Scanning device, imaging system, method, storage medium and program product

Abstract

The present invention relates to the field of medical image technology, and specifically provides a scanning device, an imaging system, a method, a storage medium, and a program product. Within a preset DBT reconstruction angle range, the subject is rotated at a preset first speed and the subject is scanned to obtain first scanning data, the first scanning data is used for DBT reconstruction, the DBT reconstruction angle range includes the angle corresponding to the target projection position, outside the DBT reconstruction angle range, the subject is rotated at a speed higher than the first speed and the subject is scanned to obtain second scanning data, the second scanning data is used to form CT scanning data in combination with the first scanning data, and the minimum angle interval between multiple projection images formed by the second scanning data is greater than the angle interval between multiple projection images formed by the first scanning data. According to the present invention, imaging in both CT and DBT modes can be performed using the scanning data obtained by a single round of scanning.

Description

Technical Field

[0001] The present invention relates to the field of medical imaging technology, and in particular to a scanning device, an imaging system, a scanning method, an imaging method, a readable storage medium and a computer program product. Background Art

[0002] DBT (Digital Breast Tomosynthesis) is a method of scanning and imaging the breast. It takes several images within a certain angle range and reconstructs them to obtain a tomographic image. It can be used to detect breast lesions and find hidden tiny lesions. The equipment is easy and quick to operate. Breast CT is also a method of scanning and imaging the breast. It scans and reconstructs the breast to obtain a complete three-dimensional image of the breast. It can also be used to examine breast lesions, and the image display is more comprehensive.

[0003] Breast CT and DBT have their own characteristics and are both commonly used examination methods for breast examination. However, breast CT equipment and DBT equipment are independent devices. If you need to obtain both breast CT images and DBT images of the subject, you need to scan the subject separately with breast CT equipment and DBT equipment, which is high in medical cost and time cost. Summary of the invention

[0004] In order to solve at least one of the above technical problems, the present invention provides a scanning device, an imaging system, a scanning method, an imaging method, a readable storage medium and a computer program product.

[0005] A first aspect of the present invention provides a scanning device, comprising: a scanning component, a processor and a memory, wherein the scanning component comprises a radiation source and a detector arranged relatively to each other, and the memory stores a computer program, and when the computer program is executed by the processor, the processor controls the scanning component to perform the following process: within a preset DBT reconstruction angle range, rotating around a subject at a preset first speed and scanning the subject to obtain first scanning data, wherein the first scanning data is used for DBT reconstruction, and the DBT reconstruction angle range includes the angle corresponding to the target projection position; and outside the DBT reconstruction angle range, rotating around the subject at a speed higher than the first speed and scanning the subject to obtain second scanning data, wherein the second scanning data is used to form CT scanning data in combination with the first scanning data, and the minimum angular interval between multiple projection images formed by the second scanning data is greater than the angular interval between multiple projection images formed by the first scanning data.

[0006] According to some embodiments of the present invention, rotating around a subject at a speed higher than the first speed and scanning the subject includes: during the start process of scanning, rotating around the subject at a preset second speed from a starting position and scanning the subject to obtain third scanning data, wherein the second speed is higher than the first speed.

[0007] According to some embodiments of the present invention, the starting position is outside a preset target angle range, the DBT reconstruction angle range is truly included in the target angle range, and one target angle range only includes one DBT reconstruction angle range.

[0008] According to some embodiments of the present invention, the method of rotating around a subject at a speed higher than the first speed and scanning the subject comprises: when a deceleration condition is met, decelerating from a speed higher than the first speed to the first speed, and scanning the subject to obtain fourth scanning data, and the scanning component enters the DBT reconstruction angle range at the first speed after completing the deceleration, and the deceleration condition comprises: the scanning component rotates to reach a preset first position.

[0009] According to some embodiments of the invention, the first position is outside the DBT reconstruction angle range.

[0010] According to some embodiments of the present invention, rotating around a subject at a speed higher than the first speed and scanning the subject includes: when a speed increase condition is met, increasing the speed from the first speed to a speed higher than the first speed, and scanning the subject to obtain fifth scanning data, and the speed increase condition includes: the scanning component rotates until it begins to leave the DBT reconstruction angle range.

[0011] According to some embodiments of the present invention, the starting speed of deceleration when the deceleration condition is met and the deceleration begins is equal to the ending speed of acceleration when the acceleration is completed.

[0012] According to some embodiments of the present invention, the method comprises rotating around the object at a speed higher than the first speed and scanning the object, comprising: when the speed is increased from the first speed to a speed higher than the first speed, maintaining a speed higher than the first speed while scanning the object to obtain sixth scanning data, until a deceleration condition is met or the scanning of all the angles to be scanned is completed.

[0013] According to some embodiments of the present invention, an acquisition resolution when the object is scanned at a speed higher than the first speed is smaller than an acquisition resolution when the object is scanned at the first speed.

[0014] According to some embodiments of the present invention, an acquisition frame rate when scanning the object at a speed higher than the first speed is greater than an acquisition frame rate when scanning the object at the first speed.

[0015] According to some embodiments of the present invention, if the detector is offset relative to the radiation source, or the scanning component rotates around the object in a spiral scanning manner during the scanning process, then: the angle of rotation of the scanning component from the beginning of the scan to the end of the scan is greater than or equal to 360°, and two DBT reconstruction angle ranges are provided, and the two DBT reconstruction angle ranges are symmetrically arranged relative to the rotation center of the scanning component.

[0016] According to some embodiments of the present invention, the target projection position includes a cranio-caudal position.

[0017] According to some embodiments of the present invention, the angle corresponding to the target projection position is the central angle of the DBT reconstruction angle range.

[0018] According to some embodiments of the invention, the DBT reconstruction angle range is less than or equal to 60°.

[0019] A second aspect of the present invention proposes an imaging system, comprising: a scanning device as described in any of the above-mentioned embodiments; an interpolation module, used to interpolate the first scanning data and part of the second scanning data according to multiple CT scanning angles within a first angle range to obtain interpolated images of the multiple CT scanning angles, wherein the first angle range includes the DBT reconstruction angle range and the angle range passed by the scanning component of the scanning device during the speed change process, and the speed change process includes a speed reduction process and a speed increase process; and a reconstruction module, used to perform DBT reconstruction based on the first scanning data to obtain a DBT image, and perform CT reconstruction based on the interpolated image and the scanning data corresponding to angles outside the first angle range in the second scanning data to obtain a breast CT image.

[0020] According to some embodiments of the present invention, if the detector of the scanning component is offset relative to the radiation source of the scanning component, or the scanning component rotates around the object in a spiral scanning manner during the scanning process, the reconstruction module performs DBT reconstruction on multiple first scanning data to obtain a DBT image, and the multiple first scanning data are data obtained by scanning when the scanning component rotates multiple times through the DBT reconstruction angle range.

[0021] A third aspect of the present invention proposes a scanning method, which is applied to a scanning component, and the scanning method includes: within a preset DBT reconstruction angle range, rotating around a subject at a preset first speed and scanning the subject to obtain first scanning data, wherein the first scanning data is used for DBT reconstruction, and the DBT reconstruction angle range includes the angle corresponding to the target projection position; and outside the DBT reconstruction angle range, rotating around the subject at a speed higher than the first speed and scanning the subject to obtain second scanning data, wherein the second scanning data is used to form CT scanning data in combination with the first scanning data, and the minimum angular interval between multiple projection images formed by the second scanning data is greater than the angular interval between multiple projection images formed by the first scanning data.

[0022] A fourth aspect of the present invention provides an imaging method, comprising: scanning a subject by the scanning method described in any of the above-mentioned embodiments to obtain first scanning data and second scanning data; interpolating the first scanning data and part of the second scanning data according to multiple CT scanning angles within a first angle range to obtain interpolated images of the multiple CT scanning angles, wherein the first angle range includes the DBT reconstruction angle range and the angle range passed by the scanning component of the scanning device during the speed change process, and the speed change process includes a speed reduction process and a speed increase process; and performing DBT reconstruction based on the first scanning data to obtain a DBT image, and performing CT reconstruction based on the interpolated image and the scanning data corresponding to angles outside the first angle range in the second scanning data to obtain a breast CT image.

[0023] A fifth aspect of the present invention provides a readable storage medium, in which a computer program is stored. When the computer program is executed by a processor, it is used to implement the method described in any of the above embodiments.

[0024] A sixth aspect of the present invention provides a computer program product, which includes a computer program. When the computer program is executed by a processor, it is used to implement at least the method described in any of the above embodiments. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] The accompanying drawings illustrate exemplary embodiments of the present invention and together with the description serve to explain the principles of the present invention. These drawings are included to provide a further understanding of the present invention and are incorporated in and constitute a part of this specification.

[0026] Figure 1 A schematic diagram showing application scenarios of scanning devices according to some embodiments of the present invention is shown.

[0027] Figure 2A flowchart showing a scanning device according to some embodiments of the present invention scanning a subject is shown.

[0028] Figure 3 A schematic top view showing the trajectory and angle of the scanning device during the scanning process according to some embodiments of the present invention is shown.

[0029] Figure 4 A schematic diagram showing the angular spacing of a portion of projection images obtained by a scanning device in some embodiments of the present invention is shown.

[0030] Figure 5 A flow chart showing the generation of DBT images and CT images by an imaging system according to some embodiments of the present invention is shown.

[0031] Figure 6 A schematic diagram showing the angle spacing of projection images used for CT reconstruction after interpolation in some embodiments of the present invention is shown.

[0032] Figure 7 A schematic diagram of a scanning device using a hardware implementation of a processing system according to some embodiments of the present invention is shown.

[0033] Figure 8 A schematic diagram of an imaging system using a hardware implementation of a processing system according to some embodiments of the present invention is shown.

[0034] Fig. 9 A schematic flow chart of a scanning method according to some embodiments of the present invention is shown.

[0035] Fig.10 A schematic flow chart of an imaging method according to some embodiments of the present invention is shown. DETAILED DESCRIPTION

[0036] The present invention will be further described in detail below in conjunction with the accompanying drawings and implementations. It is to be understood that the specific implementations described herein are only used to explain the relevant content, rather than to limit the present invention. It is also necessary to explain that, for ease of description, only the parts related to the present invention are shown in the accompanying drawings.

[0037] It should be noted that, in the absence of conflict, the embodiments of the present invention and the features in the embodiments can be combined with each other. The technical solution of the present invention will be described in detail below with reference to the accompanying drawings and in combination with the embodiments.

[0038] Unless otherwise specified, the exemplary embodiments / embodiments shown will be understood as exemplary features that provide various details of some ways in which the technical concept of the present invention can be implemented in practice. Therefore, unless otherwise specified, the features of the various embodiments / embodiments can be combined, separated, interchanged and / or rearranged without departing from the technical concept of the present invention.

[0039] The terms used herein are for the purpose of describing specific embodiments, rather than being restrictive. As used herein, unless the context clearly indicates otherwise, the singular forms "one (kind, person)" and "said (the)" are also intended to include plural forms. In addition, when the terms "comprise" and / or "include" and their variations are used in this specification, it is explained that there are stated features, integral bodies, steps, operations, parts, assemblies and / or their groups, but it is not excluded that there are or add one or more other features, integral bodies, steps, operations, parts, assemblies and / or their groups. It should also be noted that, as used herein, the terms "substantially", "approximately" and other similar terms are used as approximate terms and not as degree terms, so that they are used to explain the inherent deviations of the measured values, calculated values ​​and / or provided values ​​that will be recognized by those of ordinary skill in the art.

[0040] Breast CT and DBT (Digital Breast Tomosynthesis) are both means of three-dimensional reconstruction of the human breast. The scanning angle range of CT scanning is greater than 180°, and the reconstructed CT image can more completely display the internal tissue and structure of the breast; the scanning angle range of DBT scanning is smaller, which is an incomplete three-dimensional reconstruction, and the resulting tomographic image is thinner than the CT image.

[0041] In the process of performing breast scans on the human body to observe the tissues in the breast to identify lesions, sometimes it is necessary to perform a breast CT scan and read the breast CT images, and also to perform a DBT scan and read the DBT images, and to combine the images of both to identify lesions. Both the breast CT scanning device and the DBT scanning device are independent devices. The patient needs to undergo a CT scan and a DBT scan respectively. Only through these two scans can the CT image and the DBT image be obtained. This requires the preparation of a CT scanning device and a DBT scanning device at the same time to meet the scanning requirements. The equipment hardware cost is high, and performing two scans makes the scanning efficiency low, while also increasing the radiation dose received by the patient.

[0042] Figure 1The schematic diagram of the application scenario of the scanning device of some embodiments of the present invention is shown. In this application scenario, a scanning bed 10, a CBCT (cone beam CT) scanning assembly and a control end 30 may be included. The CBCT scanning assembly includes a radiation source 21 and a detector 22, both of which are fixedly mounted on a rotating table 23, and the radiation source 21 and the detector 22 are arranged relative to each other, and the radiation emitted by the radiation source 21 can pass through the scanning position 11 and reach the detection surface of the detector 22. The detector 22 can be offset relative to the radiation source 21, or it can be upright. The rotating table 23 is installed on the base 24. The radiation source 21, the detector 22 and the rotating table 23 all communicate and transmit data with the control end 30 in a wired or wireless manner. The control end 30 includes a processor and a memory. The rotating table 23 can be controlled by the control end 30 to rotate at a set speed and angle, driving the radiation source 21 and the detector 22 to rotate, and the radiation source 21 and the detector 22 can be controlled by the control end 30 to scan at a set frame rate. The rotating stage 23 can rotate in a single horizontal plane or slowly rise while rotating, that is, spiral rotation. Scanning under spiral rotation is called spiral scanning. Figure 1 The supporting structure and other components of the scanning bed 10 are not shown. Figure 1 The shapes and structures of the scanning bed 10, CBCT scanning assembly and control terminal 30 shown in the figure should not be understood as limiting the scope of protection of the present invention. In the present invention, the "control terminal" can be different types of electronic devices, for example, the terminal can be a mobile phone, a tablet computer, a laptop computer, a desktop computer or a self-service machine.

[0043] Figure 2 A flowchart showing a scanning device according to some embodiments of the present invention scanning a subject is shown. Figure 2 The detailed description is for a clearer understanding of the technical solution of the present invention and should not be considered as a limitation of the protection scope of the present invention. In the process of implementing the technical idea of ​​the present invention, one or some steps may be omitted, or other alternatives may be adopted.

[0044] See also Figure 2 The process of generating CT images and DBT images by the imaging system mainly includes a scanning stage and an imaging stage. The scanning stage is performed first. Before starting the scan, the patient is positioned first. During the scan, the patient lies on the scanning bed, with the head located at the A end of the scanning bed 10 and the feet located at the B end of the scanning bed 10. The breast of the subject naturally droops through the slot and is not located at the scanning position 11 shown by the dotted line. After the patient completes the positioning, the scanning process is started.

[0045] Figure 3 FIG. 1 is a schematic top view showing the trajectory and angle of the scanning device during the scanning process in some embodiments of the present invention. Figure 3, S is the scanning starting position of the radiation source 21 or the detector 22. Position S can be a fixed starting position, and each scan can be rotated from position S; position S can also be the stop position after the last scan is completed. Figure 3 In the example, the radiation source 21 is currently located at position S, and the processor controls the rotation of the rotating table so that the radiation source 21 starts to rotate clockwise along the arrow direction at point S, and the detector 22 also starts to rotate clockwise at the same speed on the opposite side. It can be understood that the rotation direction can also be counterclockwise, and the rotation direction can be set according to the working conditions.

[0046] R1 is the first speed change angle range, R2 is the DBT reconstruction angle range, and R3 is the second speed change angle range. When the source 21 and the detector 22 rotate clockwise to scan the subject, R1 is the speed reduction angle range, R2 is the uniform speed angle range, and R3 is the speed increase angle range. R0 is the target angle range, and R0 includes R2 and a speed change segment adjacent to R2, and the speed change segment included in R0 is close to the direction of the source 21. Figure 3 , the radiation source 21 rotates from one side clockwise from position S, so the speed change section included in R0 is R1. The range values ​​of R1, R2, R3 and other angle ranges can be pre-set, wherein the range of R2 can include a pre-set projection position, i.e., the target projection position. The target projection position can describe the patient's position during scanning. When the target projection position is determined, the position of R2 in the full scanning angle (360°) can be pre-set based on the target projection position. Since the motor parameters of the rotating table can be pre-set, the positions of R1 and R3 on both sides of R2 within the full scanning angle range can also be pre-set. The same is true for other angle ranges outside R1 and R3. All operating parameters such as angles, speeds, frame rates, doses, etc. of the overall scanning process from the beginning to the end can be pre-set, and the scanning device can be controlled to operate according to the pre-set parameters.

[0047] Figure 3 The head-to-tail position (CC position) is used as the target projection position. When the patient's head is located at the A end and the foot is located at the B end, the angle when projecting from the head to the foot and the angle when projecting from the foot to the head both belong to the angle corresponding to the target projection position, that is, there are two CC positions, and point P1 and point P2 represent the two CC positions respectively. When projecting in the target projection position, the radiation source 21 is located at point P1 or point P2. There are two symmetrically set DBT reconstruction angle ranges R2 within the full scanning angle range, and points P1 and P2 can be located at the center angles of the two DBT reconstruction angle ranges R2 respectively.

[0048] The scan data collected within the angle range R2 is the first scan data, and the first scan data is used to form a DBT projection map to reconstruct a DBT image. The R2 angle range can be slightly lower than 60°. The scan data collected outside the angle range R2 (including R1, R3 and other angle ranges) is the second scan data, and the angle range corresponding to the second scan data is greater than R2. The second scan data is processed together with the first scan data to obtain a CT projection map, thereby reconstructing a CT image.

[0049] Position S is outside the DBT reconstruction angle range. As the source 21 and the detector 22 start and begin to rotate, the rotation speed of the source 21 and the detector 22 is quickly increased to the second speed v2, and then the source 21 and the detector 22 rotate at a uniform speed at the second speed v2 and scan the subject at the same time until they reach the first position P3 located on the boundary of the angle range R0, which is also called the deceleration starting position. Since the parameters such as the rotation speed are preset, the way to judge the arrival point P3 can be through the number of electronic pulses or time parameters. The DBT reconstruction angle range R2 and the first speed change angle range R1 form the target angle range R0. The source 21 enters R0 from one side of R0, which is the side where R1 is located in R0. The source 21 and the detector 22 rotate around the subject from position S until the rotation position reaches the first position P3. During the process, data acquisition is performed at the first acquisition frame rate f1 to obtain the third scanning data (projection image). The acquisition frame rate refers to the number of images acquired per unit time. The second speed v2 may be 1 degree rotation per second, and the frame rate f1 may be 1 image captured per second, which is equivalent to capturing 1 projection image per rotation of 1 degree, and the resolution of the captured image may be 640*640.

[0050] When the source 21 reaches the first position P3, the processor starts to reduce the rotation speed of the source 21 and the detector 22 by controlling the rotating table, so that the rotation speed is reduced from the second speed v2 to the first speed v1. The angle range rotated during this deceleration is the first speed change angle range R1. When the rotation speed drops to v1, the source 21 reaches the other side boundary of R1, and the process of this deceleration rotation ends. During the deceleration process, the subject is continuously scanned, and the first acquisition frame rate f1 can continue to be used for data acquisition to obtain the fourth scanning data. The first speed v1 can be 1 degree every 4 seconds, and the resolution of the acquired image can be 640*640. Due to the deceleration process, the angular spacing between different acquired images is different, and the number of acquired projection images will gradually increase with every 1 degree of rotation.

[0051] When the source 21 reaches one side boundary of R2, that is, when the source 21 leaves R1 and begins to enter the angle range of R2, the processor starts to control the rotating stage to maintain the rotation speed of the source 21 and the detector 22, so that the source 21 and the detector 22 rotate at a uniform speed at the first speed v1. The angle range rotated during this uniform speed is the DBT reconstruction angle range R2. When the source 21 reaches the other side boundary of R2, that is, when the source 21 begins to leave R2, the uniform rotation process ends. During the uniform rotation of the angle range R2 and scanning of the subject, the first acquisition frame rate f1 can be used to collect data to obtain the first scanning data (projection image). The first scanning data can be used by the reconstruction module for DBT reconstruction to generate a DBT image. The first speed v1 is 1 degree rotation every 4 seconds, which is equivalent to collecting 4 projection images for every 1 degree rotation, and the resolution of the collected image can be 640*640. The decrease in rotation speed and the unchanged frame rate allow more images to be collected within a unit angle, thereby meeting the requirements for the angle range and the number of images during DBT reconstruction.

[0052] When the source 21 reaches one side boundary of R3, that is, when the source 21 leaves R0 and begins to enter the angle range of R3, the processor begins to increase the rotation speed of the source 21 and the detector 22 by controlling the rotating table, so that the rotation speed increases from the first speed v1 to the second speed v2. The angle range rotated during this speed increase is the second speed change angle range R3. When the speed increases to v2, the source 21 reaches the second position P4 located on the other side boundary of R3. P4 is also called the end of the speed increase, and the process of this speed increase rotation ends. During the speed increase process, the subject is continuously scanned, and the first acquisition frame rate f1 can continue to be used for data acquisition to obtain the fifth scanning data. The second speed v2 is 1 degree rotation per 1 second, and the resolution of the acquired image can be 640*640. Because it is in the speed increase process, the angular spacing between different acquired images is different. For every 1 degree rotation, the number of acquired projection images will gradually decrease.

[0053] When leaving the second position P4, the processor starts to control the rotating table to maintain the rotation speed of the radiation source 21 and the detector 22, so that the radiation source 21 and the detector 22 rotate at a uniform speed v2, and continue to scan the subject in the process, and the acquisition frame rate can continue to use the first acquisition frame rate f1. The angle range after leaving R3 is not shown in the figure. Since the angle range corresponding to all the angles to be scanned in one round of scanning will be greater than 180°, at least one complete angle range of R1, R2 and R3 will be included in one round of scanning. If the angle range corresponding to all the angles to be scanned in this round is 360°, then two complete angle ranges of R1, R2 and R3 will be included in this round of scanning, Figure 3The angle range mark on the side where the A end is located is not shown. After passing the first R3, the radiation source 21 and the detector 22 will maintain the second speed v2 and rotate at a uniform speed until reaching the second R1 boundary, and then start to decelerate to the first speed v1, and maintain the first speed v1 to rotate through the second DBT reconstruction angle range R2, and then start to increase the speed to the second speed v2, and maintain the second speed v2 to rotate. During the uniform speed and variable speed process, the subject will be scanned at the frame rate f1 until the scanning of all the angles to be scanned is completed, and the scanning data of all the angles to be scanned are obtained.

[0054] Figure 4 FIG. 1 is a schematic diagram showing the angular spacing of a portion of the projection images obtained by the scanning device of some embodiments of the present invention. Figure 4 , where the solid line passing through the rotation center O represents the projection image. Since the rotation speed of the source 21 and the detector 22 will change during a single round of scanning, the projection image obtained after completing a round of scanning is a sequence of projection images with non-uniform angle spacing when the acquisition frame rate remains unchanged. Figure 4 Among all the solid lines shown in , the angular spacings of adjacent solid lines are not exactly the same. Among them, the projection image sequence formed by the projection images obtained within the DBT reconstruction angle range R2 is a projection image with equal angular spacing, and the spacing between the projection images is small, corresponding to a uniform rotation at a lower first speed v1. The projection image sequence formed by the projection images obtained within the ranges of R1 and R3 is a projection image with non-equal angular spacing, Figure 4 The figure shows that the spacing between the solid lines in R1 and R3 gradually changes, corresponding to the speed change during the deceleration and acceleration process. Within the angular range between the previous R3 and R1 and the angular range between the current R3 and the next R1, the sequence of projection images formed by the obtained projection images is a projection image with equal angular spacing, and the spacing between the projection images is large, corresponding to a uniform rotation at a higher second speed v2. It can be understood that Figure 4 The solid line spacing in is only an example and is not intended to limit the angular spacing between projected images.

[0055] Figure 5 FIG. 1 is a flow chart showing a method for generating DBT images and CT images by an imaging system according to some embodiments of the present invention. Figure 5 After obtaining the scan data at all the scan angles to be scanned, the scan data can be processed to obtain DBT scan data suitable for DBT reconstruction and CT scan data suitable for CT reconstruction. The first scan data collected within the DBT reconstruction angle range R2 can be used as DBT scan data, and DBT scan data is obtained after DBT reconstruction. The CT scan data needs to first interpolate a part of the existing scan data, and then obtain the CT scan data based on the interpolated image and the existing part of the scan data, and obtain the CT image after CT reconstruction through the FBP algorithm.

[0056] The scanning data corresponds to the projected image, and the scanning angle range of a single round of scanning is 360° as an example. After completing a round of scanning, the fourth scanning data of the angle range R1, the first scanning data of the angle range R2, the fifth scanning data of the angle range R3, and the scanning data between R3 and the next R1 are obtained. The scanning data between R3 and the next R1 can be called the sixth scanning data. The set of the fourth scanning data, the first scanning data and the fifth scanning data can be called the scanning data to be interpolated. Since the scanning angle range is 360°, there are two copies of the scanning data to be interpolated and the sixth scanning data, and the two scanning data correspond to two symmetrical angle ranges respectively. Figure 4 Part of the sixth scan data is shown in FIG. 1 , wherein the solid line outside R1 represents a part of one copy of the sixth scan data, and the solid line outside R3 represents a part of another copy of the sixth scan data.

[0057] The scanning data of the full angle range formed by the above-mentioned scanning data to be interpolated and the sixth scanning data corresponds to the projection image of non-uniform angle intervals, such as Figure 4 As shown in . The angular spacing between projection images required for CT reconstruction is lower than the angular spacing between projection images required for DBT reconstruction. Therefore, the angular spacing corresponding to the sixth scanning data can be used as a reference, and the interpolated scanning data can be interpolated according to the angular spacing between the sixth scanning data. New projection image data are generated between two projection images of different scanning angles in the scanning data to be interpolated by interpolation. The scanning angle corresponding to the new projection image data does not belong to the scanning angle at which the source 21 and the detector 22 perform image acquisition during the scanning process. Thus, projection image data with the same angular spacing as the scanning angle of the sixth scanning data is formed in the angle range R1, R2 and R3 by interpolation. Linear interpolation can be used as the interpolation method.

[0058] Figure 6 FIG. 1 is a schematic diagram showing the angle spacing of projection images obtained after interpolation for CT reconstruction in some embodiments of the present invention. Figure 6 , the solid line passing through the rotation center represents the projection corresponding to the sixth scan data, and the dotted line passing through the rotation center represents the projection obtained after interpolation. Figure 4 It can be seen that the angle corresponding to the dotted line is Figure 4There is no corresponding solid line. The angular spacing between the solid line and the dotted line is the same, thus forming a projection image with an equal angular spacing within a 360° angular range. The interpolated image (projection image) obtained by interpolation and the sixth scan data are subjected to CT reconstruction according to the FBP algorithm to obtain a CT image. Thus, the technology of fusing breast CT and DBT scans is realized, and imaging in two modes, CT and DBT, can be performed on the scan data obtained through a single-round scan, thereby obtaining breast CT images and DBT images respectively, and improving the scan efficiency and imaging efficiency.

[0059] In another embodiment, the image resolution r2 during scanning within the DBT reconstruction angular range R2 is greater than the image resolution r1 during scanning within other angular ranges, and the number of images acquired per unit angle within the DBT reconstruction angular range R2 is less than the number of images acquired per unit angle outside the DBT reconstruction angular range R2. For example, when the radiation source 21 and the detector 22 rotate at a constant speed v2, the acquisition frame rate of the detector 22 during scanning is the first acquisition frame rate f1, and the image resolution is the first image resolution r1, where f1 is 1 image acquired per second, r1 is 640*640, and v2 is 1 degree of rotation per second, that is, 640*640 pixel data are acquired per second. When the radiation source 21 and the detector 22 rotate at a constant speed v1, the acquisition frame rate of the detector 22 during scanning is the second acquisition frame rate f2, and the image resolution is the second image resolution r2, where f2 is 1 image acquired per 2 seconds, the second image resolution r1 is 1280*1280, and the second speed v1 is 1 degree of rotation per 4 seconds, that is, 2*1280*1280 pixel data are acquired per 2 seconds.

[0060] The number of images acquired per unit angle within the range of R2 is 1 image / degree, and the number of images acquired per unit angle outside the range of R2 is 2 images / degree. This makes the projection image sequence formed by all the scan data acquired within the angular ranges of R2 and outside R2 a non-equiangular spacing image sequence. And because f2 < f1, the given time for acquiring a unit number of images within the range of R2 is more than the given time for acquiring a unit number of images outside the range of R2. Therefore, the image resolution can be increased during image acquisition within the range of R2, and the extra time can be used for more data acquisition, thereby improving the image quality and image effect of the DBT image.

[0061] In another embodiment, the image resolution r2 during scanning within the DBT reconstruction angle range R2 is greater than the image resolution r1 during scanning within other angle ranges, and the number of images acquired per unit angle within the DBT reconstruction angle range R2 is equal to the number of images acquired per unit angle outside the DBT reconstruction angle range R2. For example, when the radiation source 21 and the detector 22 rotate at a constant speed with a second speed v2, the acquisition frame rate of the detector 22 during scanning is a first acquisition frame rate f1, and the image resolution is a first image resolution r1, where f1 is 1 image acquired per second, r1 is 640*640, and v2 is 1 degree of rotation per second, that is, 640*640 pixel data are acquired per second. When the radiation source 21 and the detector 22 rotate at a constant speed with a first speed v1, the acquisition frame rate of the detector 22 during scanning is a third acquisition frame rate f3, and the image resolution is a second image resolution r2, where f3 is 1 image acquired per 4 seconds, the second image resolution r1 is 1280*1280, and the second speed v1 is 1 degree of rotation per 4 seconds, that is, 1280*1280 pixel data are acquired per 4 seconds.

[0062] The number of images acquired per unit angle within the range of R2 is 1 image / degree, and the number of images acquired per unit angle outside the range of R2 is also 1 image / degree. This makes the projection map sequence formed by all the scan data acquired within the angle ranges of R2 and outside R2 an image sequence with equal angular spacing. And since f3 < f1, the given time for acquiring a unit number of images within the range of R2 is more than the given time for acquiring a unit number of images outside the range of R2. Therefore, when image acquisition is performed within the range of R2, the image resolution can also be increased, and the extra time can be used for more data acquisition, thereby improving the image quality and image effect of the DBT image. It can be understood that since an image sequence with equal angular spacing is directly obtained, interpolation is not required. Instead, the projection maps acquired within the range of R2 can be downsampled to obtain images of 640*640, so that the resolution of all the scan data is consistent. Then, CT reconstruction is performed using all the scan data obtained in this round of scanning to obtain a CT image.

[0063] Figure 7 The schematic diagram of a scanning device adopting a hardware implementation manner of a processing system according to some embodiments of the present invention is shown. Refer to Figure 7The scanning device 1000 provided by the present invention includes a processor 1100, a memory 1200 and a scanning component 1300. The processor 1100 may be a central processing unit (CPU). The processor 1100 may also be other general-purpose processors, digital signal processors (DSP), application-specific integrated circuits (ASIC), field-programmable gate arrays (FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components and other chips, or a combination of the above chips.

[0064] The hardware structure of the device 1000 can be implemented using a bus architecture. The bus architecture can include any number of interconnecting buses and bridges, depending on the specific application and overall design constraints of the hardware. The bus 1400 connects various circuits including one or more processors 1100, memory 1200, and / or hardware modules together. The bus 1400 can also connect various other circuits 1500 such as peripherals, voltage regulators, power management circuits, external antennas, etc.

[0065] The bus 1400 may be an Industry Standard Architecture (ISA) bus, a Peripheral Component Interconnect (PCI) bus, or an Extended Industry Standard Component (EISA) bus, etc. A bus may be divided into an address bus, a data bus, a control bus, etc. For ease of representation, only one connecting line is used in the figure, but it does not mean that there is only one bus or one type of bus.

[0066] The memory 1200 can be used as a non-transitory computer-readable storage medium, and can be used to store non-transitory software programs, non-transitory computer executable programs and modules, such as program instructions of the computer program in the embodiment of the present invention. The processor 1100 executes various functional applications and data processing of the scanning device 1000 by running the non-transitory software programs, instructions and modules stored in the memory 1200, thereby realizing scanning of the subject.

[0067] The memory 1200 may include a program storage area and a data storage area, wherein the program storage area may store an operating system and an application required by at least one function; the data storage area may store data created by the processor 1100, such as parameter configurations of each structure in the scanning component 1300, collected scanning data, reconstructed images, etc. In addition, the memory 1200 may include a high-speed random access memory, and may also include a non-transitory memory, such as at least one disk storage device, a flash memory device, or other non-transitory solid-state storage device. In some embodiments, the memory 1200 may optionally include a memory remotely arranged relative to the processor 1100, and these remote memories may be connected to the processor 1100 via a network. Examples of the above-mentioned network include, but are not limited to, the Internet, an intranet, a local area network, a mobile communication network, and combinations thereof.

[0068] The scanning assembly 1300 may include a radiation source and a detector, which are arranged facing each other. The radiation source and the detector may be mounted on a rotating platform, which is controlled by the processor 1100 to rotate.

[0069] The memory 1200 stores a computer program. When the computer program is executed by the processor 1100, the processor 1100 can execute the following steps to control the scanning component 1300 to operate so as to implement the scanning method.

[0070] S110, within a preset DBT reconstruction angle range, rotate around the subject at a preset first speed and scan the subject to obtain first scan data. The first scan data is used for DBT reconstruction, and the DBT reconstruction angle range includes the angle corresponding to the target projection position. Step S110 can be implemented by the first scan control module 1002.

[0071] S120, outside the DBT reconstruction angle range, rotating around the object at a speed higher than the first speed and scanning the object to obtain second scan data. The second scan data is used to form CT scan data in combination with the first scan data, and the minimum angle interval between the multiple projections formed by the second scan data is greater than the angle interval between the multiple projections formed by the first scan data. Step S110 can be implemented by the second scan control module 1004.

[0072] The scanning device proposed in the embodiment of the present invention scans at a relatively low speed within the angle range suitable for DBT scanning to obtain a DBT projection image sequence corresponding to a partial scanning angle with a relatively small angular spacing therebetween; and scans at a relatively high speed within the angle range outside the angle range suitable for DBT scanning to obtain a projection image sequence with a relatively large angular spacing therebetween. Combining the projection image sequence with a relatively large angular spacing with the DBT projection image sequence can obtain a CT projection image sequence corresponding to the full scanning angle, thereby achieving two scanning mode projection image sequences through a single round of scanning, thereby improving the scanning efficiency compared to performing DBT scanning alone and CT scanning alone.

[0073] See also Figure 1 , the subject is in the scanning position, the body axis and the line between end A and end B roughly coincide, the human foot can correspond to end B, the head can correspond to end A. The DBT reconstruction angle range and position are pre-set, and can be set according to the target projection position. The target projection position can include the head-tail position (CC position), from which the breast can be observed at a wider angle, thereby meeting the requirements for image quality and effect of the desired observation area. At this time, there are two CC positions within the 360° range, such as Figure 3 As shown, point P1 is the CC position corresponding to the foot, and point P2 is the CC position corresponding to the head. The DBT reconstruction angle range R2 is set according to the positions of points P1 and P2. Within the range of 360°, the number of DBT reconstruction angle ranges can be the same as the number of CC positions. Each R2 contains a CC position, such as Figure 3 R2 in the figure includes point P1, and the DBT reconstruction angle range corresponding to point P2 is not shown in the figure.

[0074] The angle corresponding to the target projection position can be the center angle of the DBT reconstruction angle range, that is, point P1 can be located at the center of R2. Since DBT scanning is a scan at a local angle, the DBT reconstruction angle range can be less than or equal to 60°, for example, 30°≤R2≤60°. And since the scanning density (the number of images obtained per unit angle) of DBT scanning is high, the processor 1100 uses a lower first speed v1 to control the rotation of the scanning component 1300 within the R2 range, and uses a speed higher than v1 to control the rotation of the scanning component 1300 outside the R2 range, which can not only ensure the requirements for DBT scanning density within the R2 range, but also ensure the requirements for CT scanning density outside the R2 range, and at the same time ensure that the efficiency of a single round of scanning can meet the requirements.

[0075] The first scanning frame rate f1 is used to scan and acquire images at the same time at a uniform speed v1 within the DBT reconstruction angle range. The first acquisition frame rate f1 can meet the DBT scanning density requirements. The angle spacing between the projection images corresponding to the first scanning data obtained is equal, and can be directly used as a DBT projection image sequence for DBT reconstruction. Outside the DBT reconstruction angle range, the first scanning frame rate f1 is used to scan and acquire images at a higher speed. The second scanning data obtained can be combined with the first scanning data to form a CT projection image sequence for CT reconstruction.

[0076] If the acquisition frame rate in this round of scanning adopts the first acquisition frame rate f1, the smaller the rotation speed, the greater the scanning density, which makes the angular interval between each projection image in the first scanning data smaller than the angular interval between any two adjacent projection images in the second scanning data.

[0077] The rotation speed and acquisition frame rate during scanning within the DBT reconstruction angle range can meet the requirements of DBT reconstruction, that is, the projection angle interval of the first scanning data can meet the requirements of DBT reconstruction. At this time, the first scanning data can be directly reconstructed by DBT using the FBP algorithm to obtain a DBT image.

[0078] The rotation speed and acquisition frame rate when scanning outside the DBT reconstruction angle range can meet the requirements of CT reconstruction. Since the requirements of CT reconstruction for scanning density are lower than those of DBT reconstruction, the projection angle intervals of the first scanning data and the second scanning data can meet the requirements of CT reconstruction. At this time, the first scanning data and the second scanning data can be directly reconstructed by CT using the FBP algorithm to obtain a CT image.

[0079] It is understandable that the acquisition frame rate when scanning within the DBT reconstruction angle range may be different from the acquisition frame rate when scanning outside the DBT reconstruction angle range. The acquisition frame rate may be set according to the working conditions as long as it meets the corresponding reconstruction requirements.

[0080] Due to the limitation of hardware devices, when the processor 1100 controls the scanning component 1300 to rotate, the process of changing from the first speed of rotation to the rotation higher than the first speed, and changing from the rotation higher than the first speed to the first speed of rotation involves a speed change process, and even involves a speed change process when the scanning component 1300 starts to rotate. The speed change rotation process and the uniform speed rotation process are described below.

[0081] The process of the scanning component 1300 rotating from rest until the speed increases to the required speed is as follows. In step S120, the process of rotating around the subject at a speed higher than the first speed and scanning the subject may include the following steps: during the start of the scan, rotating around the subject at a preset second speed from the start position, and scanning the subject to obtain third scan data. The second speed is higher than the first speed. The start position may be outside the preset target angle range, the DBT reconstruction angle range may be truly included in the target angle range, and a target angle range may only include one DBT reconstruction angle range.

[0082] See also Figure 3 , S is the starting position of the scanning assembly 1300. Before the scanning starts, the radiation source 21 is located at the position S. The position S is usually located outside the DBT reconstruction angle range R2 and the two speed change sections adjacent to R2, for example, outside the target angle range R0. The target angle range R0 may have a common boundary with the DBT reconstruction angle range R2, and the common boundary is the boundary when the radiation source 21 leaves the target angle range R0.

[0083] Starting from position S, the radiation source 21 presses Figure 3 The clockwise direction indicated by the arrow at the middle position S begins to accelerate to the second speed v2. Since the speed change takes a certain time, the rotation passes a certain angle during this period. Then the second speed v2 is maintained for rotation until reaching point P3. P3 is located on the boundary of R0 and also on the boundary of the first speed change angle range R1. The scan data obtained by scanning during the rotation of the radiation source 21 from point S to point P3 is the third scan data, which is a part of the CT scan data and is used to form a CT projection image sequence.

[0084] If the detector is an upright detector, that is, it is not offset relative to the radiation source, then the scanning angle of this round can be set to be greater than 180° and less than 360°. In this case, only one R2 can be passed during this round of scanning; if the detector is offset relative to the radiation source, then the scanning angle of this round can be set to be equal to 360°. In this case, two R2s can be passed during this round of scanning, and the two R2s are symmetrically arranged relative to the rotation center of the scanning component 1300.

[0085] The scanning component 1300 starts to rotate at a constant speed after being raised to the required speed, and starts to decelerate to another required speed when the deceleration condition is met, and the process is as follows. In step S120, the process of rotating around the object at a speed higher than the first speed and scanning the object may include the following steps: when the deceleration condition is met, the speed is reduced from a speed higher than the first speed to the first speed, and the object is scanned to obtain fourth scanning data. Among them, the scanning component enters the DBT reconstruction angle range at the first speed after completing the deceleration. The deceleration condition may include: the scanning component rotates to reach a preset first position. Among them, the first position may be located outside the DBT reconstruction angle range.

[0086] Continue reading Figure 3 , when the radiation source 21 moves at a uniform speed of the second speed v2 to the arrival point P3, that is, when it reaches the first position, it begins to enter the range of R1. The radiation source 21 will decelerate when rotating in the range of R1 until it begins to enter the range of R2 and the rotation speed is reduced to the first speed v1. v1 can be half of v2. The speed change parameters of the rotating table can be set in advance so that when the radiation source 21 reaches the common boundary of R1 and R2, the speed just drops to the first speed v1. During the deceleration process within the range of R1, the acquisition frame rate can remain unchanged at the frame rate before entering R1, and the data obtained by scanning is the fourth scanning data, which is a part of the CT scanning data and is used to form a CT projection image sequence.

[0087] Afterwards, the radiation source 21 moves at a uniform speed v1 through R2 and reaches the common boundary of R2 and R0. During the process, the acquisition frame rate can remain unchanged as the frame rate when scanning in R1. The data obtained by the scan is the first scan data, which is the DBT scan data, which is used to form a DBT projection image sequence and is also used to assist in forming a CT projection image sequence.

[0088] The scanning component 1300 rotates at a constant speed for a certain angle at another required speed and then starts to increase the speed, and the process is as follows. In step S120, the process of rotating around the object at a speed higher than the first speed and scanning the object may include the following steps: when the speed increase condition is met, the speed is increased from the first speed to a speed higher than the first speed, and the object is scanned to obtain the fifth scanning data. Among them, the speed increase condition includes: the scanning component rotates to start leaving the DBT reconstruction angle range. When the speed reduction condition is met and the speed reduction begins, the starting speed can be equal to the speed increase end speed when the speed increase is completed.

[0089] Continue reading Figure 3, when the radiation source 21 moves at a uniform speed of the first speed v1 until it reaches the common boundary of R2 and R3, it begins to enter the second speed change angle range R3. When the radiation source 21 rotates in the range of R3, the speed will be increased until the rotation speed is increased to the second speed v2 when it begins to leave the range of R3, that is, the rotation speed is restored to the speed before the deceleration. The speed change parameters of the rotating table can be set in advance so that when the radiation source 21 reaches the common boundary of R2 and R3, the speed is just increased to the second speed v2. During the speed increase process within the range of R3, the acquisition frame rate can remain unchanged at the frame rate when scanning within the range of R2, and the data obtained by scanning is the fifth scanning data, which is a part of the CT scanning data and is used to form a CT projection image sequence.

[0090] After the scanning component 1300 completes the speed increase, it starts to rotate at a uniform speed, and the process is as follows. In step S120, the process of rotating around the object at a speed higher than the first speed and scanning the object may include the following steps: when the speed increase from the first speed to the speed higher than the first speed is completed, the speed higher than the first speed is maintained while scanning the object to obtain the sixth scanning data, until the speed reduction condition is met or the scanning of all the angles to be scanned is completed.

[0091] Continue reading Figure 3 After the speed increase is completed, the radiation source 21 will continue to rotate and scan in the clockwise direction. If the detector is not biased, it can directly rotate at a uniform speed at the second speed v2 until all the scanning angles to be scanned are completed, that is, the entire scanning process only undergoes a process of first increasing the speed, then uniformizing the speed, and then decelerating (corresponding to R1, R2, and R3 in sequence). Thus, the first scanning data and the second scanning data including the third scanning data, the fourth scanning data, the fifth scanning data, and the sixth scanning data are obtained.

[0092] The acquisition resolution when scanning the object at a speed higher than the first speed may be lower than the acquisition resolution when scanning the object at the first speed. The acquisition frame rate when scanning the object at a speed higher than the first speed may be higher than the acquisition frame rate when scanning the object at the first speed.

[0093] For example, when rotating and scanning around the subject at the second speed v2, the scan data obtained at this time is used for CT reconstruction. The rotation speed is high and the acquisition frame rate is f1. At this time, the image resolution can be set to the normal resolution of 640*640, so that when the scanning component rotates to the next scanning angle and scans, the data at the previous scanning angle has been transmitted.

[0094] When rotating and scanning around the object to be examined at the first speed v1, the scanning data obtained at this time is used for DBT reconstruction. The rotation speed is relatively low, and the acquisition frame rate is f2 which is greater than f1. At this time, the image resolution can be set to the high resolution of 1280*1280. In this way, it can not only ensure that when the scanning component rotates to the next scanning angle and scans, the data at the previous scanning angle has been transmitted, but also increase the image clarity and content richness, and improve the image quality and image effect.

[0095] It should be noted that the unit of the frame rate f is frames per second, and the unit of the rotation speed v is degrees per second. If f1 / v1 < f2 / v2, it means that the number of projection images collected per degree of rotation in the non-DBT reconstruction angle range is less than the number of projection images collected per degree of rotation in the DBT reconstruction angle range, and the angular interval of the projection images of the first scanning data satisfies being less than the angular interval of the projection images of the second scanning data. When f1 / v1 = f2 / v2, that is, when the projection images of the first scanning data and the second scanning data are all at equal angular intervals, the function of performing high-resolution scanning at v1 and ordinary-resolution scanning at v2 to improve the DBT image quality can also be realized.

[0096] If the detector is offset relative to the radiation source, or the scanning component rotates around the object to be examined in a helical scanning manner during the scanning process, then: the angle rotated by the scanning component from the start of scanning to the end of scanning is greater than or equal to 360°, and there are two DBT reconstruction angle ranges set, and the two DBT reconstruction angle ranges are symmetrically set with respect to the rotation center of the scanning component.

[0097] If the detector is offset, after leaving R3, it will rotate uniformly to the first variable-speed angle range at the A end. After decelerating in the first variable-speed angle range at the A end, it will move uniformly at the first speed v1 within the DBT reconstruction angle range at the A end, and then accelerate in the first variable-speed angle range at the A end. After accelerating, it will move uniformly until the scanning of all the angles to be scanned is completed. During the scanning process in the above three angle ranges at the A end, the acquisition frame rate can remain unchanged as the frame rate during the scanning in the R3 range. The above three angle ranges at the A end and the above three angle ranges at the B end are symmetrically set with respect to the rotation center of the scanning component 1300.

[0098] If the detector is not offset and uses a helical scanning method to rotate and rise at the same time, the scanning angle will be greater than 360°, that is, the number of turns of rotation is greater than 1 turn. Then the radiation source 21 and the detector 22 will pass through the processes of accelerating first, then moving uniformly, and then decelerating multiple times, and obtain multiple first scanning data, multiple third scanning data, multiple fourth scanning data, multiple fifth scanning data, and multiple sixth scanning data.

[0099] Figure 8A schematic diagram of an imaging system using a hardware implementation of a processing system according to some embodiments of the present invention is shown. Figure 8 The imaging system 2000 provided by the present invention includes: a scanning device, an interpolation module 2002 and a reconstruction module 2004. The scanning device may include a processor 1100, a memory 1200 and a scanning component 1300. The scanning component 1300 may include a radiation source and a detector. The processor 1100 may include a first scanning control module and a second scanning control module. The memory 1200 stores a computer program. When the computer program is executed by the processor 1100, the processor 1100 may execute the following steps S110 and S120 to control the scanning component 1300 to achieve the scanning method.

[0100] S110, within a preset DBT reconstruction angle range, rotate around the subject at a preset first speed and scan the subject to obtain first scan data. The first scan data is used for DBT reconstruction, and the DBT reconstruction angle range includes the angle corresponding to the target projection position. Step S110 can be implemented by the first scan control module 1002.

[0101] S120, outside the DBT reconstruction angle range, rotating around the object at a speed higher than the first speed and scanning the object to obtain second scan data. The second scan data is used to form CT scan data in combination with the first scan data, and the minimum angle interval between the multiple projections formed by the second scan data is greater than the angle interval between the multiple projections formed by the first scan data. Step S110 can be implemented by the second scan control module 1004.

[0102] It should be noted that the undisclosed details about the scanning device in the imaging system 2000 of this embodiment, including the functions and working principles of the scanning device, can refer to the details disclosed in the scanning device 1000 of the above-mentioned embodiment proposed by the present invention, and will not be repeated here.

[0103] The interpolation module 2002 is used to interpolate the first scan data and part of the second scan data according to multiple CT scan angles within a first angle range to obtain interpolated images of multiple CT scan angles. The first angle range includes a DBT reconstruction angle range and an angle range that a scanning component of the scanning device passes through during a speed change process, and the speed change process includes a speed reduction process and a speed increase process.

[0104] The reconstruction module 2004 is used to perform DBT reconstruction based on the first scan data to obtain a DBT image, and to perform CT reconstruction based on the interpolated image and the scan data corresponding to angles outside the first angle range in the second scan data to obtain a breast CT image.

[0105] See also Figure 4 After the first scanning data and the second scanning data are obtained by the scanning device, the angular spacing between the projections of the first scanning data and the second scanning data is different. Assuming that the angular spacing of the data obtained by scanning at the second speed v2 is ( Figure 4 The angle interval between the solid lines in the figure is w2, then the angles to be interpolated in the first speed change angle range, the second speed change angle range and the DBT reconstruction angle range are determined, and the angle interval between the angles to be interpolated is w2, such as Figure 6 Then, interpolation is performed according to the interpolation angle and the scan data collected in the first speed change angle range, the second speed change angle range and the DBT reconstruction angle range to obtain Figure 6 The interpolated image at the midpoint dash line position. The interpolation method can be bilinear interpolation, nearest neighbor interpolation, or cubic interpolation in the angular direction.

[0106] The interpolated images are combined with the projection images scanned under v2 to form a sequence of CT projection images with equal angle spacing, that is, Figure 6 The solid lines and dotted lines together form a CT projection image sequence. The first scan data itself can form a DBT projection image series with equal angle spacing. Then, the reconstruction module 2004 is used to perform DBT reconstruction and CT reconstruction respectively to obtain DBT images and CT images.

[0107] It is understandable that when the subject is scanned by spiral scanning, the first scanning data and the second scanning data obtained have multiple segments. During DBT reconstruction, the multiple segments of the first scanning data and the FDK reconstruction algorithm are used for reconstruction to obtain the DBT reconstruction result.

[0108] Fig. 9 FIG. 1 is a schematic flow chart showing a scanning method according to some embodiments of the present invention. Fig. 9 The present invention provides a scanning method M100, which is applied to a scanning component. The scanning component may include a radiation source and a detector, and the radiation source and the detector are arranged opposite to each other. The radiation source and the detector may be installed on a rotating table, and the rotating table is controlled to rotate. The scanning method M100 may include the following steps S110 and S120.

[0109] S110, within a preset DBT reconstruction angle range, rotate around the subject at a preset first speed and scan the subject to obtain first scan data. The first scan data is used for DBT reconstruction, and the DBT reconstruction angle range includes the angle corresponding to the target projection position. Step S110 can be implemented by the first scan control module 1002.

[0110] S120, outside the DBT reconstruction angle range, rotating around the object at a speed higher than the first speed and scanning the object to obtain second scan data. The second scan data is used to form CT scan data in combination with the first scan data, and the minimum angle interval between the multiple projections formed by the second scan data is greater than the angle interval between the multiple projections formed by the first scan data. Step S110 can be implemented by the second scan control module 1004.

[0111] It should be noted that the details not disclosed in the scanning method M100 of this embodiment can refer to the details disclosed in the scanning device 1000 of the above embodiment proposed by the present invention, and will not be repeated here.

[0112] Fig.10 Schematic diagram showing the flow of imaging methods according to some embodiments of the present invention. Fig.10 The present invention provides an imaging method M200, and the imaging method M200 may include the following steps S210, S220 and S230.

[0113] S210 , scanning the object using the scanning method M100 to obtain first scanning data and second scanning data.

[0114] S220, interpolating the first scan data and part of the second scan data at multiple CT scan angles within a first angle range to obtain interpolated images of multiple CT scan angles. The first angle range includes a DBT reconstruction angle range and an angle range that a scanning component of the scanning device passes through during a speed change process, and the speed change process includes a speed reduction process and a speed increase process.

[0115] S230, performing DBT reconstruction based on the first scan data to obtain a DBT image, and performing CT reconstruction based on the interpolated image and the scan data corresponding to angles outside the first angle range in the second scan data to obtain a breast CT image.

[0116] The scanning method M100 may include step S110 and step S120.

[0117] S110, within a preset DBT reconstruction angle range, rotate around the subject at a preset first speed and scan the subject to obtain first scan data. The first scan data is used for DBT reconstruction, and the DBT reconstruction angle range includes the angle corresponding to the target projection position. Step S110 can be implemented by the first scan control module 1002.

[0118] S120, outside the DBT reconstruction angle range, rotating around the object at a speed higher than the first speed and scanning the object to obtain second scan data. The second scan data is used to form CT scan data in combination with the first scan data, and the minimum angle interval between the multiple projections formed by the second scan data is greater than the angle interval between the multiple projections formed by the first scan data. Step S110 can be implemented by the second scan control module 1004.

[0119] It should be noted that the details not disclosed in the imaging method M200 of this embodiment can refer to the details disclosed in the scanning device 1000 and the imaging system 2000 of the above-mentioned embodiment proposed by the present invention, and will not be repeated here.

[0120] The present invention also provides a readable storage medium, in which a computer program is stored. When the computer program is executed by a processor, it is used to implement the method of any of the above-mentioned embodiments.

[0121] For the purposes of this specification, a "readable storage medium" may be any device that can contain, store, communicate, propagate or transport a program for use with or in conjunction with an instruction execution system, apparatus or device. More specific examples (a non-exhaustive list) of readable storage media include the following: an electrical connection with one or more wires (electronic device), a portable computer disk case (magnetic device), a random access memory (RAM), a read-only memory (ROM), an erasable and programmable read-only memory (EPROM or flash memory), a fiber optic device, and a portable read-only memory (CDROM).

[0122] The present invention also provides a computer program product. The method of the present invention can be implemented in whole or in part by software, hardware, firmware or any combination thereof. When implemented by software, it can be implemented in whole or in part in the form of a computer program product. The computer program product includes one or more computer programs or instructions. When the computer program or instruction is loaded and executed, the process or function of the present invention is executed in whole or in part. The computer can be a general-purpose computer, a special-purpose computer, a computer network, a network device, a user device, a core network device, an OAM or other programmable device.

[0123] The computer program or instructions may be stored in a computer-readable storage medium, or transmitted from one computer-readable storage medium to another computer-readable storage medium, for example, the computer program or instructions may be transmitted from one website, computer, server or data center to another website, computer, server or data center by wired or wireless means. The computer-readable storage medium may be any available medium that can be accessed by a computer or a data storage device such as a server or data center that integrates one or more available media. The available medium may be a magnetic medium, such as a floppy disk, a hard disk, or a magnetic tape; it may also be an optical medium, such as a digital video disk; it may also be a semiconductor medium, such as a solid-state drive. The computer-readable storage medium may be a volatile or non-volatile storage medium, or may include both volatile and non-volatile types of storage media.

[0124] 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.

[0125] The present invention is described with reference to flowcharts and / or block diagrams of methods, devices (systems), and computer program products according to the present invention. It should be understood that each process and / or block in the flowchart and / or block diagram, as well as the combination of processes and / or blocks in the flowchart and / or block diagram, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing device to produce a machine, so that the instructions executed by the processor of the computer or other programmable data processing device generate instructions for implementing the processes in the flowchart and / or block diagram. Figure 1 A process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0126] These computer program instructions may also be stored in a computer-readable memory capable of directing a computer or other programmable data processing device to operate in a specific manner, so that the instructions stored in the computer-readable memory produce an article of manufacture comprising an instruction device, which implements the process Figure 1 A process or multiple processes and / or boxes Figure 1 A function specified in one or more boxes.

[0127] These computer program instructions can also be loaded onto a computer or other programmable data processing device so that a series of operating steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing instructions for implementing the process in the computer or other programmable device. Figure 1 A process or multiple processes and / or boxes Figure 1 The steps for the functions specified in one or more boxes.

[0128] In the description of this specification, the description with reference to the terms "one embodiment / method", "some embodiments / methods", "specific examples", or "some examples" etc. means that the specific features, structures, materials or characteristics described in conjunction with the embodiment / method or example are included in at least one embodiment / method or example of the present invention. In this specification, the schematic representations of the above terms are not necessarily the same embodiment / method or example. Moreover, the specific features, structures, materials or characteristics described may be combined in any one or more embodiments / methods or examples in a suitable manner. In addition, those skilled in the art may combine and combine the different embodiments / methods or examples described in this specification and the features of the different embodiments / methods or examples, without contradiction.

[0129] In addition, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features defined as "first" and "second" may explicitly or implicitly include at least one of the features. In the description of the present invention, the meaning of "plurality" is at least two, such as two, three, etc., unless otherwise clearly and specifically defined.

[0130] It should be understood by those skilled in the art that the above embodiments are only for the purpose of clearly illustrating the present invention, and are not intended to limit the scope of the present invention. For those skilled in the art, other changes or modifications may be made based on the above disclosure, and these changes or modifications are still within the scope of the present invention.

Claims

1. An imaging system, characterized in that: include: A scanning device, an interpolation module and a reconstruction module; The scanning device comprises a scanning component, a processor and a memory, wherein the scanning component comprises a radiation source and a detector arranged relatively to each other, and the memory stores a computer program. When the computer program is executed by the processor, the processor controls the scanning component to perform the following process: In a preset DBT reconstruction angle range, rotating around a subject at a preset first speed and scanning the subject to obtain first scanning data, wherein the first scanning data is used for DBT reconstruction, and the DBT reconstruction angle range includes an angle corresponding to a target projection position; as well as Outside the DBT reconstruction angle range, rotating around the object at a speed higher than the first speed and scanning the object to obtain second scanning data, the second scanning data is used to form CT scanning data in combination with the first scanning data, the minimum angular interval between multiple projections formed by the second scanning data is greater than the angular interval between multiple projections formed by the first scanning data; the acquisition resolution when scanning the object at a speed higher than the first speed is less than the acquisition resolution when scanning the object at the first speed, and the acquisition frame rate when scanning the object at a speed higher than the first speed is greater than the acquisition frame rate when scanning the object at the first speed; The interpolation module is used to interpolate the first scanning data and part of the second scanning data at multiple CT scanning angles within a first angle range to obtain interpolated images of the multiple CT scanning angles, wherein the first angle range includes the DBT reconstruction angle range and the angle range passed by the scanning component of the scanning device during the speed change process, and the speed change process includes a speed reduction process and a speed increase process; The reconstruction module is used to perform DBT reconstruction based on the first scanning data to obtain a DBT image, and to perform CT reconstruction based on the interpolation image and scanning data corresponding to angles outside the first angle range in the second scanning data to obtain a breast CT image.

2. The imaging system according to claim 1, characterized in that Rotating around the object at a speed higher than the first speed and scanning the object, comprising: During the initialization of scanning, the object is rotated around the object at a preset second speed from the initial position, and the object is scanned to obtain third scanning data, wherein the second speed is higher than the first speed.

3. The imaging system according to claim 2, characterized in that The starting position is outside a preset target angle range, the DBT reconstruction angle range is truly included in the target angle range, and one target angle range only includes one DBT reconstruction angle range.

4. The imaging system according to claim 1, characterized in that Rotating around the object at a speed higher than the first speed and scanning the object, comprising: When the deceleration condition is met, the speed is reduced from a speed higher than the first speed to the first speed, and the object is scanned to obtain fourth scanning data. After completing the deceleration, the scanning component enters the DBT reconstruction angle range at the first speed. The deceleration condition includes: the scanning component rotates to reach a preset first position.

5. The imaging system according to claim 4, characterized in that: The first position is outside the DBT reconstruction angle range.

6. The imaging system according to claim 1, characterized in that: Rotating around the object at a speed higher than the first speed and scanning the object, comprising: When a speed increase condition is met, the speed is increased from the first speed to a speed higher than the first speed, and the object is scanned to obtain fifth scanning data. The speed increase condition includes: the scanning component rotates to start leaving the DBT reconstruction angle range.

7. The imaging system according to claim 6, characterized in that: The starting speed of deceleration when the deceleration condition is met and the deceleration begins is equal to the ending speed of acceleration when the acceleration is completed.

8. The imaging system according to claim 1, characterized in that: Rotating around the object at a speed higher than the first speed and scanning the object, comprising: When the speed is increased from the first speed to a speed higher than the first speed, the object is scanned while maintaining a speed higher than the first speed to obtain sixth scanning data until a speed reduction condition is met or scanning of all the angles to be scanned is completed.

9. The imaging system according to claim 1, characterized in that: If the detector is offset relative to the radiation source, or the scanning component rotates around the object in a spiral scanning manner during the scanning process, then: the angle of rotation of the scanning component from the beginning of the scan to the end of the scan is greater than or equal to 360°, and two DBT reconstruction angle ranges are set, and the two DBT reconstruction angle ranges are symmetrically set relative to the rotation center of the scanning component.

10. The imaging system according to claim 1, characterized in that The target projection position includes a head-tail position.

11. The imaging system according to claim 10, characterized in that: The angle corresponding to the target projection position is the central angle of the DBT reconstruction angle range.

12. The imaging system according to claim 1, characterized in that The DBT reconstruction angle range is less than or equal to 60°.

13. The imaging system according to claim 1, characterized in that If the detector of the scanning component is offset relative to the radiation source of the scanning component, or the scanning component rotates around the object in a spiral scanning manner during the scanning process, the reconstruction module performs DBT reconstruction on multiple first scanning data to obtain a DBT image, and the multiple first scanning data are data obtained by scanning when the scanning component rotates multiple times through the DBT reconstruction angle range.

14. An imaging method, characterized in that: include: The object is scanned by a scanning method to obtain first scanning data and second scanning data, the scanning method comprising: rotating around the object at a preset first speed and scanning the object within a preset DBT reconstruction angle range to obtain first scanning data, the first scanning data being used for DBT reconstruction, the DBT reconstruction angle range including an angle corresponding to a target projection position; and rotating around the object at a speed higher than the first speed and scanning the object outside the DBT reconstruction angle range to obtain second scanning data, the second scanning data being used to form CT scanning data in combination with the first scanning data, the minimum angle interval between multiple projection images formed by the second scanning data being greater than the angle interval between multiple projection images formed by the first scanning data; interpolating the first scan data and part of the second scan data at a plurality of CT scan angles within a first angle range to obtain interpolated images of the plurality of CT scan angles, wherein the first angle range includes the DBT reconstruction angle range and an angle range passed by a scanning component of a scanning device during a speed change process, wherein the speed change process includes a speed reduction process and a speed increase process; as well as DBT reconstruction is performed based on the first scan data to obtain a DBT image, and CT reconstruction is performed based on the interpolated image and scan data corresponding to angles outside the first angle range in the second scan data to obtain a breast CT image.

15. A readable storage medium, characterized in that: The readable storage medium stores a computer program, and when the computer program is executed by a processor, it is used to implement the method according to claim 14.

16. A computer program product, characterized in that The computer program product comprises a computer program, which is used at least to implement the method according to claim 14 when being executed by a processor.

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