Method and device for correcting SPECT image, electronic equipment and storage medium

Abstract

The application belongs to the technical field of medical imaging, and provides a single photon emission computed tomography image correction method and device, electronic equipment and storage medium, wherein the method comprises: acquiring multi-energy window scanning data obtained through single photon emission computed tomography, wherein the multi-energy window scanning data comprises main energy window scanning data and at least one scattering window scanning data; reconstructing a main energy window image using the main energy window scanning data, and reconstructing a scattering window image using the scattering window scanning data; calculating an attenuation coefficient image using the main energy window image and the scattering window image; and correcting the main energy window image using the attenuation coefficient image to obtain a single photon emission computed tomography image.

Description

Technical Field

[0001] This application belongs to the field of medical imaging, and in particular relates to a method and apparatus for attenuation correction of single-photon emission computed tomography images, an electronic device, and a computer-readable storage medium. Background Technology

[0002] Single-photon emission computed tomography (SPECT) is a type of nuclear medicine imaging. It involves administering a radioactive tracer orally or intravenously to the subject. Once inside the body, the tracer participates in the circulation and metabolism of specific organs and tissues, continuously emitting radiation. The radiation is then detected non-invasively using specialized instruments to create an image. The resulting image is a functional image, showing the morphology and function of the subject's internal organs. The radioactive tracer used in SPECT emits single-photon rays, specifically gamma rays, which play a crucial role in the early diagnosis, staging, or stratification of diseases in clinical oncology, nervous system diseases, and cardiovascular diseases, as well as in the evaluation of treatment efficacy.

[0003] The greatest advantage of SPECT is its ability to accurately and quantitatively reflect the distribution of radioactive tracers in human tissues. To meet the accuracy requirements of SPECT imaging, various influencing factors need to be corrected, one important of which is attenuation correction. Attenuation correction is used to correct for the attenuation caused by the absorption of gamma rays through interaction with atoms in human tissue cells.

[0004] In related technologies, the attenuation coefficients in X-ray computed tomography (CT) images are mainly converted and used as attenuated images for SPECT attenuation correction, leading to the development of integrated SPECT / CT devices. However, with the widespread use of SPECT / CT, many problems unfavorable to clinical applications have been discovered. Specifically, because CT scanning speed is much faster than SPECT (CT image scanning speed is measured in seconds, while SPECT scanning speed is measured in minutes), physiological movements such as respiration, heartbeat, and intestinal peristalsis cause significant mismatches between CT and SPECT images during registration, such as the "banana artifact" above the diaphragm and significant sparseness of the left ventricular myocardium at the apex in myocardial perfusion imaging. CT scans also expose patients to additional radiation, and patients undergoing efficacy evaluation often cannot have CT scans for every scan. Furthermore, the CT component increases the overall cost of the SPECT machine. Summary of the Invention

[0005] This application provides an attenuation correction method and apparatus, electronic device and computer-readable storage medium for single-photon emission computed tomography (SPECT) images, which can solve the problem that attenuation correction of SPECT using CT is not conducive to clinical application in related technologies.

[0006] In a first aspect, embodiments of this application provide a method for correcting single-photon emission computed tomography (SPECT) images. The method includes: acquiring multi-window scanning data obtained by SPECT, the multi-window scanning data including main window scanning data and at least one scattering window scanning data; reconstructing a main window image using the main window scanning data and reconstructing a scattering window image using the scattering window scanning data; calculating an attenuation coefficient image using the main window image and the scattering window image; and correcting the main window image using the attenuation coefficient image to obtain a single-photon emission computed tomography (SPECT) image.

[0007] Secondly, embodiments of this application provide a correction apparatus for single-photon emission computed tomography (SPECT) images. The apparatus includes: an acquisition module for acquiring multi-window scanning data obtained through SPECT, the multi-window scanning data including main energy window scanning data and at least one scattering window scanning data; a reconstruction module for reconstructing a main energy window image using the main energy window scanning data and reconstructing a scattering window image using the scattering window scanning data; a calculation module for calculating an attenuation coefficient image using the main energy window image and the scattering window image; and a correction module for correcting the main energy window image using the attenuation coefficient image to obtain a single-photon emission computed tomography (SPECT) image.

[0008] Thirdly, embodiments of this application provide an electronic device, including a memory, a processor, and a computer program stored in the memory and executable by the processor. When the processor executes the computer program, it implements the single-photon emission computed tomography image correction method described in the first aspect above.

[0009] Fourthly, embodiments of this application provide a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the single-photon emission computed tomography image correction method described in the first aspect.

[0010] Fifthly, embodiments of this application provide a computer program product that, when run on an electronic device, causes the electronic device to execute the single-photon emission computed tomography image correction method described in the first aspect.

[0011] The beneficial effects of this application embodiment compared with the prior art are as follows: By acquiring multi-window scanning data obtained through single-photon emission computed tomography (SPECT), the multi-window scanning data includes main window scanning data and at least one scattering window scanning data; a main window image is reconstructed using the main window scanning data, and a scattering window image is reconstructed using the scattering window scanning data; an attenuation coefficient image is calculated using the main window image and the scattering window image; attenuation correction is performed on the main window image using the attenuation coefficient image to obtain a single-photon emission computed tomography (SPECT) image. The attenuation coefficient image required for attenuation correction can be obtained using the multi-window scanning data obtained from single-photon emission computed tomography (SPECT), eliminating the need for CT imaging, reducing the additional cost to the SPECT equipment, eliminating the need to register the CT imaging results with the SPECT imaging results, saving the radioactive radiation caused by CT imaging to the examined object, reducing the cost and radiation impact of SPECT, and improving the accuracy of imaging. Attached Figure Description

[0012] To more clearly illustrate the technical solutions in the embodiments of this application, 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 this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0013] Figure 1 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application;

[0014] Figure 2 This is a schematic flowchart of a method for correcting single-photon emission computed tomography images provided in an embodiment of this application;

[0015] Figure 3 This is a schematic diagram of the main energy window and scattering window settings of 99mTc in a specific example of this application;

[0016] Figure 4 yes Figure 2 A specific process diagram of S3 in China;

[0017] Figure 5 This is a schematic flowchart of a method for correcting single-photon emission computed tomography images provided in a specific embodiment of this application;

[0018] Figure 6 This is the original SPECT image in a specific example of this application;

[0019] Figure 7 Is adopted Figure 5 The method shown is for Figure 6 The result of attenuation correction;

[0020] Figure 8 Based on CT Figure 6 The result of attenuation correction;

[0021] Figure 9 yes Figure 7 and Figure 8 The difference image;

[0022] Figure 10 This is the original SPECT image in another specific example of this application;

[0023] Figure 11 Is adopted Figure 5 The method shown is for Figure 10 The result of attenuation correction;

[0024] Figure 12 Based on CT Figure 10 The result of attenuation correction;

[0025] Figure 13 yes Figure 11 and Figure 12 The difference image;

[0026] Figure 14 This is a schematic diagram of the attenuation correction device for single-photon emission computed tomography images provided in an embodiment of this application. Detailed Implementation

[0027] In the following description, specific details such as particular system architectures and techniques are set forth for illustrative purposes and not for limitation, in order to provide a thorough understanding of the embodiments of this application. However, those skilled in the art will understand that this application may also be implemented in other embodiments without these specific details. In other instances, detailed descriptions of well-known systems, apparatuses, circuits, and methods have been omitted so as not to obscure the description of this application with unnecessary detail.

[0028] It should be understood that, when used in this application specification and the appended claims, the term "comprising" indicates the presence of the described features, integrals, steps, operations, elements and / or components, but does not exclude the presence or addition of one or more other features, integrals, steps, operations, elements, components and / or a collection thereof.

[0029] It should also be understood that the term “and / or” as used in this application specification and the appended claims means any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0030] As used in this application specification and the appended claims, the term "if" may be interpreted, depending on the context, as "when," "once," "in response to determination," or "in response to detection." Similarly, the phrase "if determined" or "if detected [the described condition or event]" may be interpreted, depending on the context, as meaning "once determined," "in response to determination," "once detected [the described condition or event]," or "in response to detection [the described condition or event]."

[0031] Furthermore, in the description of this application and the appended claims, the terms "first," "second," "third," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0032] References to "one embodiment" or "some embodiments" as described in this specification mean that one or more embodiments of this application include a specific feature, structure, or characteristic described in connection with that embodiment. Therefore, the phrases "in one embodiment," "in some embodiments," "in other embodiments," "in still other embodiments," etc., appearing in different parts of this specification do not necessarily refer to the same embodiment, but rather mean "one or more, but not all, embodiments," unless otherwise specifically emphasized. The terms "comprising," "including," "having," and variations thereof mean "including but not limited to," unless otherwise specifically emphasized.

[0033] The single-photon emission computed tomography (SECT) image correction method provided in this application can be applied to electronic devices, including but not limited to servers, server clusters, mobile phones, tablets, laptops, desktop computers, personal digital assistants, and wearable devices, which are electronic devices with computing functions. This application does not impose any restrictions on the specific type of electronic device.

[0034] Figure 1 The diagram shown is a block diagram of a portion of the structure of the electronic device provided in the embodiments of this application. (Reference) Figure 1 The electronic device includes a processor 10, a memory 20, a bus 30, an input device 40, an output device 50, and a communication device 60. The processor 10 and the memory 20 are interconnected via the bus 30, and the input device 40, output device 50, and communication device 60 are also connected to the bus 30. Those skilled in the art will understand that... Figure 1 The structure of the electronic device shown does not constitute a limitation on the electronic device and may include more or fewer components than shown, or combine certain components, or have different component arrangements.

[0035] The following is combined Figure 1 A detailed introduction to each component of the electronic device:

[0036] Processor 10 is the control center of the electronic device, capable of running programs stored in memory 20 to perform various functions and process data. Processor 10 can be a Central Processing Unit (CPU), but it can also be other general-purpose processors, digital signal processors (DSPs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor can be a microprocessor or any conventional processor. In some embodiments, processor 10 may include an AI (Artificial Intelligence) processor for handling computational operations related to machine learning.

[0037] Memory 20 is used to store the operating system, applications, bootloader, data, and other programs, such as program code for computer programs. Memory 20 can also be used to temporarily store data required and generated by the executing program. Memory 20 may include high-speed random access memory and non-volatile memory, such as flash memory, hard disk, multimedia card, card-type memory, etc. Memory 20 may include storage units located inside the electronic device, such as the hard disk of the electronic device, and / or removable external storage units, such as portable hard drives, USB flash drives, smart media cards (SMC), secure digital cards (SD cards), etc.

[0038] The input device 40 may include at least one of a keyboard, mouse, touch panel, joystick, etc., for collecting user input operations to generate corresponding operation instructions.

[0039] Output device 50 is used to output information to be provided to the user. Output device 50 generally includes a display, and optionally, may be a liquid crystal display (LCD), an organic light-emitting diode (OLED), or the like. In addition, the output device may further include a speaker.

[0040] The communication device 60 may include a modem, network card, etc., for establishing network connections with other electronic devices and communicating with each other. For example, the communication device 60 may be directly or indirectly connected to a single photon emission computed tomography (SPECT) device to acquire scan data from the SPECT device.

[0041] The method for correcting single-photon emission computed tomography (SPECT) images provided in this application can be implemented as a computer software program. For example, an embodiment of this application provides a computer program product including a computer program carried on a computer-readable medium, the computer program containing program code for performing the methods shown in the flowchart. In such an embodiment, the computer program can be downloaded and installed from a network via a communication device 60, and / or installed from a removable external storage unit. When the computer program is executed by the processor 10, it implements the various functions defined in the method for correcting single-photon emission computed tomography (SPECT) images provided in this application.

[0042] Figure 2 A schematic flowchart of a method for correcting single-photon emission computed tomography images according to an embodiment of this application is shown. This is an example and not a limitation, and the method can be applied to the above-described electronic device.

[0043] S1: Acquire multi-window scan data obtained through single-photon emission computed tomography.

[0044] Multi-window scanning data includes main window scanning data and at least one scattering window scanning data.

[0045] During SPECT imaging, gamma rays emitted by a radioactive tracer may experience energy reduction as they pass through human tissue and reach the detector. This process is known as Compton scattering or the Compton effect. Compton scattering results in the detection data obtained by SPECT detecting not only the photons emitted by the radioactive tracer (representing the incident light from Compton scattering) but also lower-energy, longer-wavelength gamma rays. These lower-energy gamma rays represent the outgoing light from Compton scattering, and their intensity is negatively correlated with the electron number of the element causing the Compton scattering, or in other words, negatively correlated with the density of the human tissue causing the scattering. Since these lower-energy gamma rays are a product of the attenuation of gamma rays emitted by the radioactive tracer by the human tissue, their intensity reflects the degree of attenuation. This attenuation can be quantified using an attenuation coefficient, which represents the proportion of gamma ray attenuation per unit distance. Therefore, the attenuation coefficient of human tissue to gamma rays is positively correlated with the density of human tissue. Generally speaking, the density of bones is the highest and the attenuation coefficient is the highest, followed by soft tissues. The lungs, due to being filled with a large amount of air, have the lowest density and the lowest attenuation coefficient.

[0046] Master energy window scan data refers to the scan data acquired in SPECT imaging by setting an energy range window around the peak energy of photons emitted by the radioactive tracer (i.e., the most likely energy of the photons). For example, for technetium-99mTc-labeled compounds, the photon energy is approximately 140 keV, so the master energy window is set near this energy peak, typically encompassing a symmetrical energy range, such as 140 keV ± 10%, or 126 keV to 154 keV. The photon data acquired using this energy window is the master energy window scan data.

[0047] The master window primarily captures photons that have not undergone Compton scattering. These photons provide information about the distribution of radioactive tracers within the subject's body, which is crucial for diagnosing and assessing various physiological and pathological processes. For example, 99mTc-MDP (technetium 99m methylene bisphosphonate injection) mainly accumulates at bone lesions, emitting a large number of photons at these sites. By reconstructing images using master window scanning data, the signal strength in the images reflects the distribution of 99mTc-MDP, which can be used to assess the metabolic activity of bone tissue and the location of lesions.

[0048] In SPECT imaging, a scattering window is an energy range outside the peak energy of the main energy window. It's used to capture photons that undergo Compton scattering as they pass through human tissue. The energy of these photons decreases due to scattering, so the scattering window is typically set in a lower energy range. Using 99mTc as an example, the scattering window can be set to 120keV~126keV. The intensity of the scattering window scan signal reflects the attenuation coefficient of gamma rays in human tissue.

[0049] The number of scattering windows is the same as the amount of scattering window scan data, and there can be one or more. For example, ... Figure 3 As shown, taking 99mTc as an example, the main energy window is set to 126keV~154keV, and the scattering window is set to 120keV~126keV.

[0050] S2: Reconstruct the main energy window image using the main energy window scan data, and reconstruct the scattering window image using the scattering window scan data.

[0051] The specific reconstruction algorithm is not limited here; for example, an iterative algorithm can be used for reconstruction. Based on the scan data obtained from multiple tomographic scans, the reconstructed main energy window image and scattering window image are three-dimensional volume images of the same size. The coordinates of each voxel in the image are represented by (x, y, z), and the value of each voxel is used to reflect the intensity of the gamma rays at the corresponding spatial location. For example, the voxel value can be the photon count within a specified energy window at the corresponding spatial location.

[0052] When both the main energy window and the main energy window scan data have a quantity of 1, the main energy window image is reconstructed using this single main energy window scan data. Similarly, when both the scattering window and the scattering window scan data have a quantity of 1, the scattering window image is reconstructed using this single scattering window scan data. When both the scattering window and the scattering window scan data have a quantity greater than 1, interpolation estimation can be performed on all the scattering window scan data to obtain an interpolated scan data set. This interpolated scan data set is then used for reconstruction to obtain a single scattering window image.

[0053] Using 99mTc as an example, the number of scattering windows is two: a low-scattering window and a high-scattering window. The main energy window is set to 126keV~154keV, and the low-scattering window and high-scattering window are set approximately at the low energy (126keV) and high energy (154keV) of the main energy window, respectively, with some overlap with the main energy window. Specifically, the low-scattering window is set to 126 keV ± 5% (120 keV - 132 keV), and the high-scattering window is set to 154 keV ± 5% (146 keV - 162 keV). The high-scattering window is used to capture scattering events that "leak" into the high-energy region due to detector resolution limitations. The scan data of the two scattering windows can be interpolated using the following formula:

[0054] {C}_{scatter}=[({C}_{high}+{C}_{low}) / 2]*({E}_{main2}-{E}_{main1}) / ({E}_{high2}-{E}_{low1})

[0055] in, This indicates interpolated scan data. This represents the scan data of the high-scattering window. This represents the scan data from the low-scattering window. , , , These represent the boundary energies of the principal energy window, high scattering window, and low scattering window, respectively.

[0056] Optionally, to reduce the impact of noise on subsequent operations, body contour extraction can be performed on the main energy window image and the scattering window image after reconstruction is complete. Specifically, a small threshold can be set to set all voxel values ​​in the main energy window image and the scattering window image that are less than the threshold to 0. The threshold can be a fixed value or it can be adjustable; for example, a very small percentage (e.g., 3%) can be set, and the product of the maximum voxel value and this percentage can be used as the threshold.

[0057] S3: Calculate the attenuation coefficient image using the main energy window image and the scattering window image.

[0058] The scattering fraction of each voxel can be calculated using the main energy window image and the scattering window image. Then, human tissues can be classified based on the scattering fraction image, and different attenuation coefficients can be assigned to different human tissues to generate attenuation coefficient images.

[0059] like Figure 4 As shown, in a specific embodiment of this application, S3 includes the following parts.

[0060] S31: Calculate the scattering fraction image using the principal energy window image and the scattering window image.

[0061] Specifically, the intermediate image can be obtained by dividing the scattering window image by the main energy window image. This division is performed on the values ​​of each voxel, and can be expressed by the following formula:

[0062] When Main_map(x,y,z) is not 0:

[0063] M_map(x,y,z) = Scatter_map(x,y,z) / Main_map(x,y,z)

[0064] When Main_map(x,y,z) = 0:

[0065] M_map(x,y,z) = 0

[0066] Where M_map(x,y,z) represents the intermediate image, Main_map(x,y,z) represents the main energy window image, and Scatter_map(x,y,z) represents the scattering window image.

[0067] The intermediate image is then post-processed to obtain the scattering fraction image. The intermediate image, scattering fraction image, principal energy window image, and scattering window image are all the same size.

[0068] Post-processing may include at least one of image correction, smoothing, and normalization. Image correction may include multiplying the scattering window image with the intermediate image, where the multiplication is performed on the values ​​of each voxel, and can be expressed by the following formula:

[0069] SF_map(x,y,z) = Scatter_map(x,y,z)*M_map(x,y,z)

[0070] Here, SF_map(x,y,z) represents the scattering fraction image.

[0071] The specific algorithm for smoothing is not limited here; for example, it could be median filtering. Normalization limits the range of voxel values ​​to [0,1].

[0072] S32: Generate an attenuation coefficient image based on the scattering fraction image.

[0073] The resulting attenuation coefficient image has the same size as the scattering fraction image, and the value of each voxel in the attenuation coefficient image is determined by the value of the corresponding voxel in the scattering fraction image. Specifically, the scattering fraction image can be traversed, and based on the mapping relationship between the value range of voxels in the scattering fraction image and the attenuation coefficient, the attenuation coefficient corresponding to the value of each voxel in the scattering fraction image can be assigned to the corresponding voxel in the attenuation coefficient image.

[0074] Taking 99mTc as an example, with a photon energy of 140keV, the voxel values ​​of the normalized scattering fraction image are divided into three intervals: (0, 0.16] and (0.62, 1], (0.16, 0.5], and (0.5, 0.62). The first interval (0, 0.16] and (0.62, 1] belong to the lungs, with the lowest density, and the corresponding attenuation coefficient in the mapping relationship is 0.00022 / cm; the second interval (0.16, 0.5] belongs to soft tissue. The attenuation coefficient corresponding to the first interval in the mapping relationship is 0.12 / cm; the third interval (0.5, 0.62] belongs to the skeleton, and the attenuation coefficient corresponding to the third interval in the mapping relationship is 0.26 / cm. The scattering fraction image calculation is based on the scattering window image divided by the main energy window image. For the lungs, since the voxel values ​​of the scattering window and the main energy window images are very small, there may be cases where dividing by a very small value results in a very large scattering fraction. Considering this situation, the largest interval (0.62, 1] is assigned to the lungs.

[0075] S4: Attenuation correction is performed on the main energy window image using the attenuation coefficient image to obtain a single-photon emission computed tomography (CT) image.

[0076] The specific correction algorithm is not limited here; for example, it can be a post-correction method, an iterative method, etc.

[0077] Through the implementation of this embodiment, multi-window scanning data obtained by single-photon emission computed tomography (SPECT) is acquired. The multi-window scanning data includes main window scanning data and at least one scattering window scanning data. A main window image is reconstructed using the main window scanning data, and a scattering window image is reconstructed using the scattering window scanning data. An attenuation coefficient image is calculated using the main window image and the scattering window image. The main window image is corrected using the attenuation coefficient image to obtain a single-photon emission computed tomography (SPECT) image. The attenuation coefficient image required for attenuation correction can be obtained using the multi-window scanning data obtained by single-photon emission computed tomography (SPECT). CT imaging is not required, no additional cost is added to the SPECT equipment, and registration of CT imaging results with SPECT imaging results is no longer necessary. This eliminates the radioactive radiation caused by CT imaging to the examined object, reduces the cost and radiation impact of SPECT, and improves the accuracy of imaging.

[0078] The following example, with reference to the accompanying drawings, illustrates the specific process of the correction method for single-photon emission computed tomography (SPECT) images.

[0079] like Figure 5 As shown in a specific embodiment of this application, the correction method for single-photon emission computed tomography (SPECT) images includes the following parts. This embodiment is a further extension of the foregoing embodiments, and the parts that are the same as those for the foregoing embodiments will not be repeated here.

[0080] S11: Acquire multi-window scan data obtained by single-photon emission computed tomography.

[0081] S12: Reconstruct the main energy window image using the main energy window scan data, and reconstruct the scattering window image using the scattering window scan data.

[0082] Reconstruction can be performed iteratively using the Block Sequential Regularized Expectation Maximization (BSREM) algorithm. The resulting scattering window image has a size of 1.

[0083] S13: Extract body contours from the main window image and the scattering window image.

[0084] S14: Divide the scattering window image by the main energy window image to obtain the intermediate image.

[0085] S15: Perform image correction, smoothing, and normalization on the intermediate image to obtain the scattering fraction image.

[0086] The median filter coefficients used for smoothing are set to (1,1,1).

[0087] S16: Generate an attenuation coefficient image based on the scattering fraction image.

[0088] S17: Correct the main energy window image using the attenuation coefficient image to obtain a single-photon emission computed tomography (CT) image.

[0089] Specific Example 1

[0090] The radioactive tracer was 99mTc-3PRGD2, the examination site was the chest, and the raw SPECT images (i.e., uncorrected master window images) were acquired as follows: Figure 6 As shown, according to Figure 5 The detailed implementation flowchart shown illustrates the results of attenuation correction on the original SPECT image. Figure 7 As shown, the results provided by the equipment manufacturer based on CT attenuation correction are as follows: Figure 8 As shown, Figure 8 and Figure 7 The difference image (where the voxel value of each voxel is...) Figure 8 and Figure 7 (The difference in voxel values ​​at the same location) such as Figure 9 As shown.

[0091] Specific Example 2

[0092] The radioactive tracer was 99mTc-ECD, the examination site was the brain, and the raw SPECT images acquired are as follows: Figure 10 As shown, according to Figure 5The detailed implementation flowchart shown illustrates the results of attenuation correction on the original SPECT image. Figure 11 As shown, the results provided by the equipment manufacturer based on CT attenuation correction are as follows: Figure 12 As shown, Figure 12 and Figure 11 The difference image is as follows Figure 13 As shown.

[0093] Figure 14 A schematic diagram of a single-photon emission computed tomography (SPECT) image correction device according to an embodiment of this application is shown. The SPECT image correction device includes an acquisition module 11, a reconstruction module 12, a calculation module 13, and a correction module 14.

[0094] The acquisition module 11 is used to acquire multi-window scanning data obtained by single-photon emission computed tomography, the multi-window scanning data including main window scanning data and at least one scattering window scanning data;

[0095] Reconstruction module 12 is used to reconstruct the main energy window image using the main energy window scan data and to reconstruct the scattering window image using the scattering window scan data;

[0096] Calculation module 13 is used to calculate the attenuation coefficient image using the main energy window image and the scattering window image;

[0097] The correction module 14 is used to correct the main energy window image using the attenuation coefficient image to obtain a single-photon emission computed tomography image.

[0098] It should be noted that the information interaction and execution process between the above-mentioned devices / modules / units are based on the same concept as the method embodiments of this application. For details on their specific functions and technical effects, please refer to the method embodiments section, and they will not be repeated here.

[0099] It should be understood that the sequence number of each step in the above embodiments does not imply the order of execution. The execution order of each process should be determined by its function and internal logic, and should not constitute any limitation on the implementation process of the embodiments of this application.

[0100] Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the above-described division of functional units and modules is merely an example. In practical applications, the above functions can be assigned to different functional units and modules as needed, that is, the internal structure of the device can be divided into different functional units or modules to complete all or part of the functions described above. The functional units and modules in the embodiments can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit. Furthermore, the specific names of the functional units and modules are only for easy differentiation and are not intended to limit the scope of protection of this application. The specific working process of the units and modules in the above system can be referred to the corresponding process in the foregoing method embodiments, and will not be repeated here.

[0101] This application also provides a computer-readable storage medium storing a computer program that, when executed by a processor, implements the steps described in the various method embodiments above.

[0102] If the integrated unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, all or part of the processes in the methods of the above embodiments of this application can be implemented by a computer program instructing related hardware. The computer program can be stored in a computer-readable storage medium, and when executed by a processor, it can implement the steps of the various method embodiments described above. The computer program includes computer program code, which can be in the form of source code, object code, executable files, or certain intermediate forms. The computer-readable medium can include at least: any entity or device capable of carrying computer program code to a photographic device / electronic device, a recording medium, a computer memory, a read-only memory (ROM), a random access memory (RAM), an electrical carrier signal, a telecommunication signal, and a software distribution medium. Examples include USB flash drives, portable hard drives, magnetic disks, or optical disks. In some jurisdictions, according to legislation and patent practice, computer-readable media cannot be electrical carrier signals or telecommunication signals.

[0103] In the above embodiments, the descriptions of each embodiment have different focuses. For parts that are not described in detail or recorded in a certain embodiment, please refer to the relevant descriptions of other embodiments.

[0104] Those skilled in the art will recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0105] In the embodiments provided in this application, it should be understood that the disclosed apparatus / network devices and methods can be implemented in other ways. For example, the apparatus / network device embodiments described above are merely illustrative. For instance, the division of modules or units is only a logical functional division, and in actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the coupling or direct coupling or communication connection shown or discussed may be through some interfaces; the indirect coupling or communication connection between devices or units may be electrical, mechanical, or other forms.

[0106] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.

[0107] The above-described embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application 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 spirit and scope of the technical solutions of the embodiments of this application, and should all be included within the protection scope of this application.

Claims

1. A correction method for single-photon emission computed tomography (SPECT), characterized in that, The method includes: Acquire multi-window scanning data obtained by single-photon emission computed tomography, wherein the multi-window scanning data includes main window scanning data and at least one scattering window scanning data; The main energy window image is reconstructed using the main energy window scan data, and the scattering window image is reconstructed using the scattering window scan data. The attenuation coefficient image is calculated using the main energy window image and the scattering window image; The attenuation coefficient image is used to correct the main energy window image to obtain a single-photon emission computed tomography (CT) image. The calculation of the attenuation coefficient image using the main energy window image and the scattering window image includes: The intermediate image is obtained by dividing the scattering window image by the main energy window image. The intermediate image is post-processed to obtain a scattering fraction image, wherein the post-processing includes at least one of image correction, smoothing and normalization; Traverse the scattering fraction image, and according to the mapping relationship between the value range of voxels in the scattering fraction image and the attenuation coefficient, assign the attenuation coefficient corresponding to the value of each voxel in the scattering fraction image to the corresponding voxel in the attenuation coefficient image. The size of the attenuation coefficient image is the same as that of the scattering fraction image, and the value of each voxel in the attenuation coefficient image is determined by the value of the corresponding voxel in the scattering fraction image.

2. The method as described in claim 1, characterized in that, The image correction includes multiplying the scatter window image with the intermediate image.

3. The method according to any one of claims 1-2, characterized in that, Before calculating the attenuation coefficient image using the main energy window image and the scattering window image, the following steps are also included: Body contour extraction is performed on the main energy window image and the scattering window image.

4. A correction device for single-photon emission computed tomography (CT) images, characterized in that, The device includes: The acquisition module is used to acquire multi-window scanning data obtained by single-photon emission computed tomography, wherein the multi-window scanning data includes main window scanning data and at least one scattering window scanning data. The reconstruction module is used to reconstruct a main energy window image using the main energy window scan data, and to reconstruct a scattering window image using the scattering window scan data. The calculation module is used to calculate the attenuation coefficient image using the main energy window image and the scattering window image; The correction module is used to correct the main energy window image using the attenuation coefficient image to obtain a single-photon emission computed tomography image. The calculation module is specifically used to divide the scattering window image by the main energy window image to obtain an intermediate image; to perform post-processing on the intermediate image to obtain a scattering fraction image, wherein the post-processing includes at least one of image correction, smoothing, and normalization; to traverse the scattering fraction image, and according to the mapping relationship between the value range of voxels in the scattering fraction image and the attenuation coefficient, to assign the attenuation coefficient corresponding to the value of each voxel in the scattering fraction image to the corresponding voxel in the attenuation coefficient image, wherein the size of the attenuation coefficient image is the same as that of the scattering fraction image, and the value of each voxel in the attenuation coefficient image is determined by the value of the corresponding voxel in the scattering fraction image.

5. An electronic device comprising a memory, a processor, and a computer program stored in the memory and executable by the processor, characterized in that, When the processor executes the computer program, it implements the method as described in any one of claims 1 to 3.

6. A computer-readable storage medium storing a computer program, characterized in that, When the computer program is executed by a processor, it implements the method as described in any one of claims 1 to 3.

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