A method and system for image position correction for SPECT and CT devices

Abstract

The present application relates to a kind of image position correction method and system for SPECT and CT equipment, the method comprises: establishing reference coordinate system, reference coordinate system origin and CT light plane center and SPECT center are all on Z axis;With Z axis as reference, the distance Zs of the scanning starting position of scanning object to bedhead is determined, the distance Ze of the scanning end position of scanning object to bedhead;SPECT and CT equipment coordinate system to reference coordinate system is determined SPECT and CT offset vector in combination with Zs and Ze respectively;Alignment correction in system correction is carried out to scanning image, and the correction offset vector of CT image relative to SPECT image is obtained;According to preliminary CT offset vector and correction offset vector, the final CT offset vector of CT image conversion to reference coordinate system is determined;According to SPECT offset vector and final CT offset vector, SPECT and CT equipment are carried out position correction, to carry out image fusion.It has beneficial effect, the difference between equipment is solved, the image fusion of SPECT and CT equipment is realized, and the accuracy of image after fusion is ensured.

Description

TECHNICAL FIELD

[0001] The present application relates to the medical technology field, and in particular to an image position correction method and system for SPECT and CT devices. BACKGROUND

[0002] SPECT, which stands for Single-Photon Emission Computed Tomography, is a common imaging method in nuclear medicine. It uses the gamma rays emitted by single-photon radioactive isotopes (such as 99mTc) injected into the human body, which are absorbed by the detector and converted into electrical signals, and then calculated by a computer to finally reconstruct tomographic or whole-body images. Organs that can absorb radioactive drugs will appear as bright blocks in the image, and abnormal absorption will cause abnormal parts to be brighter or darker, thus revealing possible lesions.

[0003] SPECT / CT is a multi-modal imaging device that combines SPECT and CT imaging devices. It can obtain both CT anatomical images and SPECT functional images in one scan, and can fuse them in real time. This allows for observation of both the anatomical morphology of the lesion and its functional metabolism, making it easier to detect early and occult changes in the lesion.

[0004] After scanning the patient, SPECT DICOM images and CT DICOM images need to be fused for diagnosis. SPECT and CT devices are very different, and in actual development of SPECT / CT, the two devices are developed by different departments, or even from different manufacturers. SPECT devices have corresponding scan beds, CT devices have corresponding scan beds, and SPECT and CT devices generate DICOM images through custom device coordinate systems, which makes it impossible to fuse the images generated by SPECT and CT devices. SUMMARY

[0005] Technical problems to be solved

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

[0007] Technical solutions

[0008] In order to achieve the above-mentioned purposes, the main technical solutions adopted by the present application include:

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

[0010] establishing a reference coordinate system, the origin of which is on the Z axis with the center of the CT light plane and the center of the SPECT;

[0011] determining 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, with the Z axis as the reference;

[0012] determining the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system in combination with Zs and Ze;

[0013] determining the preliminary CT offset vector from the CT device coordinate system to the reference coordinate system in combination with Zs and Ze;

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

[0015] determining the final CT offset vector of the CT image converted to the reference coordinate system according to the SPECT offset vector and the correction offset vector;

[0016] performing the position correction on the SPECT and CT devices according to the SPECT offset vector and the CT offset vector for image fusion.

[0017] Optionally, the determination of the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system in combination with Zs and Ze comprises:

[0018] calculating the reconstruction range R of the image according to the spacing*row in the DICOM Tag of the scanning image;

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

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

[0021] Optionally, the determination of the preliminary CT offset vector of the CT image converted to the reference coordinate system in combination with Zs and Ze comprises:

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

[0023] According to Dpc, the scanning object located in the range of [Zs, Ze] is moved to the CT light plane range 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 scanning image on the Z axis is obtained, and the scanning range of the CT image on the Z axis is [Zz2, Zz2+Dz], and the preliminary offset vector of the CT device coordinate system to the reference coordinate system is (0, 0, Vct), wherein Vct=Zz2-Pct-Zs.

[0025] Optionally, the final CT offset vector of the CT image converted to the reference coordinate system is determined according to the preliminary CT offset vector and the correction offset vector, and the final CT offset vector comprises:

[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), wherein Vcx=Ax, Vcy=Ay, and Vcz=Vct+Az.

[0027] Optionally, the position correction of the SPECT image and the CT image is performed according to the SPECT offset vector and the final CT offset vector, and the position correction comprises:

[0028] The SPECT offset vector (0, 0, Vp) is added to all the scanned SPECT images, and the final CT offset vector (Vcx, Vcy, Vcz) is added to all the scanned CT images, so that the SPECT image and the CT image are corrected in the same coordinate system, and the position correction of the SPECT image and the CT image is realized.

[0029] Optionally, the method further comprises:

[0030] The PET offset vector is determined by using the same steps as the SPECT, and the position correction of the PET and SPECT devices or the position correction of the PET / CT device is realized according to the PET offset vector.

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

[0032] The coordinate system establishing module establishes the reference coordinate system, and the origin of the reference coordinate system is on the Z axis with the center of the CT light plane and the center of the SPECT;

[0033] The first determining module determines a distance Zs from a scanning starting position of the scanning object to the bed head and a distance Ze from a scanning ending position of the scanning object to the bed head based on the Z axis as a reference;

[0034] The second determining module determines a SPECT offset vector from the SPECT device coordinate system to the reference coordinate system based on the Zs and the Ze;

[0035] The third determining module determines a preliminary CT offset vector from the CT device coordinate system to the reference coordinate system based on the Zs and the Ze;

[0036] The correction offset vector determining module performs an Alignment correction in system correction on the scanning image to obtain a correction offset vector of the CT image relative to the SPECT image;

[0037] The fourth determining module determines a final CT offset vector of the CT image converted to the reference coordinate system based on the preliminary CT offset vector and the correction offset vector;

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

[0039] In a third aspect, the present application provides a computer readable storage medium, which stores a computer program, and the program is executed to realize the image position correction method for the SPECT and the CT device according to any one of the first aspect.

[0040] In a fourth aspect, the present application provides a storage device, which comprises a storage medium and a processor, and the storage medium stores a computer program, and the program is executed by the processor to realize the image position correction method for the SPECT and the CT device according to any one of the first aspect.

[0041] Advantages

[0042] The present application has the following advantages: the image position correction method for the SPECT and the CT device according to the present application converts the SPECT and the CT device to the same reference coordinate system by defining a conversion vector of the SPECT image and a conversion vector of the CT image, and realizes fusion. The difference between the SPECT device and the CT device developed by different departments or manufacturers is solved. Even if the difference between different devices is large, the position correction can be realized by the method of the present application, and the method can be applied between multiple devices, ensuring the accuracy of the fused image and improving the reliability of the fusion result. The method can provide more accurate and comprehensive basis for doctors, and improve the accuracy and safety of treatment. BRIEF DESCRIPTION OF DRAWINGS

[0043] Figure 1A flow chart of a method for image position correction of SPECT and CT devices is provided in the embodiments of the present application.

[0044] Figure 2 A device placement diagram is provided in the embodiments of the present application.

[0045] Figure 3 An object scanning diagram is provided in the embodiments of the present application.

[0046] Figure 4 A reference coordinate system diagram is provided in the embodiments of the present application.

[0047] Figure 5 A diagram of a scanned object in a reference coordinate system is provided in the embodiments of the present application. DETAILED DESCRIPTION

[0048] In order to better explain the present application, and to facilitate understanding, the present application is described in detail below with reference to the accompanying drawings, through specific embodiments.

[0049] The method for image position correction of SPECT and CT devices provided in the embodiments of the present application can fuse images of SPECT and CT devices developed by two different departments or manufacturers through correction of the bed and the images. Meanwhile, 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 solutions, exemplary embodiments of the present application will be described in more detail below with reference to the accompanying drawings. Although the exemplary embodiments of the present application are shown in the drawings, it should be understood that the present application 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, more thorough understanding of the present application and to fully convey the scope of the present application to those skilled in the art.

[0051] In a first aspect, with reference to Figure 1 The present embodiment provides a method for image position correction of SPECT and CT devices, comprising:

[0052] S1, a reference coordinate system is established, and the origin of the reference coordinate system is on the Z-axis with the center of the CT light plane and the center of the SPECT.

[0053] As Figure 2 The physical placement position diagram of the device is shown, and from the perspective of the human eye, the bed, the SPECT device and the CT device are sequentially arranged.

[0054] As Figure 3The object scanning schematic diagram is shown. When scanning SPECT, the detector acquires an image in a certain interval at one time, such as the black part in the schematic diagram, and then reconstructs to generate a tomographic image. When scanning CT, the device pushes the bed plate at a constant speed to reconstruct the object passing through the CT light plane to generate a tomographic image. Therefore, SPECT moves the bed to a fixed position, performs tomographic scanning and reconstruction, and can obtain a tomographic image of the target. CT needs to determine the moving range of the bed, and performs scanning to obtain the target image.

[0055] First, a reference coordinate system is set, because the SPECT / CT device scanning is mainly based on SPECT, and all standard coordinate systems take the SPECT device position as the reference coordinate. For example, Figure 4 The schematic diagram of the reference coordinate system is shown. From the direction of the bed to the device, 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, the scanning start position of the scanned object to the bed head distance Zs is determined based on the Z axis, and the scanning end position of the scanned object to the bed head distance Ze.

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

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

[0059] The object in the scanning schematic diagram, the start position to the bed head distance is Zs, the end position to the bed distance is Ze, the length from the beginning to the end is Dz=Ze-Zs. The expected image center range in the Z direction is (0, 0, Zs) to (0, 0, Ze). In actual scanning, the image ranges reconstructed by SPECT and CT on the object in the Z direction are from Zs to Ze, so that SPECT and CT can be correctly fused.

[0060] S3, the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system is determined in combination with Zs and Ze.

[0061] Different parameter SPECT images have different sizes, but the center positions of all SPECT images are located at the position of the center of the SPECT detector.

[0062] In combination with Figure 5The center of the scanned object is moved to the SPECT center position, and the distance of the movement is set as Zc, and the length of Zc is Zs plus the distance from the bed head to the SPECT center.

[0063] Optionally, the SPECT offset vector of the SPECT device coordinate system to the reference coordinate system is determined in combination with Zs and Ze, and the method comprises the following steps:

[0064] The reconstruction range R of the image is calculated according to the spacing*row in the DICOM Tag of the scanned image.

[0065] The center of the scanned object is moved to the SPECT center.

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

[0067] S4, the preliminary CT offset vector of the CT device coordinate system to the reference coordinate system is determined in combination with Zs and Ze.

[0068] Optionally, the preliminary CT offset vector of the CT image converted to the reference coordinate system is determined in combination with Zs and Ze, and the method comprises the following steps:

[0069] The coordinates (0, 0, Pct) of the CT light plane center in the reference coordinate system are determined according to the distance Dpc from the CT light plane to the SPECT detection center, wherein Pct=Dpc+Dz.

[0070] The scanned object located in the range [Zs, Ze] is moved to the CT scanning range according to Dpc;

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

[0072] The distance between the CT light plane and the SPECT detection center is measured physically, and the value of the distance is set as Dpc millimeters.

[0073] The object in the range of [Zs, Ze] is scanned by CT, and the object in the range is moved to the light plane range, and the distance of the object moving bed is calculated from [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 of the CT image converted to the reference coordinate system according to the SPECT offset vector and the correction offset vector.

[0076] Optionally, determining the final CT offset vector of the CT image converted to the reference coordinate system according to the preliminary CT offset vector and the correction offset vector comprises:

[0077] Adding the preliminary CT offset vector (0, 0, Vct) and the correction offset vector (Ax, Ay, Az) to obtain the final CT offset vector (Vcx, Vcy, Vcz), wherein Vcx=Ax, Vcy=Ay, and 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 comprises:

[0080] Adding the SPECT offset vector (0, 0, Vp) to all scanned SPECT images and adding the final CT offset vector (Vcx, Vcy, Vcz) to all scanned CT images to correct the SPECT image and the CT image in the same coordinate system, so as to realize position correction of the SPECT image and the CT image.

[0081] Adding the conversion vector (0, 0, Vp) to all scanned SPECT images and adding the conversion vector (Vcx, Vcy, Vcz) to all scanned CT images can realize that the SPECT tomographic image and the CT tomographic image are in the same coordinate system, and the scanning ranges of the two devices overlapped can be normally fused.

[0082] Optionally, the method further comprises:

[0083] Determining a PET offset vector according to the same steps as the SPECT, and performing position correction on the PET and SPECT devices or the PET / CT device according to the PET offset vector.

[0084] PET and SPECT devices are both to move the bed to the specified position, then collect a range of data and reconstruction to generate DICOM images, SPECT and PET position correction can use the same method. CT needs to scan when moving the bed, collect a range of data and reconstruction to generate DICOM images. If the combination is PET / CT device, only need to refer to the calculation method of SPECT can get the conversion vector of PET.

[0085] If it is a combination of PET / SPECT / CT three kinds of equipment, only need to refer to the calculation method of SPECT, plus the conversion vector of PET, can get the correction method of image position of three kinds of equipment combination.

[0086] The embodiment provides an image position correction method for SPECT and CT devices, which realizes fusion by defining a conversion vector of a SPECT image and a conversion vector of a CT image, and converting the SPECT and CT devices to the same reference coordinate system. The difference between the SPECT device and the CT device developed by different departments or manufacturers is solved. Even if the difference between different devices is large, the position correction can be realized through the method of the embodiment, and the method can be applied between multiple devices, ensures the accuracy of the fused image, improves the reliability of the fusion result, provides more accurate and comprehensive basis for doctors for diagnosis and treatment, and improves the precision and safety of treatment.

[0087] In a second aspect, the embodiment provides an image position correction system for SPECT and CT devices, comprising: a coordinate system establishing module, which establishes a reference coordinate system, the origin of the reference coordinate system being on the Z axis with the center of the CT light plane and the center of the SPECT; a first determining module, which determines the distance Zs from the scanning start position of a scanning object to the head of a bed and the distance Ze from the scanning end position of the scanning object to the head of the bed, taking the Z axis as a reference; a second determining module, which determines a SPECT offset vector from the SPECT device coordinate system to the reference coordinate system in combination with Zs and Ze; a third determining module, which 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 determining module, which performs an Alignment correction in the system correction on a scanning image to obtain a correction offset vector of the CT image relative to the SPECT image; a fourth determining module, which determines a final CT offset vector of the CT image converted to the reference coordinate system according to the preliminary CT offset vector and the correction offset vector; and a correction module, which 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. The image position correction system for SPECT and CT devices provided by the embodiment has all the technical effects of the image position correction method for SPECT and CT devices provided by the first aspect of the present application, and thus repeated description is omitted here.

[0088] In a third aspect, the embodiment provides a computer readable storage medium, which stores a computer program, the program being executed to implement the image position correction method for SPECT and CT devices provided by any one of the first aspect.

[0089] In a fourth aspect, the embodiment provides a storage device, which comprises a storage medium and a processor, the storage medium storing a computer program, the program being executed by the processor to implement the image position correction method for SPECT and CT devices provided by any one of the first aspect.

[0090] Those skilled in the art should understand that the embodiments of the present application can be provided as a method, a system or a computer program product. Therefore, the present application can adopt a completely hardware embodiment, a completely software embodiment, or an embodiment combining software and hardware aspects. Moreover, the present application can adopt 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, various modifications and changes can be made to the present application by those skilled in the art without departing from the spirit and scope of the present application. Accordingly, it is intended that the present application encompass all such modifications and changes as fall within the scope of the claims and their equivalents.

[0092] Although the embodiments of the present application have been shown and described above, it is to be understood that the above-described embodiments are merely exemplary and are not to be taken in a limiting sense, but the scope of the present application is not to be understood as limited to such exemplary embodiments. Therefore, it is intended that the present application encompass all modifications and changes as fall within the scope of the claims and their equivalents.

Claims

1. An image position correction method for a SPECT and CT device, characterized by, The application relates to a method for correcting the position of a CT and SPECT device, and belongs to the technical field of medical imaging. The method comprises the following steps: A reference coordinate system is established, and the origins of the reference coordinate system and the CT light plane center and the SPECT center are all on the Z axis; The distance Zs from the scanning object scanning start position to the bed head is determined with the Z axis as the reference, and the distance Ze from the scanning object scanning end position to the bed head is determined; The SPECT device coordinate system to the reference coordinate system SPECT offset vector is determined by combining Zs and Ze; The SPECT device coordinate system to the reference coordinate system SPECT offset vector is determined by combining Zs and Ze, which comprises the following steps: The image reconstruction range R is calculated according to the spacing*row in the DICOM Tag of the scanning image; The center of the scanning object is moved to the SPECT center; The image center position on the Z axis is obtained according to the ImagePosition in the DICOM Tag of the scanning image, and the SPECT tomographic image range on the Z axis is [Zz-Dz / 2, Zz+Dz / 2], wherein Dz=Ze-Zs, the SPECT device coordinate system to the reference coordinate system offset vector is (0, 0, Vp), wherein Vp=Zs-Zz+Dz / 2; The preliminary CT offset vector of the CT device coordinate system to the reference coordinate system is determined by combining Zs and Ze; The Alignment correction in the system correction is performed on the scanning image, and the correction offset vector of the CT image relative to the SPECT image is obtained; The final CT offset vector of the CT image conversion to the reference coordinate system is determined according to the preliminary CT offset vector and the correction offset vector; 2. The image position correction method for a SPECT and CT device according to claim 1, wherein, The positions of the SPECT and CT devices are corrected according to the SPECT offset vector and the final CT offset vector, so that the image fusion is performed. The preliminary CT offset vector of the CT image conversion to the reference coordinate system is determined by combining Zs and Ze, which comprises the following steps: The CT light plane center coordinate in the reference coordinate system is determined as (0, 0, Pct) according to the distance Dpc from the CT light plane to the SPECT detection center, wherein Pct=Dpc+Dz; The scanning object located in the range [Zs, Ze] is moved to the CT scanning light plane range according to Dpc; 3. The image position correction method for a SPECT and CT device according to claim 2, wherein, The scanning object located in the range [Zs, Ze] is moved to the CT scanning light plane range according to Dpc; The scanning object located in the range [Zs, Ze] is moved to the CT scanning light plane range according to Dpc; 4. The image position correction method for a SPECT and CT device according to claim 3, wherein, The CT image scanning range on the Z axis is [Zz2, Zz2+Dz] according to the scanning image center position on the Z axis obtained according to the ImagePosition in the DICOM Tag of the first CT image, and the preliminary offset vector of the CT device coordinate system to the reference coordinate system is (0, 0, Vct), wherein Vct=Zz2-Pct-Zs. The final CT offset vector of the CT image conversion to the reference coordinate system is determined according to the preliminary CT offset vector and the correction offset vector, which comprises the following steps: The final CT offset vector (Vcx, Vcy, Vcz) is obtained by adding the preliminary CT offset vector (0, 0, Vct) and the correction offset vector (Ax, Ay, Az), wherein Vcx=Ax, Vcy=Ay, and Vcz=Vct+Az. The positions of the SPECT image and the CT image are corrected according to the SPECT offset vector and the final CT offset vector, which comprises the following steps: All scanned SPECT images are added with a SPECT offset vector (0, 0, Vp), and all scanned CT images are added with a final CT offset vector (Vcx, Vcy, Vcz), so that the SPECT images and the CT images are registered in the same coordinate system, and the position correction of the SPECT images and the CT images is realized.

5. The image position correction method for a SPECT and CT device according to claim 4, characterized by, The method further comprises: The method further comprises:

6. An image position correction system for a SPECT and CT device, characterized by The method further comprises: The method further comprises: The coordinate system establishing module establishes a reference coordinate system, and the origin of the reference coordinate system is on the Z axis together with the center of the CT light plane and the center of the SPECT; The first determining 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; The second determining module determines the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system based on Zs and Ze; The second determining module determines the SPECT offset vector from the SPECT device coordinate system to the reference coordinate system based on Zs and Ze, which comprises: The reconstruction range R of the image is calculated according to the spacing*row in the DICOM Tag of the scanning image; The center of the scanned object is moved to the SPECT center; The position Zz of the image center on the Z axis is obtained according to the ImagePosition in the DICOM Tag of the scanning image, and the range of the SPECT tomographic image on the Z axis is [Zz-Dz / 2, Zz+Dz / 2], wherein Dz=Ze-Zs, and the offset vector from the SPECT device coordinate system to the reference coordinate system is (0, 0, Vp), wherein Vp=Zs-Zz+Dz / 2; The third determining module determines the preliminary CT offset vector from the CT device coordinate system to the reference coordinate system based on Zs and Ze; The correction offset vector determining module performs the Alignment correction in the system correction on the scanning image to obtain the correction offset vector of the CT image relative to the SPECT image; The fourth determining module determines the final CT offset vector of the CT image converted to the reference coordinate system based on the preliminary CT offset vector and the correction offset vector; 7. A computer-readable storage medium having stored thereon a computer program, characterized in that, The correction module performs the position correction of the SPECT and CT devices based on the SPECT offset vector and the final CT offset vector, so as to perform the image fusion.

8. A storage device comprising a storage medium and a processor, the storage medium storing a computer program, characterized in that, The computer program is executed by the processor to realize the image position correction method for the SPECT and CT devices according to any one of claims 1 to 5. The processor executes the computer program to realize the image position correction method for the SPECT and CT devices according to any one of claims 1 to 5.

Images