PET detector monitoring method, device, storage medium and electronic equipment

Abstract

The present application discloses a PET detector monitoring method, apparatus, storage medium, and electronic device, wherein the method includes: setting an energy collection range of a target energy window based on target radiation emitted by a target component in a target detector, or target radiation emitted by a natural radioactive background; determining target response data based on the target radiation; based on the energy collection range of the target energy window, using each detector unit in a target PET detector to collect energy from the target radiation in real time, obtaining response data corresponding to each detector unit; and monitoring each detector unit based on the target response data and the response data of each detector unit to obtain monitoring results. The monitoring method of the present application does not require an additional radiation source, making monitoring of the PET detector more convenient and faster.

Description

Technical Field

[0001] The present application relates to the technical field of medical devices, and in particular to a monitoring method, device, storage medium and electronic equipment for a PET detector. Background Art

[0002] Positron Emission Tomography (PET) detectors work by detecting the metabolism of radioactive drugs in a patient's body, thereby obtaining important clinical diagnostic information about tissue function, activity, and metabolism. PET devices are typically combined with CT devices to form PET / CT systems, seamlessly integrating functional and anatomical imaging to improve lesion localization accuracy and qualitative diagnostic capabilities.

[0003] The stable operation of each detector unit is essential for accurate diagnostic information. Any abnormalities should be promptly reported and replaced to avoid image artifacts and diagnostic issues. During daily equipment operation, the detector status should be monitored constantly. At a minimum, before each daily scan, the detector should be tested to confirm proper function. This process, often referred to as daily quality control (Daily QC), is a crucial step in verifying the proper functioning of the PET device. Specifically, PET detectors are typically monitored before and during operation to ensure proper functioning.

[0004] However, existing PET detector monitoring methods typically rely on adding an additional radioactive source, placed within the machine's shielded chamber. During quality control, the source automatically extends, and the equipment then performs the test. This process, involving the purchase, use, and storage of the radioactive source, is complex, time-consuming, and labor-intensive, making PET detector monitoring inconvenient and inefficient.

[0005] Therefore, a PET detector monitoring method is urgently needed to solve the problem that the monitoring of PET detectors in the prior art is relatively complicated, inconvenient and not fast enough. Summary of the Invention

[0006] In view of this, the present invention provides a PET detector monitoring method, device, storage medium and electronic equipment, the main purpose of which is to solve the problem that the current PET detector monitoring process is relatively cumbersome, inconvenient and not fast enough.

[0007] To solve the above problems, the present application provides a PET detector monitoring method, comprising:

[0008] Setting the energy collection range of the target energy window based on the target radiation emitted by the target component in the target detector or the target radiation emitted by the natural radioactive background;

[0009] determining target response data based on the target ray;

[0010] Based on the energy collection range of the target energy window, using each detector unit in the target PET detector to collect energy of the target ray in real time to obtain response data corresponding to each detector unit;

[0011] Based on the target response data and the response data of each detector unit, each detector unit is monitored to obtain a monitoring result.

[0012] Optionally, the target component in the target detector component is a component that can emit target rays in a predetermined energy range.

[0013] Optionally, the target component in the target detector component includes any one of the following:

[0014] A photoconductive device containing a target radioactive substance, a detector housing containing a target radioactive substance, or a device containing a coating layer containing a target radioactive substance; the target radioactive substance is a naturally occurring radioactive substance or an artificial radioactive substance obtained from industrial applications, including any one or more of the following: potassium-40, carbon-14, cesium-137, zinc-65, barium-131, sodium-22, germanium-68, gallium-68, cobalt-60, cobalt-57, iron-55, selenium-75, iodine-131, tin-113, indium-113, thulium-170, iridium-192, uranium-238, thorium-232, plutonium-238, and americium-241;

[0015] The sources of the natural radioactive background include any one or more of the following: marble floors, walls, natural radioactive substances in ambient air, and cosmic rays.

[0016] Optionally, the method further includes: determining the target ray based on the operating state of the detector, specifically including:

[0017] Crystals containing potassium-40 were identified as target components;

[0018] When the detector is in a non-clinical scanning state, determining the beta ray or gamma ray emitted by the potassium-40 as the target ray;

[0019] When the detector is in a clinical scanning state, the gamma rays emitted by the potassium-40 are determined to be target rays.

[0020] Optionally, the monitoring of each detector unit based on the target response data and the response data of each detector unit to obtain a monitoring result specifically includes:

[0021] Determining a particle response count distribution in the response data of each detector unit based on a preset interval in the target response data;

[0022] When it is determined that the particle response count distribution in the response data exceeds the preset interval, monitoring and obtaining that the detector unit corresponding to the response data is in an abnormal state;

[0023] When it is determined that the particle response count distribution in the response data does not exceed the preset interval, the detector unit corresponding to the response data is monitored to be in a normal state.

[0024] Optionally, when the monitoring result is abnormal, the method further includes: outputting an alarm signal in a predetermined manner to provide an abnormality prompt.

[0025] To solve the above problems, the present application provides a monitoring device for a PET detector, comprising:

[0026] A setting module, configured to set an energy collection range of a target energy window based on target rays emitted by a target component in a target detector or target rays emitted by a natural radioactive background;

[0027] A first determining module, configured to determine target response data based on the target ray;

[0028] an acquisition module, configured to acquire energy of the target ray in real time using each detector unit in the target PET detector based on the energy acquisition range of the target energy window, and acquire response data corresponding to each detector unit;

[0029] The monitoring module is used to monitor each of the detector units based on the target response data and the response data of each of the detector units to obtain a monitoring result.

[0030] Optionally, the monitoring device for the PET detector further includes a second determination module for determining the target ray based on an operating state of the detector, wherein the second determination module is specifically configured to:

[0031] Crystals containing potassium-40 were identified as target components;

[0032] When the detector is in a non-clinical scanning state, determining the beta ray or gamma ray emitted by the potassium-40 as the target ray;

[0033] When the detector is in a clinical scanning state, the gamma rays emitted by the potassium-40 are determined to be target rays.

[0034] Optionally, the monitoring module is specifically used to:

[0035] Determining a particle response count distribution in the response data of each detector unit based on a preset interval in the target response data;

[0036] When it is determined that the particle response count distribution in the response data exceeds the preset interval, monitoring and obtaining that the detector unit corresponding to the response data is in an abnormal state;

[0037] When it is determined that the particle response count distribution in the response data does not exceed the preset interval, the detector unit corresponding to the response data is monitored to be in a normal state.

[0038] To solve the above problems, the present application provides a storage medium, wherein the storage medium stores a computer program, and when the computer program is executed by a processor, the steps of any of the above-mentioned PET detector monitoring methods are implemented.

[0039] To solve the above problems, the present application provides an electronic device, which includes at least a memory and a processor, wherein a computer program is stored on the memory, and when the processor executes the computer program on the memory, it implements the steps of any of the above-mentioned PET detector monitoring methods.

[0040] In the present application, the target rays are emitted by components based on the natural background radioactivity in the PET detector, or the target rays are emitted by the natural radioactive background outside the PET detector. By utilizing the various detection units in the target PET detector, the target rays can be detected, thereby eliminating the need for additional radiation sources, making monitoring of the PET detector more convenient and quick.

[0041] The above description is only an overview of the technical solution of the present invention. In order to more clearly understand the technical means of the present invention, it can be implemented in accordance with the contents of the specification. In order to make the above and other purposes, features and advantages of the present invention more obvious and easy to understand, the specific implementation methods of the present invention are specifically listed below. BRIEF DESCRIPTION OF THE DRAWINGS

[0042] Various other advantages and benefits will become apparent to those skilled in the art upon reading the detailed description of the preferred embodiment below. The accompanying drawings are for illustration purposes only and are not to be considered as limiting the present invention. The same reference symbols are used throughout the drawings to represent the same components. In the drawings:

[0043] Figure 1This is a flow chart of a monitoring method for a PET detector according to an embodiment of the present application;

[0044] Figure 2 This is a flow chart of a PET detector monitoring method according to another embodiment of the present application;

[0045] Figure 3 This is the K-40 background response energy spectrum received by the PET detector in the embodiment of the present application;

[0046] Figure 4 This is a flow chart of a PET detector monitoring method according to another embodiment of the present application;

[0047] Figure 5 This is the response energy spectrum of the PET detector in the embodiment of the present application when simultaneously receiving 511keV gamma rays of clinical scanning and K-40 background gamma rays;

[0048] Figure 6 Schematic diagram of the mixed energy spectrum of 511kev and K-40γ background in the normal module clinical scanning mode;

[0049] Figure 7 The figure shows the mixed energy spectrum of 511kev and K-40γ background in the abnormal module clinical scanning mode;

[0050] Figure 8 This is a schematic structural diagram of a PET detector in another embodiment of the present application;

[0051] Figure 9 This is a schematic structural diagram of a detector unit in another embodiment of the present application;

[0052] Figure 10 This is a structural block diagram of a monitoring device for a PET detector according to another embodiment of the present application. DETAILED DESCRIPTION

[0053] Various aspects and features of the present application are described herein with reference to the accompanying drawings.

[0054] It should be understood that various modifications may be made to the embodiments of the present application. Therefore, the above description should not be considered as limiting, but merely as an example of an embodiment. Other modifications within the scope and spirit of the present application will occur to those skilled in the art.

[0055] The accompanying drawings, which are incorporated in and constitute a part of the specification, illustrate embodiments of the present application and, together with the general description of the present application given above and the detailed description of the embodiments given below, serve to explain the principles of the present application.

[0056] These and other characteristics of the present application will become apparent from the following description of a preferred form of embodiment given as a non-limiting example with reference to the accompanying drawings.

[0057] It should also be understood that although the present application has been described with reference to certain specific examples, those skilled in the art will readily be able to implement many other equivalent forms of the present application.

[0058] The above and other aspects, features and advantages of the present application will become more apparent from the following detailed description when taken in conjunction with the accompanying drawings.

[0059] Specific embodiments of the present application will be described hereinafter with reference to the accompanying drawings; however, it should be understood that the embodiments described are merely examples of the present application and may be implemented in a variety of ways. Familiar and / or repetitive functions and structures are not described in detail to avoid obscuring the present application with unnecessary or redundant details. Therefore, the specific structural and functional details described herein are not intended to be limiting, but rather serve merely as a basis and representative basis for the claims to teach those skilled in the art to variously utilize the present application with substantially any suitable detailed structure.

[0060] This specification may use the phrases "in one embodiment," "in another embodiment," "in yet another embodiment," or "in other embodiments," which may all refer to one or more of the same or different embodiments according to the present application.

[0061] The present application embodiment provides a monitoring method for a PET detector, such as Figure 1 As shown, the following steps are included:

[0062] Step S101, setting an energy collection range of a target energy window based on target rays emitted by a target component in a target detector or target rays emitted by a natural radioactive background;

[0063] The target component in the target detector component in this step is a component that can emit target rays within a predetermined energy range; the predetermined energy range is 20kev to 2000kev. Specifically, the target component in the target detector component includes any one of the following: an optical device containing a target radioactive material, a detector housing containing a target radioactive material, or a device containing a coating layer of a target radioactive material; the target radioactive material is a naturally occurring radioactive material, or an artificial radioactive material that is relatively easy to obtain in industrial applications, including but not limited to any one or more of the following: potassium-40, carbon-14, cesium-137, zinc-65, barium-131, sodium-22, germanium-68, gallium-68, cobalt-60, cobalt-57, iron-55, selenium-75, iodine-131, tin-113, indium-113, thulium-170, iridium-192, uranium-238, thorium-232, plutonium-238, and americium-241;

[0064] The sources of the natural radioactive background include but are not limited to any one or more of the following: marble floors, walls, natural radioactive substances in ambient air, and cosmic rays.

[0065] For example, a predetermined dose of cobalt-60 is evenly applied to a thin film to create a thin film source, which is then attached to the detector surface as a calibration radioactive source input. Cobalt-60 has a half-life of 5.27 years and emits two gamma rays, 1173keV and 1332keV. The detector can identify these two rays as signatures for quality control monitoring.

[0066] In this step, different rays correspond to different energy collection ranges. Therefore, after determining the target ray, the energy window can be set according to the energy collection range of the target ray.

[0067] Step S102, determining target response data based on the target ray;

[0068] During the specific implementation of this step, a mapping relationship between various radiations and standard response data can be pre-established. Thus, after the target radiation is determined, the mapping relationship can be searched based on the target radiation to obtain the corresponding standard response data, i.e., the target response data. The target response data includes preset particle count distribution data.

[0069] Step S103, based on the energy collection range of the target energy window, using each detector unit in the target PET detector to collect energy of the target ray in real time, and obtaining response data corresponding to each detector unit;

[0070] During the specific implementation of this step, after adjusting the energy window to an appropriate size, interference information such as electronic noise can be effectively filtered out, and the particle response in the target component can be fully acquired, laying the foundation for subsequent accurate monitoring of the detector unit based on the response data.

[0071] Step S104: monitoring each detector unit based on the target response data and the response data of each detector unit to obtain a monitoring result.

[0072] During the specific implementation of this step, when monitoring the detector unit to determine whether it is abnormal, the specific process is: judging the particle response count distribution in the response data of each detector unit based on the preset interval in the target response data; when it is judged that the particle response count distribution in the response data exceeds the preset interval, monitoring and obtaining that the detector unit corresponding to the response data is in an abnormal state; when it is judged that the particle response count distribution in the response data does not exceed the preset interval, monitoring and obtaining that the detector unit corresponding to the response data is in a normal state.

[0073] In this embodiment, the target rays are emitted by components based on the natural background radioactivity in the PET detector, or by the natural radioactive background outside the PET detector, and the target rays are detected by utilizing the detection units in the target PET detector. This eliminates the need for additional radiation sources, making monitoring of the PET detector more convenient and quick.

[0074] Building on the above examples, this embodiment uses potassium-40 (K-40) as an example, as the target radioactive substance in a PET detector structure. Because the PET detector structure includes components composed of crown glass (optical glass), which contains K-40, it can be detected as a target radioactive substance to obtain response data corresponding to each detector unit. In specific implementations, the following two methods can be used to perform PET detector quality control, whether in clinical scanning mode or non-clinical scanning mode.

[0075] Method 1: If Figure 2As shown, when the detector is in a non-clinical scanning state, (1) first determine that the β-ray emitted by the K-40 is the target ray, and then adjust the energy window to an appropriate size so that interference information such as electronic noise can be effectively filtered out, and most of the β-particle responses in the K-40 background radiation (with a relatively high count rate and easy to detect) can be fully acquired. (2) The data is accurately identified according to a pre-set encoding method, and the β-particle response data is uploaded to the host computer in a single event manner. (3) Based on the preset interval in the target response data, the particle response count distribution in the response data of each detector unit is judged; if the particle response count distribution in the response data exceeds the preset interval, the detector unit corresponding to the response data is monitored to be in an abnormal state; if the particle response count distribution in the response data does not exceed the preset interval, the detector unit corresponding to the response data is monitored to be in a normal state. That is, the β-particle response count distribution at each crystal position is counted and compared with the preset count distribution table to determine whether the acquired information is within the reasonable expected range. If it exceeds the range, it is determined that an abnormality has occurred in the detector area. This can send an alarm signal to achieve quality monitoring or risk warning effects, such as Figure 3 The figure shows the K-40 background response spectrum received by the PET detector. In this embodiment, when sending an alarm signal, a text or picture prompt message can be sent to a predetermined terminal device, or an alarm sound can be output to provide a warning or abnormality report.

[0076] Method 2: If Figure 4As shown, when the detector is in the clinical scanning state, (1) first determine that the gamma ray emitted by the K-40 is the target ray; then execute the clinical scanning protocol, the system opens the dual energy window, and sets the size of the first energy window based on the 511kev gamma radiation in the subject's body, for example, the range of the first energy window can be selected from 450kev to 600kev; and sets the size of the second energy window based on the gamma ray emitted by the K-40, for example, the range of the second energy window can be selected from 1350kev to 1550kev. Thus, the data outside the energy window will be filtered out, and the data within the energy window will be retained and uploaded to the host computer for image processing and monitoring. (2) The first energy window is used to receive the 511kev gamma radiation response from the body (subject). The second energy window is used to receive the γ energy response of the K40 background of 1460kev (the energy window can usually be selected between 1350kev and 1550kev, but the electronic system usually does not support such a wide dynamic range. When obtaining the 1460kev response, the signal may be saturated and compressed, and the energy window will move to the corresponding position to the left accordingly). (3) The data of the first energy window is uploaded to the host computer in a compliant manner for clinical image reconstruction. (4) The data of the second energy window accurately identifies the crystal position of the γ particle incident according to a pre-set encoding method and is uploaded to the host computer in a single event manner. (5) Based on the preset interval in the target response data, the particle response count distribution in the response data of each detector unit is judged; when it is judged that the particle response count distribution in the response data exceeds the preset interval, the detector unit corresponding to the response data is monitored to be in an abnormal state; when it is judged that the particle response count distribution in the response data does not exceed the preset interval, the detector unit corresponding to the response data is monitored to be in a normal state. That is, the distribution of the gamma particle response counting rate at each crystal position in the second energy window is statistically analyzed and compared with the preset counting rate distribution table to determine whether the information obtained is within the reasonable expected range. If the change exceeds the expected limit, the detector is judged to be abnormal, the abnormal position information can be fed back, and an alarm signal can be issued to achieve the effect of quality monitoring or risk warning. This can remind the operator that the detector state is abnormal and the currently acquired image may have certain risks, which can be used for reference or decision-making by the operator. Figure 5 The figure shows the response energy spectrum of the PET detector when it receives 511kev gamma rays from clinical scans and K-40 background gamma rays at the same time. Figure 6 The figure shows the mixed energy spectrum of 511kev and K-40 gamma background in the normal module clinical scanning mode; Figure 7The figure shows a mixed energy spectrum diagram of 511kev and K-40 gamma background in the clinical scanning mode of the abnormal module. In this embodiment, when sending an alarm signal, a text or picture prompt message can be sent to a predetermined terminal device, or an alarm sound can be output to provide a warning or abnormality report. In this step, when making an abnormality judgment, the peak position of the gamma particle energy spectrum at each crystal position in the second energy window can also be counted, and then compared with a preset peak position distribution table to determine whether the acquired information is within a reasonable expected range. If the change exceeds the expected limit, the abnormal position information is fed back and a warning prompt is issued to remind the operator that the detector status is abnormal and that the currently acquired image may have certain risks, which is provided for the operator's reference or decision-making.

[0077] The PET detector system and analysis method described in this embodiment utilizes the detector's own K-40 background as an input source for routine quality control and real-time monitoring, and are therefore widely applicable to PET detector equipment. In particular, they enable status monitoring of detectors assembled from crystals containing no natural radioactive background, such as BGO, GAGG, and NaI. K-40 has a high and stable beta count rate, making it suitable as a standard input source for routine quality control. Furthermore, the K-40 gamma background generates a high-resolution energy spectrum under single-event conditions. The gamma peak position not only does not overlap with the beta background energy spectrum, but also significantly differs from the peak position of 511 keV gamma rays emitted in the body during clinical scans. This does not affect K40 energy acquisition during clinical scans, allowing monitoring of the PET detector even during clinical scans, thus enabling real-time monitoring of the PET detector. This overcomes the current problem of using lutetium-176 in LYSO / LSO crystals as a natural radioactive background, which can only be used for quality control of the PET detector before clinical scans, rather than for real-time quality control during clinical scans. Furthermore, for detector systems constructed from crystals without natural background radiation, such as BGO, GAGG, and NaI, quality control based on Lu-176 is impossible. Furthermore, the problem of using the Lu-176 background's gamma-ray peak as a detection basis, requiring compliance measurement, is addressed. The amount of compliance data is low relative to the single-event count rate, resulting in low execution efficiency. When using single-event acquisition, the majority of data acquired is beta particle responses, and the gamma spectrum is submerged in the beta spectrum, affecting the interpretation of the results and making quality control of PET detectors less accurate.

[0078] In this embodiment, the PET detector includes a plurality of detector units, each of which is evenly arranged in a ring to form a Figure 8 The detector ring shown in FIG. The structure of each detector unit can be as follows Figure 9As shown, it includes: a BGO (short for bismuth germanium oxide) scintillation crystal array, a light guide, a SiPM silicon semiconductor photoelectric conversion array, and an electronic system. The optical components are bonded together using optical glue. The monitoring principle in this embodiment is: the protective glass on the surface of the light guide or SiPM spontaneously emits K-40 natural radioactive beta and gamma rays, the scintillation crystal array receives the rays, and emits light signals through atomic excitation and de-excitation. The light signal is arranged in a crystal array and designed in a light guide structure to form a certain light distribution. The SiPM obtains the light information and converts it into electrical information and transmits it to the back-end electronic processing system. Through the action of the PET detector, it is finally converted into the energy, position, count rate and other information of the K-40 background radiation. Therefore, the counting rate and other information can be used to monitor whether each detector unit is normal.

[0079] Another embodiment of the present application provides a monitoring device for a PET detector, such as Figure 10 As shown, including:

[0080] Setting module 1, for setting the energy collection range of the target energy window based on the target rays emitted by the target component in the target detector or the target rays emitted by the natural radioactive background;

[0081] A first determining module 2, configured to determine target response data based on the target ray;

[0082] An acquisition module 3 is configured to acquire energy of the target rays in real time using each detector unit in the target PET detector based on the energy acquisition range of the target energy window, and acquire response data corresponding to each detector unit;

[0083] The monitoring module 4 is configured to monitor each of the detector units based on the target response data and the response data of each of the detector units to obtain a monitoring result.

[0084] In this embodiment, the target component in the target detector component is a component that can emit target rays within a predetermined energy range; the predetermined energy range is 20kev to 2000kev. Specifically, the target component in the target detector component includes any one of the following: a photoconductive device containing a target radioactive substance, a detector housing containing a target radioactive substance, or a device containing a coating layer containing a target radioactive substance; the target radioactive substance is a naturally occurring radioactive substance or an artificial radioactive substance that is relatively easy to obtain in industrial applications, including but not limited to any one or more of the following: potassium-40, carbon-14, cesium-137, zinc-65, barium-131, sodium-22, germanium-68, gallium-68, cobalt-60, cobalt-57, iron-55, selenium-75, iodine-131, tin-113, indium-113, thulium-170, iridium-192, uranium-238, thorium-232, plutonium-238, and americium-241;

[0085] The sources of the natural radioactive background include but are not limited to any one or more of the following: marble floors, walls, natural radioactive substances in ambient air, and cosmic rays.

[0086] In the specific implementation process of this embodiment, the monitoring device of the PET detector also includes a second determination module for determining the target ray based on the operating state of the detector. The second determination module is specifically used to: determine that the crystal containing potassium-40 is the target component; when the detector is in a non-clinical scanning state, determine that the beta ray or gamma ray emitted by the potassium-40 is the target ray; when the detector is in a clinical scanning state, determine that the gamma ray emitted by the potassium-40 is the target ray.

[0087] In this embodiment, the monitoring module is specifically used to: judge the particle response count distribution in the response data of each detector unit based on the preset interval in the target response data; when it is judged that the particle response count distribution in the response data exceeds the preset interval, the detector unit corresponding to the response data is monitored to be in an abnormal state; when it is judged that the particle response count distribution in the response data does not exceed the preset interval, the detector unit corresponding to the response data is monitored to be in a normal state.

[0088] In this embodiment, the monitoring device of the PET detector further includes a prompt module, which is configured to output an alarm signal in a predetermined manner to provide an abnormality prompt when the monitoring result is abnormal.

[0089] In the present application, the target rays are emitted by components based on the natural background radioactivity in the PET detector, or the target rays are emitted by the natural radioactive background outside the PET detector. By utilizing the various detection units in the target PET detector, the target rays can be detected, thereby eliminating the need for additional radiation sources, making monitoring of the PET detector more convenient and quick.

[0090] Another embodiment of the present application provides a storage medium storing a computer program. When the computer program is executed by a processor, the following method steps are implemented:

[0091] Step 1: setting the energy collection range of the target energy window based on the target rays emitted by the target component in the target detector or the target rays emitted by the natural radioactive background;

[0092] Step 2: determining target response data based on the target ray;

[0093] Step 3: Based on the energy collection range of the target energy window, each detector unit in the target PET detector is used to collect energy of the target ray in real time to obtain response data corresponding to each detector unit;

[0094] Step 4: Based on the target response data and the response data of each detector unit, monitor each detector unit to obtain a monitoring result.

[0095] The specific implementation process of the above method steps can be found in the above embodiments of the monitoring method of any PET detector, and will not be repeated in this embodiment.

[0096] In the present application, the target rays are emitted by components based on the natural background radioactivity in the PET detector, or the target rays are emitted by the natural radioactive background outside the PET detector. By utilizing the various detection units in the target PET detector, the target rays can be detected, thereby eliminating the need for additional radiation sources, making monitoring of the PET detector more convenient and quick.

[0097] Another embodiment of the present application provides an electronic device, comprising at least a memory and a processor, wherein the memory stores a computer program, and the processor implements the following method steps when executing the computer program in the memory:

[0098] Step 1: setting the energy collection range of the target energy window based on the target rays emitted by the target component in the target detector or the target rays emitted by the natural radioactive background;

[0099] Step 2: determining target response data based on the target ray;

[0100] Step 3: Based on the energy collection range of the target energy window, each detector unit in the target PET detector is used to collect energy of the target ray in real time to obtain response data corresponding to each detector unit;

[0101] Step 4: Based on the target response data and the response data of each detector unit, monitor each detector unit to obtain a monitoring result.

[0102] The specific implementation process of the above method steps can be found in the above embodiments of the monitoring method of any PET detector, and will not be repeated in this embodiment.

[0103] In the present application, the target rays are emitted by components based on the natural background radioactivity in the PET detector, or the target rays are emitted by the natural radioactive background outside the PET detector. By utilizing the various detection units in the target PET detector, the target rays can be detected, thereby eliminating the need for additional radiation sources, making monitoring of the PET detector more convenient and quick.

[0104] The above embodiments are merely exemplary embodiments of the present application and are not intended to limit the scope of the present application. The scope of protection of the present application is defined by the claims. Those skilled in the art may make various modifications or equivalent substitutions to the present application within the essence and scope of protection of the present application, and such modifications or equivalent substitutions shall also be deemed to fall within the scope of protection of the present application.

Claims

1. A PET detector monitoring method, characterized in that: The method comprises: Setting the energy collection range of the target energy window based on the target radiation emitted by the target component in the target detector or the target radiation emitted by the natural radioactive background; determining target response data based on the target ray; Based on the energy collection range of the target energy window, using each detector unit in the target PET detector to collect energy of the target ray in real time to obtain response data corresponding to each detector unit; Based on the target response data and the response data of each detector unit, monitoring each detector unit to obtain a monitoring result; The step of monitoring each detector unit based on the target response data and the response data of each detector unit to obtain a monitoring result specifically includes: Determining a particle response count distribution in the response data of each detector unit based on a preset interval in the target response data; When it is determined that the particle response count distribution in the response data exceeds the preset interval, monitoring and obtaining that the detector unit corresponding to the response data is in an abnormal state; When it is determined that the particle response count distribution in the response data does not exceed the preset interval, the detector unit corresponding to the response data is monitored to be in a normal state.

2. The method according to claim 1, wherein The target component in the target detector component is a component that can emit target rays in a predetermined energy range.

3. The method according to claim 2, wherein The target component in the target detector component includes any one of the following: A photoconductive device containing a target radioactive substance, a detector housing containing a target radioactive substance, or a device containing a coating layer containing a target radioactive substance; the target radioactive substance is a naturally occurring radioactive substance or an artificial radioactive substance obtained from industrial applications, including any one or more of the following: potassium-40, carbon-14, cesium-137, zinc-65, barium-131, sodium-22, germanium-68, gallium-68, cobalt-60, cobalt-57, iron-55, selenium-75, iodine-131, tin-113, indium-113, thulium-170, iridium-192, uranium-238, thorium-232, plutonium-238, and americium-241; The sources of the natural radioactive background include any one or more of the following: marble floors, walls, natural radioactive substances in ambient air, and cosmic rays.

4. The method according to claim 3, wherein The method further includes: determining the target ray based on the operating state of the detector, specifically including: Crystals containing potassium-40 were identified as target components; When the detector is in a non-clinical scanning state, determining that the beta ray or gamma ray emitted by the potassium-40 is the target ray; When the detector is in a clinical scanning state, the gamma rays emitted by the potassium-40 are determined to be target rays.

5. The method according to claim 1, wherein In the case where the monitoring result is abnormal, the method further includes: outputting an alarm signal in a predetermined manner to provide an abnormality prompt.

6. A monitoring device for a PET detector, characterized in that: include: A setting module, configured to set an energy collection range of a target energy window based on target rays emitted by a target component in a target detector or target rays emitted by a natural radioactive background; A first determining module, configured to determine target response data based on the target ray; an acquisition module, configured to acquire energy of the target ray in real time using each detector unit in the target PET detector based on the energy acquisition range of the target energy window, and acquire response data corresponding to each detector unit; A monitoring module, configured to monitor each of the detector units based on the target response data and the response data of each of the detector units to obtain a monitoring result; The monitoring module is specifically configured to: determine the particle response count distribution in the response data of each detector unit based on a preset interval in the target response data; When it is determined that the particle response count distribution in the response data exceeds the preset interval, monitoring and obtaining that the detector unit corresponding to the response data is in an abnormal state; When it is determined that the particle response count distribution in the response data does not exceed the preset interval, the detector unit corresponding to the response data is monitored to be in a normal state.

7. The device according to claim 6, characterized in that The system further includes a second determining module for determining the target ray based on the operating state of the detector, wherein the second determining module is specifically configured to: Crystals containing potassium-40 were identified as target components; When the detector is in a non-clinical scanning state, determining that the beta ray or gamma ray emitted by the potassium-40 is the target ray; When the detector is in a clinical scanning state, the gamma rays emitted by the potassium-40 are determined to be target rays.

8. A storage medium, characterized in that: The storage medium stores a computer program, and when the computer program is executed by a processor, the steps of the PET detector monitoring method according to any one of claims 1 to 5 are implemented.

9. An electronic device, characterized in that: The system comprises at least a memory and a processor, wherein the memory stores a computer program, and the processor implements the steps of the PET detector monitoring method according to any one of claims 1 to 5 when executing the computer program on the memory.

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