Area array source-based breast imaging system, method, apparatus, and storage medium

Abstract

The embodiment of the application relates to the technical field of tomography, in particular to a breast imaging system, method and equipment based on a surface array source and a storage medium, the breast imaging system comprising a power module, a surface array source, a detection module, a data acquisition module and an image reconstruction module; the detection module comprises a detection platform, a detector and a connecting arm; the surface array source and the detection platform are located on two sides of an imaging object, the surface array source is a flat surface array source or an arc surface array source; when the flat surface array source is used, the flat surface array source comprises at least two plane ray source units; when the arc surface array source is used, only one surface array source is needed, and the surface array source semi-surrounds the imaging object. The breast imaging system based on the surface array source can realize virtual rotation projection of the imaging object, does not need a moving part, and can obtain more longitudinal projection information, thereby improving the longitudinal resolution of a reconstructed image.

Description

Technical Field

[0001] This application relates to the field of tomographic imaging technology, and in particular to a breast imaging system, method, device and storage medium based on a planar array source. Background Technology

[0002] Currently, X-ray tomography-based breast imaging systems are commonly used for early breast cancer screening, obtaining pseudo-three-dimensional images through limited-angle scanning. First, X-rays emit radiation, and the radiation dose from current X-ray tomography-based breast imaging systems remains significant. Second, current breast imaging systems use a heat source for rotational imaging, and mechanical jitter during rotation introduces artifacts, causing reconstruction errors. Third, the current scanning range of breast imaging systems is only 11-60°, resulting in severe loss of projection data, leading to decreased reconstructed image quality and an inability to accurately reconstruct minute calcifications, causing misdiagnosis and missed diagnosis.

[0003] To address the aforementioned shortcomings, several technical solutions have been implemented: Currently, some solutions use a single array X-ray source instead of a heat-source X-ray source, eliminating the need for rotation during acquisition. However, due to the limited scanning angle, a single array X-ray source still cannot effectively improve longitudinal resolution. Furthermore, because the array source is individually packaged, the spacing between the array sources cannot be ignored, leading to incomplete projection data and a decrease in reconstruction quality. Summary of the Invention

[0004] This application provides a breast imaging system, method, device, and storage medium based on a planar array source, which can realize virtual rotational projection of the imaging object without moving parts, and can obtain more longitudinal projection information through the planar array source, thereby improving the longitudinal resolution of the reconstructed image.

[0005] To address the aforementioned technical problems, in a first aspect, embodiments of this application provide a breast imaging system based on a planar array source, comprising: a power module and a planar array source, a detection module, a data acquisition module, and an image reconstruction module connected to the power module; the detection module includes a detection platform for placing an imaging object, a detector located within the detection platform, and a connecting arm for connecting the planar array source; the planar array source is located on the opposite side of the detection platform and is used to emit X-ray beams toward the imaging object; the planar array source is a flat planar array source or an arc-shaped planar array source; when the planar array source is a flat planar array source, the flat planar array source includes at least two X-ray source units, each X-ray source unit including a panel and a plurality of X-ray sources arranged in an array, the X-ray sources being disposed on the side of the panel facing the imaging object, and there being an angle between adjacent panels, the angle being... The angle range is 90° to 180°; when the area array source is an arc array source, the arc array source is a single area array source; the arc array source includes multiple X-ray sources distributed in an array, and the arc array source semi-encloses the imaging object, with the X-ray sources set on the side of the panel facing the imaging object; the arc angle range of the arc array source is 90° to 180°; the detector is a flat panel detector or an arc surface detector, which is used to receive the X-ray beam emitted by the area array source, and after receiving the acquisition command issued by the data acquisition module, the detector acquires the projection data of the area array source, and sends the acquired projection data to the image reconstruction module. The image reconstruction module reconstructs the projection data to realize the virtual rotation projection of the imaging object, and on this basis, introduces differential relations to finally obtain a high-quality reconstructed image.

[0006] In some exemplary embodiments, the area array source is located above, below, or to the side of the imaging object; the detector is positioned on the side of the imaging object away from the area array source.

[0007] In some exemplary embodiments, when the area array source is a flat surface array source, the flat surface array source includes two ray source units, both of which are disposed facing the imaging object; the two ray source units are located directly above, directly below, or to the side of the imaging object, and the two ray source units are located on the same side of the imaging object; the two ray source units are symmetrical about the longitudinal central axis of the imaging object.

[0008] In some exemplary embodiments, when the area array source is a flat surface array source, the flat surface array source includes three ray source units, all of which are disposed facing the imaging object; the flat surface array source includes a first ray source unit and a second ray source unit and a third ray source unit located on both sides of the first ray source unit; the first ray source unit is located directly above, directly below, or to the side of the imaging object, and the first ray source unit, the second ray source unit, and the third ray source unit are located on the same side of the imaging object; the second ray source unit and the third ray source unit are symmetrical about the longitudinal central axis of the imaging object.

[0009] In some exemplary embodiments, the detection module further includes a pressure plate for fixing the imaging object.

[0010] In some exemplary embodiments, the image reconstruction module includes a correction unit, a preprocessing unit, and a reconstruction unit connected in sequence. The correction unit is used to perform correction processing on the projection data. The correction processing includes bright field correction, dark field correction, zero field correction, and detection response correction. The correction unit includes a judgment unit and a correction selection unit. The correction selection unit includes a phantom correction module and a phantomless correction module. The judgment unit is used to determine whether a correction phantom exists in the module. The correction selection unit is used to select the phantom correction module to perform correction processing on the projection data when a correction phantom exists in the module, and to select the phantomless correction module to perform correction processing on the projection data when no correction phantom exists in the module. The preprocessing unit is used to preprocess the corrected projection data. The preprocessing includes beam shape correction and light intensity correction. The reconstruction unit is used to design differential constraint terms based on the differential relationship between the angle of the virtual rotation projection and the detector, and to optimize and solve the differential relationship based on the differential constraint terms to reconstruct the preprocessed projection data and obtain the internal structure of the imaging object.

[0011] In some exemplary embodiments, the area array source includes a beam beamer for beaming the radiation source on the radiation source unit; the beam beamer is disposed inside the panel, or the beam beamer is disposed on the side surface of the panel facing the imaging object.

[0012] Secondly, this application also provides a breast imaging method based on a planar array source. Using the aforementioned breast imaging system based on a planar array source for CT imaging, the method includes the following steps: setting imaging parameters; placing the imaging object on a detection platform and setting the angle between the panels of adjacent X-ray source units, or the radian angle of the arc-shaped planar array source; addressably illuminating the X-ray sources of the X-ray source units under an encoding template; collecting projection information of all X-ray beams emitted by the X-ray sources under the encoding template using a detector to obtain projection data; rearranging the angles of the panels of the X-ray source units to obtain a virtual rotational projection of the planar array source onto the imaging object; designing differential constraint terms based on the differential relationship between the angle of the virtual rotational projection and the detector, and optimizing the differential relationship based on the differential constraint terms; reconstructing the preprocessed projection data to obtain the internal structure of the imaging object.

[0013] In some exemplary embodiments, the detector receives information on all the X-ray beams emitted by the X-ray source under the encoding template to obtain projection data, including: under different encoding templates, the detector samples the projection information of all the X-ray beams emitted by the X-ray source to obtain projection data.

[0014] In some exemplary embodiments, the detector acquires projection information of all ray beams emitted by the ray source under the coded template, and the acquisition process is represented as follows:

[0015]

[0016] Where b represents the measurement data, Let M represent the sampling matrix, M represent the number of light sources, 1 indicates that the light source at this location is lit in k measurements, P represent the projection data matrix, which is the projection data of each point source, mathematically equal to Af, where A is the known projection matrix, f is the image to be reconstructed, and Pij represents the measurement data received by the d-th detector from the j-th light source.

[0017] In some exemplary embodiments, obtaining a virtual rotational projection of the surface array source onto the imaging object by rearranging the angles of the panel of the ray source unit includes: dealiasing the coded emitting cone beam to obtain a single-point cone beam; and rearranging the projection of the ray source unit to obtain parallel beams at different angles to obtain a virtual rotational projection.

[0018] This application also provides an electronic device, including: at least one processor; and a memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, the instructions being executed by the at least one processor to enable the at least one processor to perform the above-described breast imaging method based on an area array source.

[0019] This application also provides a computer-readable storage medium storing a computer program that, when executed by a processor, implements the above-described breast imaging method based on a planar array source.

[0020] The technical solution provided in this application has at least the following advantages:

[0021] This application provides a breast imaging system, method, device, and storage medium based on a planar array source. The breast imaging system includes: a power module and a planar array source, a detection module, a data acquisition module, and an image reconstruction module connected to the power module; the detection module includes a detection platform for placing the imaging object, a detector located within the detection platform, and a connecting arm for connecting the planar array source; the planar array source is located on the opposite side of the detection platform and is used to emit X-ray beams towards the imaging object; the planar array source can be a flat planar array source or an arc-shaped planar array source. When a flat planar array source is used, the planar planar array source includes at least two X-ray source units, each X-ray source unit including a panel and multiple X-ray sources arranged in an array. The X-ray sources are located on the side of the panel facing the imaging object, and there is an angle between adjacent panels, the angle ranging from 90° to 180°; when an arc-shaped planar array source is used, only one planar array source is needed, the planar array source semi-encloses the imaging object, and the arc angle range is 90° to 180°. The detector is used to receive the X-ray beam emitted by the surface array source. The detector can be a curved surface detector or a flat surface detector. After receiving the acquisition command issued by the data acquisition module, the detector acquires the projection data of the surface array source and sends the acquired projection data to the image reconstruction module. The image reconstruction module reconstructs the projection data to realize the virtual rotation projection of the imaging object.

[0022] The breast imaging system based on a planar array source provided in this application firstly greatly increases the scanning range by arranging multiple sets of flat planar array sources or arc-shaped planar array sources around the object to be reconstructed. Secondly, by having each radiation source cover only a portion of the imaging object and coded emission, extremely low-dose scanning can be achieved, reducing radiation risk. Thirdly, dealiasing is performed based on the coded measurement data to obtain a cone-beam projection of a single-point source, which is then arranged into parallel beam projections at different angles to obtain a virtual rotational projection of the imaging object. Fourthly, through the design of the image reconstruction module, the angle of the measurement data and the differential relationship of the detector are introduced to improve the resolution and imaging quality of the reconstructed image, while reducing the number of coded emission modes. Attached Figure Description

[0023] One or more embodiments are illustrated by way of example with reference to the accompanying drawings. These illustrations do not constitute a limitation on the embodiments, and unless otherwise stated, the figures in the drawings are not to be limited by scale.

[0024] Figure 1 A structural block diagram of a breast imaging system based on a planar array source provided in one embodiment of this application;

[0025] Figure 2 A schematic diagram of a breast imaging system based on a planar array source provided in an embodiment of this application;

[0026] Figure 3 A schematic diagram of a breast imaging system based on a planar array source is provided for another embodiment of this application;

[0027] Figure 4a A schematic diagram illustrating the placement and configuration of a breast imaging system based on a planar array source for breast imaging, provided in an embodiment of this application.

[0028] Figure 4b A schematic diagram showing the placement and setup of a breast imaging system based on a planar array source for breast imaging, provided as another embodiment of this application;

[0029] Figure 4c A schematic diagram showing the placement of a breast imaging system based on a planar array source for breast imaging, provided in another embodiment of this application;

[0030] Figure 5a A schematic diagram of a breast imaging system based on a planar array source, provided as another embodiment of this application;

[0031] Figure 5b A schematic diagram of a breast imaging system based on a planar array source, provided as another embodiment of this application;

[0032] Figure 6A schematic diagram of a breast imaging system based on a planar array source, provided as another embodiment of this application;

[0033] Figure 7 A schematic diagram of a breast imaging system based on a planar array source, provided as another embodiment of this application;

[0034] Figure 8 A cross-sectional view of a data acquisition process provided in an embodiment of this application;

[0035] Figure 9 A cross-sectional view of a data acquisition process provided for another embodiment of this application;

[0036] Figure 10 A cross-sectional view of a data acquisition process provided in yet another embodiment of this application;

[0037] Figure 11 A schematic diagram of the correction process of a correction unit provided in an embodiment of this application;

[0038] Figure 12 A schematic flowchart illustrating a breast imaging method based on a planar array source, provided in an embodiment of this application;

[0039] Figure 13 A schematic flowchart of a breast imaging data acquisition and reconstruction method provided in an embodiment of this application;

[0040] Figure 14 A schematic diagram of coded sampling for a breast imaging system based on a planar array source, provided in an embodiment of this application;

[0041] Figure 15 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. Detailed Implementation

[0042] As can be seen from the background technology, existing static structural breast imaging systems only use a single array X-ray source to replace the heat source X-ray source. No rotation is required during the acquisition process. However, the single array X-ray source still cannot improve the longitudinal resolution, and the spacing between the individually packaged array sources will also cause incomplete projection data, resulting in a decrease in reconstruction quality.

[0043] Current technical solutions employ a planar array source instead of a thermal X-ray source. The planar array source is positioned opposite the detector to receive measurement signals, and the received data is transmitted to the reconstruction system via detector acquisition software. Using a planar array source instead of a thermal X-ray source can improve longitudinal resolution to some extent compared to a single array source. However, using only a simple parallel arrangement of a flat planar array source and detector still limits the scanning range and cannot guarantee the reconstruction quality of fine structures.

[0044] To address this technical problem, this application provides a breast imaging system, method, device, and storage medium based on a planar array source. The breast imaging system includes: a power module and a planar array source, a detection module, a data acquisition module, and an image reconstruction module connected to the power module; the detection module includes a detection platform for placing the imaging object, a detector located within the detection platform, and a connecting arm for connecting the planar array source; the planar array source is located on the opposite side of the detection platform and is used to emit X-ray beams towards the imaging object; the planar array source can be a flat planar array source or an arc-shaped planar array source. When a flat planar array source is used, the flat planar array source includes at least two X-ray source units, each X-ray source unit including a panel and multiple X-ray sources arranged in an array. The source is positioned on the side of the panel facing the imaging object, and there is an angle between adjacent panels, the angle ranging from 90° to 180°. When an arc-shaped surface array source is used, only a single surface array source is needed, which partially surrounds the imaging object, with an arc angle ranging from 90° to 180°. The detector can be a flat panel detector or an arc-shaped detector, which is used to receive the X-ray beam emitted by the surface array source. After receiving the acquisition command from the data acquisition module, the detector acquires the projection data of the surface array source and sends the acquired projection data to the image reconstruction module. The image reconstruction module reconstructs the projection data to achieve virtual rotation of the imaging object. Based on this, a differential relationship is introduced to finally obtain a high-quality reconstructed image.

[0045] This application provides a breast imaging system, method, device, and storage medium based on a planar array source, which obtains more longitudinal projection information and improves longitudinal resolution. First, by arranging multiple sets of flat or curved planar array sources around the object to be reconstructed, the scanning range is greatly increased. Second, by having each radiation source cover only a portion of the imaging object and using coded emission, extremely low-dose scanning can be achieved, reducing radiation risk. Third, dealiasing is performed based on the coded measurement data to obtain a cone-beam projection of a single-point source, which is then arranged into parallel beam projections at different angles to obtain a virtual rotational projection of the imaging object. Fourth, the design of the reconstruction system incorporates the angle of the measurement data and the detector differential relationship to improve reconstruction quality.

[0046] The embodiments of this application will now be described in detail with reference to the accompanying drawings. However, those skilled in the art will understand that many technical details have been provided in the embodiments of this application to facilitate a better understanding of the application. However, the technical solutions claimed in this application can be implemented even without these technical details and various variations and modifications based on the following embodiments.

[0047] See Figure 1 and Figure 2This application provides a breast imaging system based on an area array source, including: a power module 1 and an area array source 2, a detection module 3, a data acquisition module 4, and an image reconstruction module 5 connected to the power module 1; the detection module 3 includes a detection platform 31 for placing an imaging object 6, a detector 32 located within the detection platform 31, and a connecting arm 33 for connecting the area array source 2; the area array source 2 is located on the opposite side of the detection platform 31 and is used to emit an X-ray beam to the imaging object 6.

[0048] Please refer to Figure 1 The power supply module 1 is connected to the area array source 2, the detection module 3, the data acquisition module 4, and the image reconstruction module 5, respectively. The power supply module 1 mainly provides the high-voltage and ordinary power required by each module. The structural diagram of the breast imaging system based on the area array source provided in this embodiment is shown below. Figure 2 As shown.

[0049] It should be noted that the surface array source 2 can be a flat surface array source or an arc-shaped surface array source. Figure 2 This illustrates the case where the area array source in a breast imaging system is a flat panel area array source.

[0050] When the area array source 2 is a flat area array source, such as Figure 2 As shown, the planar array source 2 includes at least two X-ray source units 21. Each X-ray source unit 21 includes a panel 211 and multiple X-ray sources 212 arranged in an array. The X-ray sources 212 are located on the side of the panel 211 facing the imaging object 6, and there is an angle between adjacent panels 211, with the angle ranging from 90° to 180°. The detector 32 is used to receive the X-ray beam emitted by the planar array source. After receiving the acquisition command issued by the data acquisition module 4, the detector 32 acquires the projection data of the planar array source and sends the acquired projection data to the image reconstruction module 5. The image reconstruction module 5 reconstructs the projection data to realize the virtual rotation projection of the imaging object 6. Based on this, a differential relationship is introduced to finally obtain a high-quality reconstructed image.

[0051] like Figure 2 As shown, the imaging object 6 is placed on the detection platform 31, and the detector 32 is installed inside the detection platform 31. The surface array source 2 (flat surface array source) and the detection platform 31 are connected by a connecting arm 33, that is, the connecting arm 33 fixes the flat surface array source above the detection platform 31. Specifically, the connecting arm 33 can be a telescopic connecting rod, and the position of the flat surface array source can be adjusted by adjusting the length and angle of the telescopic connecting rod. The detection platform 31 can be a support table or a support plate, and the detector is built into the support table or support plate. The detector 32 can be a flat detector or a curved detector.

[0052] Please continue reading. Figure 2 The area array source 2 is located above the detection platform 31 and is used to emit X-ray beams towards the imaging object 6; the area array source 2 includes at least two X-ray source units 21. Figure 2 The diagram illustrates a surface array source 2 comprising two X-ray source units 21. These two X-ray source units 21 are arranged at a certain angle, and both X-ray source units 21 are positioned towards the imaging object 6. The X-ray sources 212 are distributed in a matrix array on the panels 211 of the X-ray source units 21, and there is an angle between adjacent panels 211, i.e., there is an angle between the two X-ray source units 21. Figure 2 As shown, two X-ray source units 21 are arranged at an angle α above the imaging object 6, and the angle α can range from 90° to 180°. For example, the angle α can be 90°, 120°, 150°, or 180°. Because the two X-ray source units 21 are arranged at a certain angle, the X-ray beam emitted by the X-ray source 212 covers the imaging object 6, which can obtain more longitudinal projection information, thereby improving the longitudinal resolution.

[0053] It should be noted that the angle α can be adjusted according to different imaging requirements.

[0054] It should be noted that during data acquisition, detector 32 receives information from all the X-ray beams of the area array source 2 under the encoding template. Detector 32 can be a flat panel detector or an arc-shaped detector; the arc-shaped detector is located inside the detection platform 31, such as... Figure 3 As shown. In some embodiments, the area array source 2 is located above, below, or to the side of the imaging object 6, and the detector 32 is disposed on the side of the imaging object 6 away from the area array source 2. That is, in some embodiments, the area array source 2 may be located above the imaging object 6, and the detector 32 may be located below the imaging object 6.

[0055] In other embodiments, the area array source 2 may also be located below the imaging object 6, and the detector 32 may be located above the imaging object 6.

[0056] In other embodiments, the area array source 2 may also be located to the side of the imaging object 6, and the detector 32 may be located on the side of the imaging object 6 away from the area array source 2.

[0057] like Figures 4a to 4c As shown, Figures 4a to 4c The diagram illustrates various placement methods of the breast imaging system based on area array source provided in this application during practical applications. Figures 4a to 4c In the example, the surface array source 2 is a flat surface array source, and the surface array source 2 includes two flat surface array sources.

[0058] When the area array source 2 is a flat area array source, the area array source 2 includes two ray source units 21, both of which are positioned facing the imaging object 6; the two ray source units 21 are located directly above, directly below, or to the side of the imaging object 6, and are located on the same side of the imaging object 6, and are symmetrical about the longitudinal central axis of the imaging object 6. Figure 4a As shown, the two X-ray source units 21 are located directly above the imaging object 6, and the detector 32 ( Figure 4a The image shows the detection module 3, with the detector 32 located inside the detection module 3, directly below the imaging object 6; as shown. Figure 4b As shown, the two X-ray source units 21 are located directly below the imaging object 6, and the detector 32 ( Figure 4b The image shows the detection module 3, with the detector 32 located inside the detection module 3, directly above the imaging object 6; as shown. Figure 4c As shown, the two X-ray source units 21 are located on the side of the imaging object 6, and the two X-ray source units 21 are located on the same side of the imaging object 6. Detector 32 ( Figure 4c The image shows a detection module 3, with a detector 32 located inside the detection module 3, positioned opposite the imaging object 6, and two X-ray source units 21 positioned opposite the detector 32, with the imaging object 6 located between them.

[0059] Of course, it is understood that the area array source 2 may also include three ray source units 21. In some embodiments, the area array source 2 includes three ray source units 21, all of which are disposed facing the imaging object 6; such as Figure 5a As shown, the area array source includes a first ray source unit 21a and a second ray source unit 21b and a third ray source unit 21c located on either side of the first ray source unit 21a; the first ray source unit 21a is located directly above the imaging object 6, and the second ray source unit 21b and the third ray source unit 21c are symmetrical about the longitudinal central axis of the imaging object 6. Figure 5a As shown, the angle between the first X-ray source unit 21a and the second X-ray source unit 21b is 60°, and the angle between the first X-ray source unit 21a and the third X-ray source unit 21c is also 60°. That is, the angle between any two of the three X-ray source units 21 is 120°. With this configuration, the X-ray beams emitted by the X-ray sources 212 of the three X-ray source units 21 cover the imaging object 6, enabling the acquisition of more longitudinal projection information and further improving the longitudinal resolution.

[0060] It is understandable that when the area array source 2 includes three X-ray source units 21, the detector 32 can also be an arc-shaped detector, which is embedded inside the detection platform 31, such as... Figure 5b As shown.

[0061] In some embodiments, the area array source 2 further includes a beam beamer for beaming the X-ray source 212 on the X-ray source unit 21. The beam beamer can be disposed inside the panel 211 or on the side surface of the panel 211 facing the imaging object 6. That is, a beam beamer can be placed in front of the area array source 2 or a beam beamer can be built into it to meet the imaging requirements.

[0062] As mentioned earlier, the surface array source 2 can be a flat surface array source or an arc-shaped surface array source.

[0063] When the surface array source 2 is an arc-shaped surface array source, the arc-shaped surface array source is a single surface array source; the arc-shaped surface array source includes multiple ray sources 212 distributed in an array, and the arc-shaped surface array source surrounds the imaging object 6 in a semi-enclosed shape, and the ray sources 212 are set on the side of the panel 211 facing the imaging object 6; the arc angle range of the arc-shaped surface array source is 90° to 180°.

[0064] like Figure 6 and Figure 7 As shown, the arc-shaped panel of the arc-shaped array source can be a single structure. The panel 211 (arc-shaped plate) is positioned above the detection platform 31 and the imaging object 6. The X-ray source unit 21 is fixed on the side of the panel 211 facing the imaging object 6, and there is an included angle between adjacent X-ray source units 21. Figure 6 As shown, the two ends of the panel 211 are at a certain angle α to the bottom center of the imaging object 6, and the angle α can be 90° to 180°.

[0065] like Figure 6 As shown, the X-ray sources 212 of the X-ray source unit 21 are arranged in a matrix array on the side of the panel 211 (arc plate) facing the imaging object 6. Each X-ray source 212 emits a cone beam of light, covering a part of the imaging object 6. When all X-ray sources 212 (light sources) are lit, they can completely cover the imaging object 6. The power supply module 1 can control the surface array source 2 to emit X-ray beams according to a specific lighting mode, so that the surface array source 2 emits X-ray beams under different coding templates. Figure 7 A schematic diagram of the structure of a breast imaging system based on a surface array source provided in this application embodiment is shown, in the case of using an arc plate and an arc surface detector.

[0066] In some embodiments, the detection module 3 further includes a pressure plate 7 for fixing the imaging object 6. The pressure plate 7 presses down on the imaging object 6 to fix the imaging target. The X-ray source 212 of the X-ray source unit 21 can emit an X-ray beam towards the imaging object 6 through the pressure plate 7. Figures 8 to 10As shown, in the acquisition system, the imaging object 6 is placed on the detection platform 31, and a pressure plate 7 fixes the imaging object 6 above it. Under the current encoding condition, the X-ray source unit 21 of the area array source 2 emits a X-ray beam (cone beam) that covers a portion of the imaging object 6. The detector 32 receives the X-ray beams emitted by all X-ray sources 212 in the area array source 2. During the acquisition process, one X-ray source unit 21 is first illuminated. After all encoding methods are acquired, another X-ray source unit 21 is illuminated, completing the acquisition of all set encodings.

[0067] During the acquisition process, each X-ray source unit 21 emits a cone beam of light, covering a portion of the imaging object 6. When all light sources are lit, the imaging object 6 can be completely covered. The power supply module 1 controls the X-ray source unit 21 to emit X-ray beams under different coding templates according to a specific lighting mode. During the acquisition process, the detector 32 receives information from all X-ray beams under the coding templates.

[0068] It should be noted that during the acquisition process, the illumination mode can be customized according to the imaging object 6, or commonly used compressed sensing templates can be used, such as: Hadamard template, orthogonal template, Gaussian random matrix template, etc.

[0069] After the data acquisition is completed, the coded luminescent cone beam is de-aliased to obtain a single-point cone beam. Then, through the rearrangement of the projection, parallel beams at different angles are obtained, thus achieving virtual rotation.

[0070] In some embodiments, the image reconstruction module 5 includes a correction unit, a preprocessing unit, and a reconstruction unit connected in sequence. The correction unit is used to perform correction processing on the projection data. The correction processing includes bright field correction, dark field correction, zero field correction, and detection response correction. The correction unit includes a judgment unit and a correction selection unit. The correction selection unit includes a phantom correction module and a phantomless correction module. The judgment unit is used to determine whether a correction phantom exists in the module. The correction selection unit is used to select the phantom correction module to perform correction processing on the projection data when a correction phantom exists in the module, and to select the phantomless correction module to perform correction processing on the projection data when no correction phantom exists in the module. The preprocessing unit is used to preprocess the corrected projection data. The preprocessing includes beam shape correction and light intensity correction. The reconstruction unit is used to design differential constraint terms based on the differential relationship between the angle of the virtual rotation projection and the detector, and to optimize and solve the differential relationship based on the differential constraint terms to reconstruct the preprocessed projection data and obtain the internal structure of the imaging object.

[0071] like Figure 11As shown, specifically, the image reconstruction module 5 includes a phantom-free correction scheme and a phantom-based correction scheme. The judgment unit within the correction unit first determines whether a correction phantom exists. If a correction phantom exists, the correction selection unit selects the correction method with the correction phantom to correct the projection data; if no correction phantom exists, the correction selection unit selects the correction method without the correction phantom to correct the projection data. The preprocessing unit is used to address the issue of inconsistent current levels under different illumination modes.

[0072] In summary, the breast imaging system based on a static structure using a planar array source provided in this application firstly significantly increases the scanning range by arranging multiple sets of flat or arc-shaped planar array sources around the object to be reconstructed; secondly, by having each radiation source cover only a portion of the imaging object and emitting light through encoding, extremely low-dose scanning can be achieved, reducing radiation risk; thirdly, dealiasing is performed based on the encoded measurement data to obtain a cone-beam projection of a single-point source, which is then arranged into parallel beam projections at different angles to obtain a virtual rotation of the imaging object; and fourthly, the design of the image reconstruction module incorporates the angle of the measurement data and the differential relationship of the detector, improving the reconstruction quality.

[0073] like Figure 12 As shown in the embodiments of this application, a breast imaging method based on a planar array source is also provided. The method uses the breast imaging system based on a planar array source described in the above embodiments for CT imaging, and includes the following steps:

[0074] Step S1: Set imaging parameters.

[0075] Step S2: Place the imaging object on the detection platform and set the angle between the panels of adjacent X-ray source units, or the radian angle of the arc surface array source.

[0076] Step S3: Under the encoding template, addressably illuminate the X-ray source of the X-ray source unit.

[0077] Step S4: The detector collects the projection information of all the X-ray beams emitted by the X-ray source under the coded template to obtain projection data.

[0078] Step S5: By rearranging the panel angles of the X-ray source unit, obtain the virtual rotational projection of the surface array source onto the imaging object.

[0079] Step S6: Based on the differential relationship between the virtual rotation projection angle and the detector, design differential constraint terms, optimize and solve the differential relationship based on the differential constraint terms, reconstruct the internal structure of the imaging object from the preprocessed projection data.

[0080] like Figure 13As shown, during the acquisition process, imaging parameters are first set, and the area array sources are controlled in the set order. Different encoding methods are loaded. After determining whether the current encoding sampling is complete and acquiring data from all area array sources, the acquired data is input into the image reconstruction module, which includes a data preprocessing module (preprocessing unit) and an iterative reconstruction module (reconstruction unit) based on differential relationships.

[0081] In some embodiments, the detector receives information about all the X-ray beams emitted by the X-ray source under the coded template to obtain projection data, including: under different coded templates, the detector samples the projection information of all the X-ray beams emitted by the X-ray source to obtain projection data.

[0082] Specifically, during the projection generation process, a control circuit is used to addressably illuminate the ray source. Here, Pattern = {S1, S2, ..., S...} i ...,S N Given N designed irradiation scheme sequences, the ideal acquisition process can be represented as follows:

[0083]

[0084] Where b represents the measurement data, Let M represent the sampling matrix, M represent the number of light sources, 1 indicates that the light source at this location is lit in k measurements, P represent the projection data matrix, which is the projection data of each point source, mathematically equal to Af, where A is the known projection matrix, f is the image to be reconstructed, and Pij represents the measurement data received by the d-th detector from the j-th light source.

[0085] The process of recovering the imaged object f from the measurement data b is a typical inverse problem. Based on Bayesian estimation, by maximizing the posterior probability, the following optimization equation can be constructed and solved:

[0086]

[0087] Where w is the weight, R i (f) is the image domain-based regularization term, R j (P) is the regularization term based on the projection domain, R k (P) is a regularization term based on both projection and image domains.

[0088] In the image domain regularization term, based on the prior information of the image, regularization terms based on compressed sensing, such as Total Variation (TV) and Dictionary Learning (DL), can be selected. In the projection domain regularization term, Total Variation (TV) can be selected as the regularization term.

[0089] In designing R kIn (P), the differential constraint terms are designed using the differential relationship between the projection and the angle and the detector. For example, the following relationship can be used:

[0090]

[0091] In the two-dimensional case, θ⊥=(sinθ,-cosθ), x is the coordinate of the image, B(.) represents the function that transforms the aliased projection data into a virtual rotational projection, and t represents the detector index.

[0092] The above optimization problem can be solved using the alternating multiplier method.

[0093] The above problem can also be viewed as an optimization problem based on partial differential equation constraints, which can be described as:

[0094]

[0095] Where y(x) is the state function, u(x) is the control function, J is the objective function in integral form, and F is the partial differential equation function. The quality of image reconstruction can be constrained by constructing the differential relationship between the angle of the known measurement data and the detector as the control function u(x).

[0096] Within this framework, the above problem can be described as:

[0097]

[0098] F is a partial differential equation function, and its design is not unique. By introducing a virtual detector plane and a virtual rotation center, the above problem can be specifically addressed as follows:

[0099]

[0100] Where p represents the projection measurement data, η is the detector index, H is the height of the light source from the detector, d is the height of the virtual rotation center from the detector, o is the virtual detector plane index, and θ is the angle between the ray and the detector normal. Let p be the p-norm of u(P).

[0101] In addition, we can also choose:

[0102] or Construct optimization equations and solve them.

[0103] For the above optimization problem, a traditional iterative approach can be used to solve it, or a deep learning approach can be nested, using a physical neural network (PINN) to solve the partial differential equation and then substituting it into the iterative framework for the solution.

[0104] In some embodiments, by rearranging the angles of the panel of the X-ray source unit, a virtual rotational projection of the area array source onto the imaging object is obtained, including: using a coded luminescent cone beam to dealias and obtain a single-point cone beam; rearranging the projections of the X-ray source unit to obtain parallel beams at different angles, thereby obtaining a virtual rotational projection; and introducing differential relations on this basis to reconstruct a high-quality reconstructed image.

[0105] Figure 14 As an example of coded sampling in a breast imaging system based on a planar array source, the coded sampling process begins as follows: the X-ray source unit emits a cone-shaped beam of light, covering a portion of the object being imaged; illuminating all light sources completely covers the object. The power module controls the planar array source to emit X-ray beams under different coded templates according to a specific illumination pattern. The detector receives information from all X-ray beams under their respective coded templates. After sampling of all coded templates, dealiasing is performed to obtain the single-point-source cone-beam projection of the current planar array X-ray source. By rearranging the angles, a virtual rotational projection of the planar array X-ray source onto the object is obtained.

[0106] The breast imaging method based on a planar array source provided in this application uses the breast imaging system based on a planar array source in the above embodiment to perform CT imaging. It dealiased the encoded measurement data to obtain the cone-beam projection of a single source, and then arranged the parallel beam projections at different angles to obtain the virtual rotation of the imaging object. Furthermore, through the design of the image reconstruction module, the angle of the measurement data and the differential relationship of the detector are introduced to improve the reconstruction quality.

[0107] refer to Figure 15 Another embodiment of this application provides an electronic device, including: at least one processor 110; and a memory 111 communicatively connected to the at least one processor; wherein the memory 111 stores instructions executable by the at least one processor 110, the instructions being executed by the at least one processor 110 to enable the at least one processor 110 to perform any of the above method embodiments.

[0108] The memory 111 and processor 110 are connected via a bus, which may include any number of interconnecting buses and bridges, connecting various circuits of one or more processors 110 and memory 111. The bus may also connect various other circuits, such as peripheral devices, voltage regulators, and power management circuits, which are well known in the art and therefore will not be described further herein. A bus interface provides an interface between the bus and the transceiver. The transceiver may be a single element or multiple elements, such as multiple receivers and transmitters, providing a unit for communicating with various other devices over a transmission medium. Data processed by processor 110 is transmitted over a wireless medium via an antenna, which further receives data and transmits it to processor 110.

[0109] Processor 110 is responsible for managing the bus and general processing, and can also provide various functions, including timing, peripheral interfaces, voltage regulation, power management, and other control functions. Memory 111 can be used to store data used by processor 110 during operation.

[0110] Based on the above technical solutions, this application provides a breast imaging system, method, device, and storage medium based on a planar array source. The breast imaging system includes: a power module and a planar array source, a detection module, a data acquisition module, and an image reconstruction module connected to the power module; the detection module includes a detection platform for placing the imaging object, a detector located within the detection platform, and a connecting arm for connecting to the planar array source; the planar array source is located on the opposite side of the detection platform and is used to emit X-ray beams towards the imaging object; the planar array source can be a flat planar array source or an arc-shaped planar array source; when a flat planar array source is used, the flat planar array source includes at least two X-ray source units, each X-ray source unit including a panel and multiple X-ray sources arranged in an array, and the X-ray beams... The source is positioned on the side of the panel facing the imaging object, and there is an angle between adjacent panels, with the angle ranging from 90° to 180°. When an arc-shaped surface array source is used, only one surface array source is needed. The surface array source partially surrounds the imaging object, and the arc angle ranges from 90° to 180°. The detector is used to receive the X-ray beam emitted by the surface array source. It can be a flat panel detector or an arc-shaped detector. After receiving the acquisition command issued by the data acquisition module, the detector acquires the projection data of the surface array source and sends the acquired projection data to the image reconstruction module. The image reconstruction module reconstructs the projection data to realize the virtual rotation of the imaging object. Based on this, a differential relationship is introduced to finally obtain a high-quality reconstructed image.

[0111] The breast imaging system based on a planar array source provided in this application firstly greatly increases the scanning range by arranging multiple sets of flat planar array sources or arc-shaped planar array sources around the object to be reconstructed. Secondly, by having each radiation source cover only a portion of the imaging object and emitting light through encoding, extremely low-dose scanning can be achieved, reducing radiation risk. Thirdly, dealiasing is performed based on the encoded measurement data to obtain a cone-beam projection of a single-point source, which is then arranged into parallel beam projections at different angles to obtain a virtual rotational projection of the imaging object. Fourthly, the reconstruction quality is improved by incorporating the angle of the measurement data and the differential relationship of the detector through the design of the image reconstruction module.

[0112] Those skilled in the art will understand that the above-described embodiments are specific examples of implementing this application, and in practical applications, various changes in form and detail may be made without departing from the spirit and scope of this application. Any person skilled in the art can make their own modifications and alterations without departing from the spirit and scope of this application; therefore, the scope of protection of this application should be determined by the scope defined in the claims.

Claims

1. A breast imaging system based on a planar array source, characterized in that, include: A power module and a surface array source, a detection module, a data acquisition module, and an image reconstruction module connected to the power module; The detection module includes a detection platform for placing the imaging object, a detector located within the detection platform, and a connecting arm for connecting the area array source. The area array source is located on the opposite side of the detection platform and is used to emit X-ray beams toward the imaging object; the area array source is a flat area array source or an arc-shaped area array source. When the area array source is a flat area array source, the flat area array source includes at least two X-ray source units. Each X-ray source unit includes a panel and a plurality of X-ray sources arranged in an array. The X-ray sources are disposed on the side of the panel facing the imaging object, and there is an included angle between adjacent panels. The included angle ranges from 90° to 180°. When the area array source is an arc-shaped area array source, the arc-shaped area array source is a single area array source; The arc-shaped surface array source includes multiple ray sources arranged in an array, and the arc-shaped surface array source surrounds the imaging object in a semi-enclosed shape. The ray sources are located on the side of the panel facing the imaging object; the arc angle of the arc-shaped surface array source ranges from 90° to 180°. The detector is a flat-panel detector or a curved-surface detector. The detector receives the X-ray beam emitted by the surface array source. After receiving the acquisition command from the data acquisition module, the detector acquires the projection data of the surface array source and sends the acquired projection data to the image reconstruction module. The image reconstruction module reconstructs the projection data, using a coded, emitting cone beam to dealias and obtain a single-point cone beam. By rearranging the projections of the X-ray source units, parallel beams at different angles are obtained, acquiring the virtual rotational projection of the surface array source onto the imaging object. Based on the differential relationship between the angle of the virtual rotational projection and the detector, differential constraint terms are designed, and the differential relationship is optimized and solved based on the differential constraint terms. The preprocessed projection data is reconstructed to obtain the internal structure of the imaging object, thereby achieving three-dimensional breast imaging. In designing the regularization term based on both projection and image domains, the differential constraint term is designed using the differential relationship between the projection and the angle and the detector. The relationship of the differential constraint term is shown below: In the two-dimensional case, , x The coordinates of the image, This represents a function that converts aliased projection data into a virtual rotational projection. t Indicates the detector index.

2. The breast imaging system based on a planar array source according to claim 1, characterized in that, The area array source is located above, below, or to the side of the imaging object, and the detector is disposed on the side of the imaging object away from the area array source.

3. The breast imaging system based on a planar array source according to claim 1, characterized in that, When the area array source is a flat area array source, the flat area array source includes two ray source units, both of which are positioned facing the imaging object; The two X-ray source units are located directly above, directly below, or to the side of the imaging object, and the two X-ray source units are located on the same side of the imaging object; The two X-ray source units are symmetrical about the longitudinal central axis of the imaging object.

4. The breast imaging system based on a planar array source according to claim 1, characterized in that, When the area array source is a flat area array source, the flat area array source includes three ray source units, all of which are arranged facing the imaging object; The flat panel array source includes a first ray source unit and a second ray source unit and a third ray source unit located on both sides of the first ray source unit; the first ray source unit is located directly above, directly below, or to the side of the imaging object, and the first ray source unit, the second ray source unit, and the third ray source unit are located on the same side of the imaging object; The second and third X-ray source units are symmetrical about the longitudinal central axis of the imaging object.

5. The breast imaging system based on a planar array source according to claim 1, characterized in that, The detection module also includes a pressure plate for fixing the imaging object.

6. The breast imaging system based on a planar array source according to claim 1, characterized in that, The image reconstruction module includes a correction unit, a preprocessing unit, and a reconstruction unit connected in sequence. The correction unit is used to perform correction processing on the projection data; the correction processing includes bright field correction, dark field correction, zero field correction, and probe response correction; the correction unit includes a judgment unit and a correction selection unit; the correction selection unit includes a phantom correction module and a phantomless correction module; the judgment unit is used to determine whether a correction phantom exists in the module; the correction selection unit is used to select the phantom correction module to perform correction processing on the projection data when a correction phantom exists in the module; and to select the phantomless correction module to perform correction processing on the projection data when no correction phantom exists in the module. The preprocessing unit is used to preprocess the corrected projection data; the preprocessing includes beam shape correction and light intensity correction. The reconstruction unit is used to design differential constraint terms based on the differential relationship between the angle of the virtual rotation projection and the detector, and to optimize and solve the differential relationship based on the differential constraint terms, thereby reconstructing the internal structure of the imaging object from the preprocessed projection data.

7. The breast imaging system based on a planar array source according to claim 1, characterized in that, The area array source includes a beam beamer for beaming the radiation sources on the radiation source unit; The beam snoop is disposed inside the panel, or the beam snoop is disposed on the side surface of the panel facing the imaging object.

8. A breast imaging method based on a planar array source, comprising CT imaging using a breast imaging system based on a planar array source as described in any one of claims 1 to 7, characterized in that, include: Set imaging parameters; The object to be imaged is placed on the detection platform, and the angle between the panels of adjacent X-ray source units is set. Under the encoding template, the ray source of the ray source unit is addressed and illuminated; The detector collects the projection information of all the X-ray beams emitted by the X-ray source under the coded template to obtain projection data; By rearranging the angles of the panel of the X-ray source unit, a virtual rotational projection of the area array source onto the imaging object is obtained. Based on the differential relationship between the virtual rotation projection angle and the detector, differential constraint terms are designed, and the differential relationship is optimized and solved based on the differential constraint terms. The preprocessed projection data is then reconstructed to obtain the internal structure of the imaging object.

9. The breast imaging method based on a planar array source according to claim 8, characterized in that, The detector receives information from all the radiation beams emitted by the radiation source under the encoded template to obtain projection data, including: Under different encoding templates, the detector samples the projection information of all the X-ray beams emitted by the X-ray source to obtain projection data.

10. The breast imaging method based on a planar array source according to claim 8, characterized in that, By rearranging the angles of the panels of the ray source unit, a virtual rotational projection of the area array source onto the imaging object is obtained, including: By dealiasing the coded luminescent cone beam, a single-point cone beam is obtained; By rearranging the projections of the X-ray source unit, parallel beams at different angles are obtained, thus achieving a virtual rotational projection.

11. An electronic device, characterized in that, include: At least one processor; as well as, A memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, the instructions being executed by the at least one processor to enable the at least one processor to perform the breast imaging method based on a planar array source as described in any one of claims 8 to 10.

12. A computer-readable storage medium storing a computer program, characterized in that, When the computer program is executed by the processor, it implements the breast imaging method based on a planar array source as described in any one of claims 8 to 10.

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