Image position correction method and system for SPECT and CT equipment

Abstract

The invention relates to an image position correction method and system for SPECT and CT equipment, and the method comprises the steps: building a reference coordinate system, and enabling the original point of the reference coordinate system, the center of a CT light plane and the center of the SPECT to be on a Z axis; determining the distance Zs from the scanning starting position of the scanned object to the bed head and the distance Ze from the scanning ending position of the scanned object to the bed head by taking the Z axis as a reference; respectively determining SPECT and CT offset vectors from the SPECT and CT equipment coordinate systems to the reference coordinate system in combination with Zs and Ze; executing Alignment correction in system correction on the scanned image to obtain a correction offset vector of the CT image relative to the SPECT image; determining a final CT offset vector of the CT image converted to the reference coordinate system according to the initial CT offset vector and the corrected offset vector; and according to the SPECT offset vector and the final CT offset vector, carrying out position correction on the SPECT and CT equipment so as to carry out image fusion. The method has the beneficial effects that the problem of difference between equipment is solved, image fusion of the SPECT equipment and the CT equipment is realized, and the accuracy of the fused image is ensured.

Description

Technical Field

[0001] The present invention relates to the field of medical technology, and in particular to an image position correction method and system for SPECT and CT equipment. Background Art

[0002] SPECT, the full name of which is Single-Photon Emission Computed Tomography, is a commonly used imaging method in nuclear medicine. It uses the gamma rays emitted by single-photon radionuclides (such as 99mTc, etc.) injected into the human body, which are absorbed and converted into electrical signals by the detector, and then calculated by the computer to finally reconstruct the tomographic or overall image. These organs that can absorb radioactive drugs will appear as bright blocks in the image. If there is an abnormal absorption state, the abnormal part will be brighter or darker, thereby revealing the possibility of lesions.

[0003] SPECT / CT is a multimodal imager that integrates SPECT and CT imaging devices. In one scan, it can simultaneously obtain anatomical images acquired by CT and functional images acquired by SPECT, and can fuse the two in real time. It can observe both the anatomical morphology and the functional metabolism of the lesions, and is more conducive to discovering changes in early and hidden lesions.

[0004] After scanning the patient, SPECT / CT needs to fuse the SPECT DICOM image and CT DICOM image for diagnosis. SPECT and CT devices are very different devices. In the actual development of SPECT / CT, the two devices will be developed by different departments, and even the two devices will come from different manufacturers. SPECT devices will have a scanning bed corresponding to the SPECT device, and CT devices will have a scanning bed corresponding to the CT device. The DICOM images generated by the SPECT device and the CT device will also be generated through a custom device coordinate system, which will cause the images generated by the SPECT device and the CT device to be unable to be fused. Summary of the invention

[0005] Technical issues to be solved

[0006] In view of the above-mentioned shortcomings and deficiencies of the prior art, the present invention provides an image position correction method and system for SPECT and CT equipment, which solves the technical problem of how to fuse images generated by SPECT equipment and CT equipment developed by different departments or manufacturers.

[0007] Technical Solution

[0008] In order to achieve the above object, the main technical solutions adopted by the present invention include:

[0009] In a first aspect, the present invention provides an image position correction method for SPECT and CT equipment, comprising:

[0010] Establish a reference coordinate system, the origin of which, together with the center of the CT light plane and the center of the SPECT, are all on the Z axis;

[0011] Taking the Z axis as a reference, determine the distance Zs from the scanning start position of the scanned object to the bed head, and the distance Ze from the scanning end position of the scanned object to the bed head;

[0012] Determine the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system by combining Zs and Ze;

[0013] Determine the preliminary CT offset vector from the CT device coordinate system to the reference coordinate system by combining Zs and Ze;

[0014] Perform Alignment correction in system correction on the scanned image to obtain the correction offset vector of the CT image relative to the SPECT image;

[0015] Determine a final CT offset vector for converting the CT image to a reference coordinate system according to the SPECT offset vector and the correction offset vector;

[0016] The positions of the SPECT and CT devices are corrected according to the SPECT offset vector and the CT offset vector to perform image fusion.

[0017] Optionally, determining a SPECT offset vector from the SPECT device coordinate system to the reference coordinate system in combination with Zs and Ze includes:

[0018] The reconstruction range R of the image is calculated based on the spacing*row in the DICOM Tag of the scanned image;

[0019] Move the center of the scanned object to the SPECT center;

[0020] According to the ImagePosition in the DICOM Tag of the scanned image, the position Zz of the image center on the Z axis is obtained, and the range of the SPECT tomographic image on the Z axis is [Zz-Dz / 2, Zz+Dz / 2], where Dz=Ze-Zs, and the offset vector from the SPECT device coordinate system to the reference coordinate system is (0, 0, Vp), where Vp=Zs-Zz+Dz / 2.

[0021] Optionally, a preliminary CT offset vector for converting the CT image to a reference coordinate system is determined by combining Zs and Ze, including:

[0022] According to the distance Dpc from the CT light plane to the SPECT detection center, the coordinates of the center of the CT light plane in the reference coordinate system are determined to be (0, 0, Pct), where Pct = Dpc + Dz;

[0023] According to Dpc, the scanning object located in the range of [Zs, Ze] is moved to the range of the light plane for CT scanning;

[0024] According to the ImagePosition in the DICOM Tag of the first CT image, the position Zz2 of the center of the scanned image on the Z axis is obtained. The scanning range of the CT image on the Z axis is [Zz2, Zz2+Dz], and the initial offset vector from the CT device coordinate system to the reference coordinate system is (0, 0, Vct), where Vct = Zz2-Pct-Zs.

[0025] Optionally, determining a final CT offset vector for converting the CT image to a reference coordinate system according to the preliminary CT offset vector and the correction offset vector includes:

[0026] The preliminary CT offset vector (0, 0, Vct) and the correction offset vector (Ax, Ay, Az) are added to obtain the final CT offset vector (Vcx, Vcy, Vcz), where Vcx=Ax, Vcy=Ay, Vcz=Vct+Az.

[0027] Optionally, performing position correction on the SPECT image and the CT image according to the SPECT offset vector and the final CT offset vector includes:

[0028] All scanned SPECT images are added with the SPECT offset vector (0, 0, Vp), and all scanned CT images are added with the final CT offset vector (Vcx, Vcy, Vcz), and the SPECT images and CT images are corrected in the same coordinate system to achieve position correction of the SPECT images and CT images.

[0029] Optionally, the method further comprises:

[0030] The PET offset vector is determined by the same steps as SPECT, and the position correction of the PET and SPECT equipment, or the position correction of the PET / CT equipment, is achieved based on the PET offset vector.

[0031] In a second aspect, the present invention provides an image position correction system for SPECT and CT equipment, comprising:

[0032] A coordinate system establishment module is used to establish a reference coordinate system, where the origin of the reference coordinate system and the center of the CT light plane and the center of the SPECT are all on the Z axis;

[0033] The first determination module determines the distance Zs from the scanning start position of the scanned object to the bed head, and the distance Ze from the scanning end position of the scanned object to the bed head based on the Z axis;

[0034] A second determination module determines a SPECT offset vector from the SPECT device coordinate system to the reference coordinate system in combination with Zs and Ze;

[0035] A third determination module determines a preliminary CT offset vector from the CT device coordinate system to the reference coordinate system in combination with Zs and Ze;

[0036] A correction offset vector determination module performs alignment correction in system correction on the scanned image to obtain a correction offset vector of the CT image relative to the SPECT image;

[0037] A fourth determination module determines a final CT offset vector for converting the CT image to a reference coordinate system according to the preliminary CT offset vector and the correction offset vector;

[0038] The correction module performs position correction on the SPECT and CT devices according to the SPECT offset vector and the final CT offset vector to perform image fusion.

[0039] In a third aspect, the present invention provides a computer-readable storage medium having a computer program stored thereon, wherein when the program is executed, the image position correction method for SPECT and CT equipment described in any one of the first aspects above is implemented.

[0040] In a fourth aspect, the present invention provides a storage device comprising a storage medium and a processor, wherein the storage medium stores a computer program, and when the program is executed by the processor, an image position correction method for SPECT and CT equipment as described in any one of the first aspects above is implemented.

[0041] Beneficial Effects

[0042] The beneficial effects of the present invention are as follows: the image position correction method for SPECT and CT devices of the present invention, by defining a conversion vector of a SPECT image and a conversion vector of a CT image, allows the SPECT and CT devices to be converted to the same reference coordinate system to achieve fusion. The problem of differences between SPECT devices and CT devices developed by different departments or manufacturers is solved. Even if the differences between different devices are large, position correction can be achieved through the method of the present invention, and it can be applied between multiple devices to ensure the accuracy of the fused image and improve the reliability of the fusion result. It can provide doctors with a more accurate and comprehensive basis for diagnosis and treatment, and improve the accuracy and safety of treatment. BRIEF DESCRIPTION OF THE DRAWINGS

[0043] Figure 1A flow chart of an image position correction method for SPECT and CT equipment provided by an embodiment of the present invention;

[0044] Figure 2 A schematic diagram of the arrangement of devices provided in an embodiment of the present invention;

[0045] Figure 3 A schematic diagram of object scanning provided by an embodiment of the present invention;

[0046] Figure 4 A schematic diagram of a reference coordinate system provided by an embodiment of the present invention;

[0047] Figure 5 A schematic diagram of a scanned object in a reference coordinate system provided by an embodiment of the present invention. DETAILED DESCRIPTION

[0048] In order to better explain the present invention and facilitate understanding, the present invention is described in detail below through specific implementation modes in conjunction with the accompanying drawings.

[0049] The embodiment of the present invention proposes an image position correction method for SPECT and CT devices, which can enable SPECT and CT devices developed by two different departments or manufacturers to achieve image fusion through bed and image correction. At the same time, this method can be extended to different combinations of SPECT, PET, and CT devices, such as SPECT / CT, PET / CT, and SPECT / PET / CT.

[0050] In order to better understand the above technical solution, exemplary embodiments of the present invention will be described in more detail below with reference to the accompanying drawings. Although exemplary embodiments of the present invention are shown in the accompanying drawings, it should be understood that the present invention can be implemented in various forms and should not be limited by the embodiments described herein. On the contrary, these embodiments are provided to enable a clearer and more thorough understanding of the present invention and to fully convey the scope of the present invention to those skilled in the art.

[0051] First, refer to Figure 1 This embodiment provides an image position correction method for SPECT and CT equipment, comprising:

[0052] S1, establish a reference coordinate system, the origin of the reference coordinate system and the center of the CT light plane and the center of the SPECT are all on the Z axis.

[0053] like Figure 2 The figure shows the physical placement of the equipment. From the perspective of human vision, they are the bed, SPECT equipment, and CT equipment.

[0054] like Figure 3The figure shows a schematic diagram of object scanning. When scanning SPECT, the detector collects images within a certain interval at one time, such as the black part in the schematic diagram, and then reconstructs the tomographic image. When scanning CT, the device reconstructs the tomographic image of the object passing through the CT light plane by pushing the bed at a constant speed. Therefore, SPECT moves the bed to a fixed position, performs tomographic scanning and reconstruction, and can obtain the tomographic image of the target. CT needs to determine the movement range of the bed and scan to obtain the target image.

[0055] First, set up a reference coordinate system. Since the SPECT / CT device scans mainly based on SPECT, all standard coordinate systems use the SPECT device position as the reference coordinate. Figure 4 It is a schematic diagram of the reference coordinate system. Looking from the direction of the bed toward the equipment, the positive direction of X is to the right, the positive direction of Y is outward, and the positive direction of Z is outward.

[0056] S2, using the Z axis as a reference, determining the distance Zs from the scan start position of the scanned object to the bed head, and the distance Ze from the scan end position of the scanned object to the bed head.

[0057] In the reference coordinate system, the origin coordinate (0, 0, 0) is defined as O(sc). Under ideal conditions without mechanical installation errors, the x and y coordinates of the origin, the center of the CT light plane, and the center of the SPECT are the same, all 0, and all three points are on the Z axis.

[0058] It is located at the same position as the CT light plane center and the SPECT center in the Z-axis direction. Figure 4 The position (0, 0, 0) is the origin of the reference coordinate system.

[0059] For the object in the scanning diagram, the distance from the starting position to the bedside is Zs, the distance from the ending position to the bed is Ze, and the length from the start to the end is Dz = Ze-Zs. The desired image center range in the Z direction is (0, 0, Zs) to (0, 0, Ze). In actual scanning, it is necessary to achieve that the range of the image reconstructed by SPECT and CT for the object is from Zs to Ze in the Z direction, so that SPECT and CT can be correctly fused.

[0060] S3, combining Zs and Ze to determine the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system.

[0061] SPECT images with different parameters have different sizes, but the center of all SPECT images is located at the center of the SPECT detector.

[0062] Combination Figure 5, move the center of the scanned object to the center of SPECT, and set the moving distance to Zc, where the length of Zc is Zs plus the distance from the bedside to the center of SPECT.

[0063] Optionally, determining a SPECT offset vector from the SPECT device coordinate system to the reference coordinate system in combination with Zs and Ze includes:

[0064] The reconstruction range R of the image is calculated based on the spacing*row in the DICOM Tag of the scanned image;

[0065] Move the center of the scanned object to the SPECT center;

[0066] According to the ImagePosition in the DICOM Tag of the scanned image, the position Zz of the image center on the Z axis is obtained, and the range of the SPECT tomographic image on the Z axis is [Zz-Dz / 2, Zz+Dz / 2], where Dz=Ze-Zs, and the offset vector from the SPECT device coordinate system to the reference coordinate system is (0, 0, Vp), where Vp=Zs-Zz+Dz / 2.

[0067] S4, combining Zs and Ze to determine a preliminary CT offset vector from the CT device coordinate system to the reference coordinate system.

[0068] Optionally, a preliminary CT offset vector for converting the CT image to a reference coordinate system is determined by combining Zs and Ze, including:

[0069] According to the distance Dpc from the CT light plane to the SPECT detection center, the coordinates of the center of the CT light plane in the reference coordinate system are determined to be (0, 0, Pct), where Pct = Dpc + Dz;

[0070] According to Dpc, the scanning object located in the range of [Zs, Ze] is moved to the range of the light plane for CT scanning;

[0071] According to the ImagePosition in the DICOM Tag of the first CT image, the position Zz2 of the center of the scanned image on the Z axis is obtained. The scanning range of the CT image on the Z axis is [Zz2, Zz2+Dz], and the initial offset vector from the CT device coordinate system to the reference coordinate system is (0, 0, Vct), where Vct = Zz2-Pct-Zs.

[0072] By physically measuring the distance between the CT light plane and the SPECT detection center, the value of the distance is determined as Dpc mm.

[0073] When using CT to scan an object in the range [Zs, Ze], it is necessary to move the object in this range into the light plane. The distance the object needs to be moved can be calculated to be [Pct+Zs, Pct+Ze].

[0074] S5, performing alignment correction in system correction on the scanned image to obtain a correction offset vector of the CT image relative to the SPECT image.

[0075] S6, determining a final CT offset vector for converting the CT image to the reference coordinate system according to the SPECT offset vector and the correction offset vector.

[0076] Optionally, determining a final CT offset vector for converting the CT image to a reference coordinate system according to the preliminary CT offset vector and the correction offset vector includes:

[0077] The preliminary CT offset vector (0, 0, Vct) and the correction offset vector (Ax, Ay, Az) are added to obtain the final CT offset vector (Vcx, Vcy, Vcz), where Vcx=Ax, Vcy=Ay, Vcz=Vct+Az.

[0078] S7, performing position correction on the SPECT and CT devices according to the SPECT offset vector and the CT offset vector to perform image fusion.

[0079] Optionally, performing position correction on the SPECT image and the CT image according to the SPECT offset vector and the final CT offset vector includes:

[0080] All scanned SPECT images are added with the SPECT offset vector (0, 0, Vp), and all scanned CT images are added with the final CT offset vector (Vcx, Vcy, Vcz), and the SPECT images and CT images are corrected in the same coordinate system to achieve position correction of the SPECT images and CT images.

[0081] All scanned SPECT images are added with the conversion vector (0, 0, Vp), and all scanned CT images are added with the conversion vector (Vcx, Vcy, Vcz), so that the SPECT tomographic images and CT tomographic images are in the same coordinate system, and the overlapping scanning ranges of the two devices can be fused normally.

[0082] Optionally, the method further comprises:

[0083] The PET offset vector is determined by the same steps as SPECT, and the position correction of the PET and SPECT equipment, or the position correction of the PET / CT equipment, is achieved based on the PET offset vector.

[0084] Both PET and SPECT devices move the bed to a specified position, then collect data within a range and reconstruct a DICOM image. The same method can be used for position correction of SPECT and PET. When CT needs to scan, the bed is moved, data within a range is collected and reconstructed to generate a DICOM image. If the combination is a PET / CT device, you only need to refer to the calculation method of SPECT to obtain the transformation vector of PET.

[0085] If it is a combination of PET / SPECT / CT, you only need to refer to the calculation method of SPECT, and add the transformation vector of PET to get the correction method of the image position of the combination of the three devices.

[0086] This embodiment provides an image position correction method for SPECT and CT devices. By defining a conversion vector of a SPECT image and a conversion vector of a CT image, the SPECT and CT devices are converted to the same reference coordinate system to achieve fusion. This solves the problem of differences between SPECT devices and CT devices developed by different departments or manufacturers. Even if the differences between different devices are large, position correction can be achieved through the method of the present invention, and it can be applied between multiple devices to ensure the accuracy of the fused image and improve the reliability of the fusion results. It can provide doctors with a more accurate and comprehensive basis for diagnosis and treatment, and improve the accuracy and safety of treatment.

[0087] In a second aspect, the present embodiment provides an image position correction system for SPECT and CT equipment, including: a coordinate system establishment module, which establishes a reference coordinate system, wherein the origin of the reference coordinate system and the center of the CT light plane and the SPECT center are all on the Z axis; a first determination module, which determines the distance Zs from the scanning start position of the scanned object to the bedside, and the distance Ze from the scanning end position of the scanned object to the bedside with the Z axis as the reference; a second determination module, which determines the SPECT offset vector from the SPECT equipment coordinate system to the reference coordinate system in combination with Zs and Ze; a third determination module, which determines the preliminary CT offset vector from the CT equipment coordinate system to the reference coordinate system in combination with Zs and Ze; a correction offset vector determination module, which performs alignment correction in system correction on the scanned image to obtain the correction offset vector of the CT image relative to the SPECT image; a fourth determination module, which determines the final CT offset vector for converting the CT image to the reference coordinate system based on the preliminary CT offset vector and the correction offset vector; and a correction module, which performs position correction on the SPECT and CT equipment based on the SPECT offset vector and the final CT offset vector to perform image fusion. According to the image position correction system for SPECT and CT devices provided in this embodiment, since it is used to implement the steps of an image position correction method for SPECT and CT devices provided in the first aspect of the present invention, the image position correction system for SPECT and CT devices has all the technical effects of the image position correction method for SPECT and CT devices, which will not be repeated here.

[0088] In a third aspect, an embodiment of the present invention provides a computer-readable storage medium having a computer program stored thereon, wherein when the program is executed, the image position correction method for SPECT and CT equipment described in any one of the first aspects above is implemented.

[0089] In a fourth aspect, an embodiment of the present invention provides a storage device, comprising a storage medium and a processor, wherein the storage medium stores a computer program, and when the program is executed by the processor, an image position correction method for SPECT and CT devices as described in any one of the first aspects above is implemented.

[0090] It will be appreciated by those skilled in the art that embodiments of the present invention may be provided as methods, systems or computer program products. Therefore, the present invention may take the form of a complete hardware embodiment, a complete 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 computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0091] Obviously, those skilled in the art can make various modifications and variations to the present invention without departing from the spirit and scope of the present invention. Thus, if these modifications and variations of the present invention fall within the scope of the claims of the present invention and their equivalents, the present invention should also include these modifications and variations.

[0092] Although the embodiments of the present invention have been shown and described above, it is to be understood that the above embodiments are exemplary and are not to be construed as limitations of the present invention. A person skilled in the art may alter, modify, replace and modify the above embodiments within the scope of the present invention.

Claims

1. An image position correction method for SPECT and CT equipment, characterized in that: include: Establish a reference coordinate system, the origin of which, together with the center of the CT light plane and the center of the SPECT, are all on the Z axis; Taking the Z axis as a reference, determine the distance Zs from the scanning start position of the scanned object to the bed head, and the distance Ze from the scanning end position of the scanned object to the bed head; Determine the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system by combining Zs and Ze; Determine the preliminary CT offset vector from the CT device coordinate system to the reference coordinate system by combining Zs and Ze; Perform alignment correction in system correction on the scanned image to obtain a correction offset vector of the CT image relative to the SPECT image; Determine a final CT offset vector for converting the CT image to a reference coordinate system according to the preliminary CT offset vector and the correction offset vector; The positions of the SPECT and CT devices are corrected according to the SPECT offset vector and the final CT offset vector for image fusion.

2. The image position correction method for SPECT and CT equipment according to claim 1, characterized in that: Combining Zs and Ze to determine the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system includes: The reconstruction range R of the image is calculated based on the spacing*row in the DICOM Tag of the scanned image; Move the center of the scanned object to the SPECT center; According to the ImagePosition in the DICOM Tag of the scanned image, the position Zz of the image center on the Z axis is obtained, and the range of the SPECT tomographic image on the Z axis is [Zz-Dz / 2, Zz+Dz / 2], where Dz=Ze-Zs, and the offset vector from the SPECT device coordinate system to the reference coordinate system is (0, 0, Vp), where Vp=Zs-Zz+Dz / 2.

3. The image position correction method for SPECT and CT equipment according to claim 2, characterized in that: Combine Zs and Ze to determine the preliminary CT offset vector for transforming the CT image to the reference coordinate system, including: According to the distance Dpc from the CT light plane to the SPECT detection center, the coordinates of the center of the CT light plane in the reference coordinate system are determined to be (0, 0, Pct), where Pct = Dpc + Dz; According to Dpc, the scanning object located in the range of [Zs, Ze] is moved to the range of the light plane for CT scanning; According to the ImagePosition in the DICOM Tag of the first CT image, the position Zz2 of the center of the scanned image on the Z axis is obtained. The scanning range of the CT image on the Z axis is [Zz2, Zz2+Dz], and the initial offset vector from the CT device coordinate system to the reference coordinate system is (0, 0, Vct), where Vct = Zz2-Pct-Zs.

4. The image position correction method for SPECT and CT equipment according to claim 3, characterized in that: The final CT offset vector for converting the CT image to the reference coordinate system is determined according to the preliminary CT offset vector and the correction offset vector, including: The preliminary CT offset vector (0, 0, Vct) and the correction offset vector (Ax, Ay, Az) are added to obtain the final CT offset vector (Vcx, Vcy, Vcz), where Vcx=Ax, Vcy=Ay, Vcz=Vct+Az.

5. The image position correction method for SPECT and CT equipment according to claim 4, characterized in that: The SPECT image and the CT image are positionally corrected according to the SPECT offset vector and the final CT offset vector, including: All scanned SPECT images are added with the SPECT offset vector (0, 0, Vp), and all scanned CT images are added with the final CT offset vector (Vcx, Vcy, Vcz), and the SPECT images and CT images are corrected in the same coordinate system to achieve position correction of the SPECT images and CT images.

6. The image position correction method for SPECT and CT equipment according to claim 5, characterized in that: The method further comprises: The PET offset vector is determined by the same steps as SPECT, and the position correction of the PET and SPECT equipment, or the position correction of the PET / CT equipment, is achieved based on the PET offset vector.

7. An image position correction system for SPECT and CT equipment, characterized in that: include: A coordinate system establishment module is used to establish a reference coordinate system, where the origin of the reference coordinate system and the center of the CT light plane and the center of the SPECT are all on the Z axis; The first determination module determines the distance Zs from the scanning start position of the scanned object to the bed head, and the distance Ze from the scanning end position of the scanned object to the bed head based on the Z axis; A second determination module determines a SPECT offset vector from the SPECT device coordinate system to the reference coordinate system in combination with Zs and Ze; A third determination module determines a preliminary CT offset vector from the CT device coordinate system to the reference coordinate system in combination with Zs and Ze; A correction offset vector determination module performs alignment correction in system correction on the scanned image to obtain a correction offset vector of the CT image relative to the SPECT image; A fourth determination module determines a final CT offset vector for converting the CT image to a reference coordinate system according to the preliminary CT offset vector and the correction offset vector; The correction module performs position correction on the SPECT and CT devices according to the SPECT offset vector and the final CT offset vector to perform image fusion.

8. A computer-readable storage medium having a computer program stored thereon, characterized in that: When the computer program is executed by a processor, the image position correction method for SPECT and CT equipment described in any one of claims 1 to 6 is implemented.

9. A storage device comprising a storage medium and a processor, wherein the storage medium stores a computer program, wherein: When the processor executes the computer program, the image position correction method for SPECT and CT equipment described in any one of claims 1 to 6 is implemented.

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