the bottom is horizontal and close to the semiconductor detector array; the detection chamber is connected to the liquid storage chamber through a liquid transport device; the semiconductor detector array is electrically connected to the data acquisition and analysis module; each detector chip in the semiconductor detector array can convert the intensity of the rays received at that position into an electrical signal; the data acquisition and analysis module collects the electrical signals output by the detectors at each position, and obtains the radiation dose distribution when the rays enter the human body at different depths by controlling the liquid level height, and visualizes it by establishing a three-dimensional grayscale image.

2. The device for detecting radiation dose distribution when rays pass through a human body according to claim 1, characterized in that: The liquid transport device comprises a water pump connected with an inlet and outlet hose, and is used for transporting the human tissue density simulation liquid to a set liquid level in the detection chamber.

3. The device for detecting radiation dose distribution when rays pass through a human body according to claim 2, characterized in that: The semiconductor band gap width of the semiconductor detector array is ≥3.26eV.

4. The device for detecting radiation dose distribution when rays pass through a human body according to claim 3, characterized in that: The semiconductor material of the semiconductor detector array is ZnO or Ga2O3, and it has dual-mode detection capabilities for X-rays and proton beams. It is used to apply voltage through an energy supply device to convert the strength of the rays it is exposed to into a corresponding output electrical signal.

5. The device for detecting radiation dose distribution when rays pass through a human body according to claim 4, characterized in that: The semiconductor unit in the semiconductor detector array is a metal-semiconductor-metal structure, the metal electrode on the semiconductor surface is a silver electrode or a platinum electrode, and the structural type is a bulk electrode structure or an interdigitated electrode structure.

6. The device for detecting radiation dose distribution when rays pass through a human body according to claim 5, characterized in that: The interdigital spacing of the interdigital electrode structure is 0.001 to 0.5 mm, the interdigital length is 0.01 to 12 mm, the interdigital width is 0.001 to 0.5 mm, and the number of interdigits in each electrode is 5 to 100.

7. A method for detecting radiation dose distribution when a ray passes through a human body, comprising: using a device for detecting radiation dose distribution when a ray passes through a human body according to any one of claims 1 to 6, and performing the following steps: S1. Transport the human tissue density simulation liquid to the set liquid level of the detection chamber through the liquid transport device and let it stand for 1 to 5 minutes; S2. If X-ray detection is required, move the bracket so that the X-ray generator is directly above the detection chamber, with the emission port facing downward. S3. transmitting an X-ray beam through a human tissue density simulating fluid in the detection chamber and into a semiconductor detector array; S4. Each semiconductor in the semiconductor detector array converts the intensity of the X-rays it receives into a corresponding output electrical signal. S5. The data acquisition and analysis module collects the output electrical signals of each semiconductor at the same liquid level. By controlling the liquid level, it obtains the radiation dose distribution when the X-ray enters the human body at different depths and creates a three-dimensional grayscale image for visualization. S6. If proton beam detection is required, move the bracket so that the proton beam generator is directly above the detection chamber, with the emission port facing downward. S7. emitting a proton beam through a human tissue density simulating fluid in the detection chamber and into a semiconductor detector array; S8. Each semiconductor in the semiconductor detector array converts the strength of the proton beam into a corresponding output electrical signal. S9. The data acquisition and analysis module collects the magnitude of the electrical signals output by each semiconductor at the same liquid level. By controlling the liquid level, it obtains the radiation dose distribution when the proton beam enters the human body at different depths and creates a three-dimensional grayscale image for visualization. S10. Adjust the intensity of the output radiation of the proton beam generator and repeat steps S6-S9 to measure the relationship between the depth position distribution of the proton beam Bragg peak and the proton beam intensity.

8. A method for tracking lesions during proton beam tumor therapy, characterized in that The following steps are involved: During tumor treatment, the lesion area is continuously irradiated with X-rays, and a semiconductor detector array and a data acquisition and analysis module placed at corresponding positions are used to collect signals in real time, which are compared with the electrical signals obtained in step S5 of claim 7 to determine the real-time human tissue thickness corresponding to the fault layer where the lesion is located; Calculate in real time the depth of the lesion center from the epidermis during tumor treatment based on the ratio of the distances between the lesion center and the front and back walls of the human tissue as shown in the CT scan and the real-time human tissue thickness; According to the relationship between the depth position distribution of the proton beam Bragg peak and the proton beam intensity obtained in step S10 of claim 7, the intensity of the output radiation of the proton beam generator for tumor treatment is adjusted in real time so that the depth position of the Bragg peak is the same as the depth of the lesion center from the epidermis.

9. A non-transitory readable recording medium for storing one or more programs comprising a plurality of instructions, characterized in that: When the instructions are executed, the processor is caused to execute the method for detecting radiation dose distribution when rays pass through a human body as described in claim 7.

10. A radiation dose distribution detection system when rays pass through the human body, characterized in that It includes a processing circuit and a memory electrically coupled thereto, characterized in that the memory is configured to store at least one program, the program includes multiple instructions, and the processing circuit runs the program to execute the radiation dose distribution detection method when rays pass through the human body as described in claim 7.

Images