CT imaging system

Abstract

Embodiments of the present application provide a CT imaging system, relating to the field of radiation scanning technology. The imaging system comprises: an imaging channel for placing an object to be imaged during imaging; M distributed radiation sources arranged at intervals along the circumference of the imaging channel, at least one of the distributed radiation sources comprising q target points; N detectors arranged at intervals along the circumference of the imaging channel, comprising a first sub-detector; the CT imaging system comprises a plurality of imaging assemblies, the imaging assembly comprising at least one distributed radiation source and at least one first sub-detector, in the same imaging assembly, the distributed radiation source and the first sub-detector are arranged face to face in the radial direction of the detection channel, and at least one target point of the distributed radiation source and at least a part of the first sub-detector are located in the same plane perpendicular to the first direction z. At least one of the M distributed radiation sources comprises q target points arranged obliquely relative to the first direction z.

Description

Technical Field

[0001] This invention relates to the field of radiation scanning technology, and more specifically, to a CT imaging system. Background Technology

[0002] CT (Computed Tomography) scanning systems are a non-destructive testing technology widely used in biomedicine, image-guided interventional procedures, security inspection, industrial and agricultural production, geophysics, and petroleum exploration. They offer fast imaging speeds, high precision, and can fully present the three-dimensional information of the examined area.

[0003] With the continuous expansion of CT applications, more and more fields are demanding rapid CT scans. For example, CT scans of moving tissues and organs in clinical diagnosis. Spiral CT significantly reduces scan time thanks to slip ring technology, but the rotation speed of the slip rings has essentially reached its limit, making it difficult to further shorten the scan time. The emergence of multi-source spiral CT has further reduced CT scan time, offering a clear advantage in scan speed; the more sources, the shorter the scan time. However, multi-source systems also bring challenges such as high cost and massive data volume.

[0004] In recent years, the emergence of distributed light sources has made it possible to further shorten scanning time. Distributed light sources avoid the use of slip rings, and imaging can be achieved simply by sequential exposure, completely eliminating mechanical movement. However, existing distributed light source scanning schemes generally suffer from problems such as finite angle scanning, data truncation, and motion artifacts. These problems increase the difficulty of data processing and image reconstruction, and also affect image quality.

[0005] It should be noted that the information disclosed in this section is only used to understand the background of the inventive concept of the present invention. Therefore, the above information may include information that does not constitute prior art. Summary of the Invention

[0006] In view of at least one aspect of the above-mentioned technical problems, the present invention provides a CT imaging system, comprising: an imaging channel, at least a portion of which extends along a first direction z, the imaging channel being used to place an object to be imaged during imaging; M distributed X-ray sources, the M distributed X-ray sources being arranged circumferentially at intervals along the imaging channel, at least one of the distributed X-ray sources including q target points, the q target points being configured to emit X-rays, where M and q are both positive integers greater than or equal to 2; and N detectors, the N detectors being arranged circumferentially at intervals along the imaging channel, the N detectors being used to detect X-rays emitted from the M distributed X-ray sources and passing through the object to be imaged, where N is a positive integer greater than or equal to M. The detector includes a first sub-detector, the CT imaging system includes multiple imaging components, each imaging component includes at least one of the distributed X-ray sources and at least one of the first sub-detectors, in the same imaging component, the distributed X-ray sources and the first sub-detectors are arranged face-to-face in the radial direction of the detection channel, and in the same imaging component, at least one target point of the distributed X-ray source and at least a portion of the first sub-detector are located in the same plane perpendicular to the first direction z, the radial direction being perpendicular to the first direction z; and at least q target points of at least one of the M distributed X-ray sources are arranged at an angle relative to the first direction z.

[0007] According to some exemplary embodiments, in at least one of the M distributed radiation sources, the q target points of the same distributed radiation source are arranged at intervals along a first straight line, the extension direction of the first straight line being inclined relative to the first direction z.

[0008] According to some exemplary embodiments, at least one of the M distributed radiation sources includes a radiation source body and q target points mounted on the radiation source body, the radiation source body being tilted relative to the first direction z.

[0009] According to some exemplary embodiments, at least one of the M distributed radiation sources includes a radiation source body and q target points mounted on the radiation source body, the radiation source body being perpendicular to the first direction z, and the q target points mounted on the radiation source body being arranged at an angle relative to the first direction z.

[0010] According to some exemplary embodiments, the q target points of the M distributed radiation sources are respectively arranged at an angle relative to the first direction z, and the first straight line containing at least two of the q target points has an unequal angle of inclination relative to the first direction z.

[0011] According to some exemplary embodiments, the first straight line containing the q target points of the M distributed radiation sources has an angle of inclination relative to the first direction z that is equal to each other.

[0012] According to some exemplary embodiments, the CT imaging system further includes a controller configured to control the beam interval time of a plurality of targets and control the movement speed of the object to be imaged.

[0013] According to some exemplary embodiments, the tilt angle of the extension direction of the first straight line relative to the first direction z is θ, and the tilt angle θ satisfies the following relationship: cosθ=v*t / s, where s is the distance between two adjacent target points along the extension direction of the first straight line among the q target points, v is the moving speed of the object to be imaged, and t is the beam exit interval time.

[0014] According to some exemplary embodiments, the M distributed radiation sources each include q target points, and the q target points of the M distributed radiation sources each have z-direction position coordinates in the first direction z; and the z-direction position coordinates of the i-th target point of the M distributed radiation sources are equal to each other, where 1≤i≤q.

[0015] According to some exemplary embodiments, the M distributed radiation sources each include q target points, and the q target points of the M distributed radiation sources each have z-direction position coordinates in the first direction z; and the z-direction position coordinates of the i-th target point of the M distributed radiation sources are not equal to each other, where 1≤i≤q.

[0016] According to some exemplary embodiments, the controller is configured to control multiple target points with equal z-axis position coordinates of the M distributed ray sources to emit beams simultaneously.

[0017] According to some exemplary embodiments, the detector further includes a second sub-detector, wherein at least one of the second sub-detectors is disposed on at least one side of at least one of the distributed radiation sources in the first direction z.

[0018] According to some exemplary embodiments, the M distributed X-ray sources are uniformly arranged at equal intervals along the circumference of the imaging channel; and / or, the CT imaging system includes M first sub-detectors, which are uniformly arranged at equal intervals along the circumference of the imaging channel.

[0019] According to some exemplary embodiments, the radiation angle coverage range of the M distributed radiation sources is 90°-120°; or the radiation angle coverage range of the M distributed radiation sources is 120°-150°; or the radiation angle coverage range of the M distributed radiation sources is 140°-160°.

[0020] According to some exemplary embodiments, the CT imaging system includes M first sub-detectors, wherein the M distributed X-ray sources and the M first sub-detectors are arranged alternately circumferentially along the imaging channel.

[0021] According to some exemplary embodiments, the second sub-detector is arranged at an angle relative to the first direction z; or, the second sub-detector is arranged perpendicular to the first direction z.

[0022] According to an embodiment of the present invention, by tilting multiple target points of the distributed X-ray source, the traditional design of circumferential arrangement is broken through, enabling the imaging system to detect from multiple angles simultaneously, improving the accuracy and breadth of detection, thereby effectively solving the problems of limited angle scanning and data truncation. Attached Figure Description

[0023] The above and other objects, features and advantages of the present invention will become more apparent from the following description of embodiments of the invention with reference to the accompanying drawings, in which:

[0024] FIG. 1 This is a schematic diagram of the structure of a X-ray scanning imaging system according to some exemplary embodiments of the present invention;

[0025] FIG. 2 This is a schematic diagram of the structure of a CT imaging system based on a three-segment coplanar scanning structure according to some exemplary embodiments of the present invention;

[0026] FIG. 3A Based on some exemplary embodiments of the present invention FIG. 2 A three-dimensional schematic diagram of a CT imaging system, which schematically shows the arrangement of multiple distributed X-ray sources and multiple detectors;

[0027] FIG. 3B Based on some exemplary embodiments of the present invention FIG. 2 A schematic diagram of the imaging optical path of a CT imaging system;

[0028] FIG. 4A This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein two X-ray sources and two detectors are schematically shown.

[0029] FIG. 4B This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein five X-ray sources and five detectors are schematically shown.

[0030] FIG. 4CThis is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein multiple X-ray sources and multiple detectors are schematically shown.

[0031] FIG. 5 A three-dimensional schematic diagram of a CT imaging system according to some exemplary embodiments of the present invention is shown, wherein the detectors include two types of detectors;

[0032] FIG. 6 Based on some exemplary embodiments of the present invention FIG. 5 A schematic diagram of the imaging optical path of a CT imaging system;

[0033] FIG. 7 This is a schematic diagram of the imaging optical path of a CT imaging system according to some other exemplary embodiments of the present invention;

[0034] FIG. 8A This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein two X-ray sources and two detectors are schematically shown.

[0035] FIG. 8B This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein five X-ray sources and five detectors are schematically shown.

[0036] FIG. 8C This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein multiple X-ray sources and multiple detectors are schematically shown.

[0037] FIG. 8D A schematic diagram of the arrangement of a distributed radiation source and a second sub-detector according to some embodiments of the present invention is shown;

[0038] FIG. 8E A schematic diagram of the arrangement of a distributed radiation source and a second sub-detector according to other embodiments of the present invention is shown;

[0039] FIG. 9A A schematic diagram of a densely arranged detector layout design according to some embodiments of the present invention is shown;

[0040] FIG. 9B A schematic diagram of a sparsely arranged detector layout design according to other embodiments of the present invention is shown;

[0041] FIG. 9C A schematic diagram of a layout design for a hybrid arrangement of detectors according to some embodiments of the present invention is shown;

[0042] FIG. 10A A schematic diagram of the ray angle coverage range in a CT imaging system according to some embodiments of the present invention is shown;

[0043] FIG. 10B A schematic diagram of the ray angle coverage in a CT imaging system according to other embodiments of the present invention is shown;

[0044] FIG. 11A A schematic diagram of the effective imaging area in a CT imaging system according to some embodiments of the present invention is shown;

[0045] FIG. 11B A schematic diagram of the effective imaging region in a CT imaging system according to other embodiments of the present invention is shown;

[0046] FIG. 12 This is a three-dimensional schematic diagram of a CT imaging system according to some exemplary embodiments of the present invention, wherein the target point of the distributed X-ray source is tilted.

[0047] FIG. 13A This is a schematic diagram of a distributed X-ray source for a CT imaging system according to some exemplary embodiments of the present invention;

[0048] FIG. 13B This is a schematic diagram of a distributed X-ray source for a CT imaging system according to some other exemplary embodiments of the present invention;

[0049] FIG. 13C to FIG. 13E Schematic diagrams of the arrangement of distributed radiation sources and second sub-detectors according to some embodiments of the present invention are shown respectively, wherein, FIG. 13C This shows that a second sub-detector is installed on both sides of the distributed radiation source. FIG. 13D The diagram shows a second sub-detector positioned above the distributed radiation source. FIG. 13E The diagram shows a second sub-detector positioned below the distributed radiation source;

[0050] FIG. 14A A schematic diagram illustrating the arrangement of the second sub-detectors according to some embodiments of the present invention is shown;

[0051] FIG. 14B A schematic diagram of the arrangement of the second sub-detectors according to other embodiments of the present invention is shown;

[0052] FIG. 15 A flowchart of an imaging method for a CT imaging system according to some exemplary embodiments of the present invention is shown;

[0053] FIG. 16A schematic diagram of the projection surface of a CT imaging system with simultaneous beam emission from multiple targets according to some exemplary embodiments of the present invention is shown.

[0054] FIG. 17 A schematic diagram of the projection plane of a multi-target time-division beam output CT imaging system according to some embodiments of the present invention is shown;

[0055] FIG. 18A These are images obtained using imaging systems and methods from related technologies;

[0056] FIG. 18B Images obtained using the imaging system and imaging method provided in the embodiments of the present invention; and

[0057] FIG. 19 A block diagram of an electronic device suitable for implementing the imaging method according to an embodiment of the present invention is shown schematically. Detailed Implementation

[0058] Hereinafter, embodiments of the present invention will be described with reference to the accompanying drawings. However, it should be understood that these descriptions are exemplary only and are not intended to limit the scope of the invention. In the following detailed description, numerous specific details are set forth to provide a thorough understanding of the embodiments of the invention for ease of explanation. However, it will be apparent that one or more embodiments may be practiced without these specific details. Furthermore, descriptions of well-known structures and techniques are omitted in the following description to avoid unnecessarily obscuring the concept of the invention.

[0059] The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the invention. The terms “comprising,” “including,” etc., as used herein indicate the presence of the stated features, steps, operations, and / or components, but do not exclude the presence or addition of one or more other features, steps, operations, or components.

[0060] All terms used herein (including technical and scientific terms) have the meanings commonly understood by those skilled in the art, unless otherwise defined. It should be noted that the terms used herein are to be interpreted in a manner consistent with the context of this specification, and not in an idealized or overly rigid way.

[0061] When using expressions such as "at least one of A, B and C", they should generally be interpreted in accordance with the meaning that is commonly understood by those skilled in the art (e.g., "a system having at least one of A, B and C" should include, but is not limited to, a system having A alone, a system having B alone, a system having C alone, a system having A and B, a system having A and C, a system having B and C, and / or a system having A, B and C, etc.).

[0062] It should be noted that in this article, computed tomography (CT) imaging refers to the process of using X-rays to perform a tomographic scan of the object to be imaged, then converting the analog signals received by the detector into digital signals, using a computer to calculate the attenuation coefficient of each pixel, and then reconstructing the image to display the tomographic structure of each part of the object to be imaged.

[0063] The following describes embodiments of the present invention in detail, using a CT scan imaging system for luggage as an example. It should be understood that the embodiments of the present invention are not limited to CT scan imaging of luggage; they can be applied to various scanning imaging scenarios. For example, they can be applied to scanning imaging scenarios involving various different objects, including but not limited to vehicle scanning imaging, luggage / parcel scanning imaging, human or animal scanning imaging, organ / tissue scanning imaging, small object scanning imaging, and large object scanning imaging such as containers. It should be noted that the description of scanning imaging scenarios here is not exhaustive, and the exemplary descriptions below should not be construed as limiting the scope of protection of the present invention.

[0064] FIG. 1 This is a schematic diagram of the structure of a X-ray scanning imaging system according to some exemplary embodiments of the present invention. FIG. 1 In this diagram, an X-ray scanning-based CT imaging system is schematically illustrated as an example of such an imaging system. FIG. 1As shown, the CT imaging system according to this embodiment includes: a gantry 20, a transport mechanism 40, a controller 50, a data processing device 60 (e.g., a computer), an imaging channel 80, etc. The gantry 20 includes a radiation source 10, such as an X-ray machine, that emits X-rays for examination, and a detection and acquisition device 30. The imaging channel 80 extends along a first direction z and is used to place the object to be imaged 70 during the imaging process. For example, at least a portion of a support device may be disposed in the imaging channel 80, and the object to be imaged 70 may be placed on the support device. During scanning, the object to be imaged 70 may remain stationary in the imaging area. As another example, at least a portion of the transport mechanism 40 is disposed in the imaging channel 80. The transport mechanism 40 carries the object to be imaged (e.g., luggage being inspected) 70 through the scanning area between the radiation source 10 and the detection and acquisition device 30 of the gantry 20. The transport mechanism 40 can move the object to be imaged 70 along the first direction z, while the radiation emitted by the radiation source 10 can pass through the object to be imaged 70 to perform a CT scan. The detection and acquisition device 30 includes, for example, a detector and data acquisition unit with an integrated modular structure, such as a flat panel detector, for detecting X-rays transmitted through the object to be imaged 70, obtaining analog signals, and converting the analog signals into digital signals to output projection data of the object to be imaged 70 as X-rays. The controller 50 is used to control the synchronous operation of all parts of the entire system. The data processing device 60 is used to process the data acquired by the data acquisition unit, process and reconstruct the data, and output the results.

[0065] like FIG. 1 As shown, the X-ray source 10 is placed on one side where the object to be inspected can be placed, and the detection and acquisition device 30 is placed on the other side of the object to be imaged 70. The device includes a detector and a data acquisition unit for acquiring transmission data and / or multi-angle projection data of the object to be imaged 70. The data acquisition unit includes a data amplification and shaping circuit, which can operate in (current) integration mode or pulse (counting) mode. The data output cable of the detection and acquisition device 30 is connected to the controller 50 and the data processing device 60, and the acquired data is stored in the data processing device 60 according to a trigger command.

[0066] In embodiments of the present invention, a radiographic scanning imaging module may be deployed in the data processing device 60. This module includes an image recognition model or a target recognition model. The radiographic scanning imaging module can use the image recognition model or target recognition model to identify the acquired on-site data (e.g., radiographic scanning images). This identification may include target detection, for example, detecting target objects or objects of interest in the radiographic scanning images. For example, the target object or object of interest may be various contraband items. It should be understood that the specific category of the target object or object of interest depends on the scanning imaging site where the radiographic scanning imaging system is deployed; in other words, the specific category of the target object or object of interest is determined by the user of the radiographic scanning imaging system according to specific scanning imaging needs, and it can be dynamically adjusted according to the scanning imaging needs.

[0067] In embodiments of the present invention, the radiation source 10 may be, for example, an X-ray machine, and the appropriate target size of the X-ray machine can be selected according to the imaging resolution. In other embodiments, an X-ray machine may not be used; instead, a linear accelerator or the like may be used to generate the X-ray beam.

[0068] The detection and acquisition device 30 includes an X-ray detector and a data acquisition circuit, etc. The X-ray detector can be a solid-state detector, a gas detector, or other detectors, and embodiments of the present invention are not limited thereto. The data acquisition circuit includes a readout circuit, an acquisition trigger circuit, and a data transmission circuit, etc.

[0069] The combination of controller 50 and data processing device 60 includes, for example, a computer device equipped with control and data processing programs, which is responsible for controlling the operation of the CT imaging device, including mechanical rotation, electrical control, safety interlock control, etc., reconstructing CT images from projection data, training image recognition models or target recognition models, and using the trained image recognition models or target recognition models to recognize X-ray scan images, etc.

[0070] Furthermore, taking a CT imaging system with a three-segment scanning structure as an example, the embodiments of the present invention will be described in detail. It should be understood that the following CT imaging system with a three-segment coplanar scanning structure is merely an exemplary structure of a CT imaging system for ease of explanation. Those skilled in the art should understand that the number and position of the X-ray source and detector can be adjusted according to specific needs to accommodate objects of different sizes and shapes to be imaged.

[0071] FIG. 2 This is a schematic diagram of a CT imaging system based on a three-segment coplanar scanning structure according to some exemplary embodiments of the present invention. FIG. 3A Based on some exemplary embodiments of the present invention FIG. 2A three-dimensional schematic diagram of a CT imaging system, which schematically shows the arrangement of multiple distributed X-ray sources and multiple detectors. FIG. 3B Based on some exemplary embodiments of the present invention FIG. 2 A schematic diagram of the imaging optical path of a CT imaging system. FIG. 4A This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein two X-ray sources and two detectors are schematically shown. FIG. 4B This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein five X-ray sources and five detectors are schematically shown. FIG. 4C This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein multiple X-ray sources and multiple detectors are schematically shown.

[0072] Combined with reference FIG. 1 to FIG. 4C In some exemplary embodiments, the X-ray source 10 of the CT imaging system 100 may include multiple distributed X-ray sources, for example, M distributed X-ray sources, where M is a positive integer greater than or equal to 2. FIG. 2 to FIG. 3B In the exemplary embodiment shown, M=3, meaning there are 3 distributed radiation sources. FIG. 4A In the exemplary embodiment shown, M=2, meaning there are two distributed radiation sources. FIG. 4B In the exemplary embodiment shown, M=5, meaning there are 5 distributed radiation sources. FIG. 4C In the exemplary embodiment shown, M is multiple, that is, multiple distributed radiation sources are provided. For ease of description, the M distributed radiation sources are respectively numbered as the first distributed radiation source 101, the second distributed radiation source 102, the third distributed radiation source 103, ... the Mth distributed radiation source 10M.

[0073] In embodiments of the present invention, the distributed X-ray source includes multiple target points (also known as focal points). For example, multiple X-ray target points can be arranged at high density within a single X-ray tube vacuum chamber. Compared to a traditional single X-ray source, the distributed X-ray source has multiple independent X-ray emission points, which can operate independently and be controlled individually. For example, the distributed X-ray source developed by the applicant of this application can integrate hundreds of X-ray target points within a single X-ray tube, each of which can be independently controlled and quickly switched as needed. For example, the emission of each target point can be precisely controlled, including parameters such as X-ray intensity and emission time, allowing for flexible adjustment of X-ray output based on different scanning locations, object density, and other factors during CT scans, thereby obtaining higher-quality images. For example, the intensity distribution of the X-ray beam can be modulated by controlling the X-ray intensity of different target points to adapt to the imaging requirements of different objects. Furthermore, by employing a multi-target distributed X-ray source, rapid scanning imaging capabilities can be achieved. Due to the presence of multiple X-ray target points, the distributed X-ray source can simultaneously or rapidly scan target objects sequentially from multiple different locations, greatly improving scanning speed. Compared to traditional CT scans, this method can acquire complete image information of an object in a shorter time, which is of great significance for scenarios requiring rapid imaging, such as medical emergencies and security checks. Furthermore, it can achieve high-quality imaging results; the collaborative work of multiple targets and precise control capabilities enable distributed X-ray sources to provide higher resolution and lower noise images. When imaging complex objects or minute structures, it can more clearly reveal the internal structure and details of the object, providing more accurate information for doctors' diagnoses or other applications.

[0074] Combined with reference FIG. 1 to FIG. 4C In some exemplary embodiments, the detection and acquisition device 30 of the CT imaging system 100 may include multiple detectors, for example, N detectors, where N is a positive integer greater than or equal to 2. For example, N is a positive integer greater than or equal to M. FIG. 2 to FIG. 3B In the exemplary embodiment shown, N=3, meaning there are 3 detectors. FIG. 4A In the exemplary embodiment shown, N=2, meaning there are 2 detectors. FIG. 4B In the exemplary embodiment shown, N=5, meaning there are 5 detectors. FIG. 4C In the exemplary embodiment shown, N is multiple, that is, multiple detectors are provided. For ease of description, the N detectors are respectively numbered as the first detector 301, the second detector 302, the third detector 303, ... the Nth detector 30N.

[0075] Reference FIG. 2 to FIG. 4CIn some exemplary embodiments, among the M distributed radiation sources, at least one distributed radiation source includes q target points 1011, where q is a positive integer greater than or equal to 2. For example, each of the M distributed radiation sources includes more than two target points. FIG. 2 In the illustrated embodiment, q=11, meaning a distributed radiation source comprises 11 target points. For ease of description, the q target points are designated as target point 111, target point 112, target point 113, ..., target point 11q. Exemplarily, the q target points are configured to be activated in a predetermined order to emit radiation.

[0076] It should be understood that the 2, 3, or 5 distributed X-ray sources and 2, 3, or 5 detectors mentioned here are merely exemplary embodiments and should not be construed as a limitation on the number of distributed X-ray sources and detectors in the embodiments of the present invention. In other embodiments, the imaging system may include fewer distributed X-ray sources and detectors, such as 4, or more, such as 6, 8, 10, or more. When more than 2 distributed X-ray sources and detectors are set, X-rays can be emitted and received simultaneously or sequentially from different angles and positions, thereby improving the imaging speed and resolution. Alternatively, 3, 4, or 5 distributed X-ray sources and detectors can be set; the combination of more than 3 distributed X-ray sources and detectors can provide a more comprehensive and detailed scan for imaging complex objects. Furthermore, setting 6 distributed X-ray sources and detectors can achieve X-ray coverage over a larger area, which has significant advantages for imaging large objects or specific application scenarios requiring high resolution. In some cases, more than eight distributed X-ray sources and detectors can be configured. This configuration allows for more complex scanning modes and multi-angle imaging, providing richer image information for security checks, medical diagnoses, and research analyses. It should be understood that as the number of X-ray sources increases, the imaging system can achieve more refined imaging, making it more adept at observing minute structures and performing high-precision detection tasks. In embodiments of this invention, the number of distributed X-ray sources and detectors can be flexibly adjusted according to specific application needs to meet the CT imaging requirements of different fields and scenarios.

[0077] It should also be understood that FIG. 2The distributed X-ray source in the figures, including 11 target points, and the number of target points shown in other figures are merely exemplary embodiments and should not be construed as a limitation on the number of target points in the embodiments of the present invention. In other embodiments, the distributed X-ray source of the imaging system may include fewer target points, such as fewer than 10, or more target points, such as 20, 50, 100, hundreds, or more. In the embodiments of the present invention, the number of target points in the distributed X-ray source can be flexibly adjusted according to specific application requirements to meet the CT imaging requirements in different fields and scenarios.

[0078] It should be noted that, unless otherwise specified, the terms "first," "second," "third," etc., used herein are merely for the convenience of referring to different components, such as distributed radiation sources, targets, and detectors, and should not be construed as imposing any limitation on the structure of such components. In embodiments of the present invention, the structures of the first distributed radiation source 101, the second distributed radiation source 102, the third distributed radiation source 103, ... the Mth distributed radiation source 10M may be identical, or a subset of the distributed radiation sources may have identical structures while other subsets may have different structures. For example, the first distributed radiation source 101, the second distributed radiation source 102, the third distributed radiation source 103, ... the Mth distributed radiation source 10M may include the same number of targets, or a subset of the distributed radiation sources may include a different number of targets than another subset, or any two distributed radiation sources may include different numbers of targets. In embodiments of the present invention, the structures of the first detector 301, the second detector 302, the third detector 303, ... the Nth detector 30N may be the same, or some of the detectors may have the same structure while others may have different structures.

[0079] It should also be noted that the structure of distributed X-ray sources is highly flexible and diverse. Their design and construction depend on various factors, including but not limited to specific application scenarios, imaging requirements, technical requirements, and engineering feasibility. Each distributed X-ray source can be independently optimized and adjusted according to actual conditions to achieve optimal performance. Whether in medical diagnostics, security inspections, industrial testing, or scientific research, the structure of distributed X-ray sources can be customized according to different goals and tasks, without being constrained by the simple numbering method used here. This numbering method is merely for the purpose of distinguishing and discussing individual distributed X-ray sources in the text description and should not be misunderstood as setting any fixed pattern or limitation for their complex and sophisticated structure.

[0080] Combined with reference FIG. 1 to FIG. 4C In this document, for ease of description, the first direction z, the second direction x, the third direction y, the circumferential direction c of the imaging channel, and the radial direction r are described separately. For example, the first direction z corresponds to the extension direction of the imaging channel 80, or, in the case of movement of the object 70 being imaged, its direction of movement. The second direction x and the third direction y intersect, and the first direction z is perpendicular to both the second direction x and the third direction y. For example, the second direction x corresponds to the width direction of the CT imaging system, and the third direction y corresponds to the height direction of the CT imaging system. The circumferential direction c of the imaging channel intersects with the radial direction r, and the first direction z is perpendicular to both the circumferential direction c and the radial direction r of the imaging channel. For example, the radial direction r of the imaging channel 80 corresponds to the direction from the center of the imaging channel 80 to the outer periphery of the imaging channel 80, and the circumferential direction c of the imaging channel 80 corresponds to the direction surrounding the imaging channel 80.

[0081] Reference FIG. 2 to FIG. 4C M distributed X-ray sources 101~10M are arranged along the circumferential direction c of the imaging channel 80. For example, the M distributed X-ray sources 101~10M are arranged at intervals along the circumferential direction c of the imaging channel 80.

[0082] Continue to refer to FIG. 2 to FIG. 4C N detectors 301~30N are arranged along the circumferential direction c of the imaging channel 80. For example, the N detectors 301~30N are arranged at intervals along the circumferential direction c of the imaging channel 80.

[0083] In some exemplary embodiments, M distributed X-ray sources 101-10M and N detectors 301-30N are arranged alternately along the circumferential direction c of the imaging channel 80. For example, the M distributed X-ray sources 101-10M are arranged at equal intervals along the circumferential direction c of the imaging channel 80, with one detector positioned between two adjacent distributed X-ray sources. The N detectors 301-30N are arranged at equal intervals along the circumferential direction c of the imaging channel 80, with one distributed X-ray source positioned between two adjacent detectors.

[0084] It should be understood that FIG. 2 , FIG. 3B , FIG. 4A to FIG. 4C The diagrams show the planes perpendicular to the first direction z, i.e. FIG. 2 , FIG. 3B , FIG. 4A to FIG. 4C The plane of the paper is perpendicular to the first direction z. For example... FIG. 2 , FIG. 3B , FIG. 4A to FIG. 4C As shown, in a plane perpendicular to the first direction z, M distributed ray sources 101~10M and N detectors 301~30N enclose and form a closed or nearly closed polygon. For example, in FIG. 2 andFIG. 3B In the center, three distributed radiation sources 101-103 and three detectors 301-303 surround and form a hexagon; FIG. 3A In the middle, two distributed radiation sources 101-102 and two detectors 301-302 surround and form a quadrilateral; in FIG. 3B In the center, five distributed radiation sources (101-105) and five detectors (301-305) form a decagon; FIG. 3A In the diagram, M distributed radiation sources (101~10M) and N detectors (301~30N) surround and form an (M+N) polygon.

[0085] In some exemplary embodiments of the present invention, the CT imaging system 100 includes a plurality of imaging components.

[0086] It should be noted that, in this document, the term "imaging component" can refer to a component capable of imaging based on detected rays. It can include a ray source for emitting rays and a detector for detecting the rays emitted by the ray source, and it is capable of imaging based on the rays detected by the detector.

[0087] For example, an imaging assembly may include at least one distributed X-ray source and at least one detector, wherein the distributed X-ray source and the detector are arranged face-to-face in the radial direction r of the imaging channel 80. For example, in FIG. 3B and FIG. 2 In the imaging channel 80, the first distributed X-ray source 101 and the first detector 301 are arranged face-to-face in the radial direction r, forming an imaging assembly; the second distributed X-ray source 102 and the second detector 302 are arranged face-to-face in the radial direction r, forming an imaging assembly; the third distributed X-ray source 103 and the third detector 303 are arranged face-to-face in the radial direction r, forming an imaging assembly.

[0088] In some exemplary embodiments of the present invention, in the same imaging assembly, at least a portion of the multiple targets of the distributed X-ray source and the detector are located in the same plane perpendicular to the first direction z.

[0089] In some exemplary embodiments of the present invention, at least q target points of a distributed radiation source are arranged at intervals along a straight line. Exemplarily, in conjunction with reference to... FIG. 3A and FIG. 3BThe q target points of the first distributed X-ray source 101 are arranged at intervals along a first straight line L1. The extension direction of the first straight line L1 can be perpendicular to both the first direction z and the radial direction r. In the same imaging assembly including the first distributed X-ray source 101 and the first detector 301, at least a portion of the first straight line L1 and the first detector 101 (the portion directly opposite the first distributed X-ray source 101) are located in the same first plane P1 perpendicular to the first direction z.

[0090] In other words, in the embodiments of the present invention, the CT imaging system adopts a source-detector coplanar structure. Specifically, multiple distributed X-ray sources and multiple detectors are located in the same plane perpendicular to the first direction z. By simultaneously employing the design of distributed X-ray sources and source-detector coplanarity, more complete data can be obtained under different angles, thereby reducing signal loss, obtaining more detailed image images, and allowing for faster scanning.

[0091] It should be noted that, unless otherwise specified, in this document, expressions such as "source and detector are coplanar," "coplanar," or "located in the same plane" include not only that the two components (e.g., the X-ray source and the detector) are located in the same plane in a geometric sense, but also that the two components (e.g., the X-ray source and the detector) are located in the same plane in an engineering sense. For example, the plane in which the two components are located may have a certain thickness, which may be determined by the manufacturing dimensions of the components. For example, it may be determined by the dimension of the target point of the X-ray source along the first direction z. In the case that the detector includes multiple rows of detector units, it may be determined by the dimension of a single row of detectors along the first direction z.

[0092] In some exemplary embodiments of the present invention, the multiple target points of the M distributed X-ray sources included in the CT imaging system are all located in the same plane perpendicular to the first direction z. For example, referring to reference FIG. 3B and FIG. 5 The q target points of the first distributed ray source 101, the q target points of the second distributed ray source 102, and the q target points of the third distributed ray source 103 are all located in the same first plane P1 perpendicular to the first direction z.

[0093] In other words, in the embodiments of the present invention, the source and probe arrangement of the entire CT imaging system adopts a coplanar structure. By simultaneously employing a distributed X-ray source and an overall coplanar source and probe design, the CT imaging system can achieve a compact structure and miniaturization, while allowing for more complete data to be obtained at different angles. This reduces signal loss, yields more detailed image images, and allows for faster scanning.

[0094] For example, refer to FIG. 6The CT imaging system 100 may also include a collimator 104. For example, the collimator 104 may be located in front of the distributed X-ray source to limit the direction and range of the X-ray beam emitted from the distributed X-ray source, ensuring that the X-ray beam can be accurately projected onto the object to be imaged, thereby reducing interference from scattered X-rays and improving the clarity of the image.

[0095] In embodiments of the present invention, the controller 50 can adjust the scanning mode of each target point in the distributed X-ray source through several key parameters to achieve optimal image quality and imaging efficiency. For example, the controller 50 can control at least one of the following aspects of each target point according to actual imaging requirements: activation time of each target point, emission range, beam emission sequence, emission intensity, and beam emission combination method of each target point, etc.

[0096] In an embodiment of the present invention, M distributed X-ray sources can be arranged at intervals along the circumferential direction of the imaging channel and distributed at different angles of the imaging area to irradiate the object to be imaged from multiple directions and obtain perspective images from different angles; while N detectors can also be arranged at intervals along the circumferential direction of the imaging channel, respectively opposite to the M distributed X-ray sources, for receiving X-ray signals transmitted through the object to be imaged and converting them into electrical signals to obtain CT projection data.

[0097] For example, such as FIG. 5 As shown, three distributed X-ray sources are positioned at different angles within the imaging area, arranged in a polygonal pattern. This design allows for X-ray illumination of the object to be imaged from multiple directions, thus obtaining perspective images from different angles. Opposite to the distributed X-ray sources, three detectors are arranged around the imaging area to receive the X-ray signals transmitted through the object. The positional relationship between the detectors and the X-ray sources ensures that the system can obtain high-quality CT projection data.

[0098] like FIG. 8AAs shown in the figure, the dashed lines represent the furthest path of the imaging optical path from the distributed X-ray source, through the object to be imaged, to the detector on the opposite side. For example, for the first distributed X-ray source 101 located above, optical path LP1 represents the optical path of the X-ray emitted from the first target point located on the leftmost side and incident on the rightmost unit of the first detector 301, and optical path LP2 represents the optical path of the X-ray emitted from the qth target point located on the rightmost side and incident on the leftmost unit of the first detector 301. The two optical paths LP1 and LP2 intersect at point Q1 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP1 and LP2 and the detection surface of the first detector 301 is the first imaging region including the imaging component of the first distributed X-ray source 101 and the first detector 301. For the second distributed X-ray source 102 located on the left, optical path LP3 represents the optical path of the X-ray emitted from the first target point located at the top and incident on the bottom unit of the second detector 302, and optical path LP4 represents the optical path of the X-ray emitted from the qth target point located at the bottom and incident on the top unit of the second detector 302. The two optical paths LP3 and LP4 intersect at point Q2 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP3 and LP4 and the detection surface of the second detector 302 is the second imaging region including the imaging component of the second distributed X-ray source 102 and the second detector 302. For the third distributed X-ray source 103 located on the right, optical path LP5 represents the optical path of the X-ray emitted from the first target point located at the top and incident on the bottommost unit of the third detector 303, and optical path LP6 represents the optical path of the X-ray emitted from the qth target point located at the bottom and incident on the topmost unit of the third detector 303. The two optical paths LP5 and LP6 intersect at point Q3 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP5 and LP6 and the detection surface of the third detector 303 is the third imaging region including the imaging assembly of the third distributed X-ray source 103 and the third detector 303. The overlapping area of ​​the first imaging region, the second imaging region, and the third imaging region constitutes a polygonal region, for example, in FIG. 8B In the example, an approximately triangular region is formed, and the largest inscribed circle of this polygonal region constitutes the effective imaging region S.

[0099] The applicant's research revealed that while the closed-loop structure of a distributed X-ray source, where the target and detector are coplanar and distributed around the object to be imaged, offers design and operational convenience, the limited angle coverage due to source-detector spacing and length ratios can lead to finite-angle scanning issues. These issues must be considered during image reconstruction, and the area of ​​the object to be imaged is also limited. Furthermore, because the effective imaging area covered by the scanning path is limited, when certain parts of the object exceed the effective imaging area S, projection data for those parts may not be obtained, resulting in missing or distorted information in certain areas of the reconstructed image—a phenomenon known as data truncation. In practical applications, especially when detecting complex or high-density objects, data truncation affects the comprehensiveness and accuracy of detection and imaging.

[0100] The applicant also discovered through research that, as another scanning imaging scheme for distributed light sources, related technologies have proposed scanning systems in which the target point and detector of the X-ray source are distributed on different planes, that is, the target point and detector are distributed in two or more planes. This scanning method causes the X-rays to obliquely scan the object, resulting in data truncation problems.

[0101] Based on this, embodiments of the present invention also propose a CT imaging system, in which two types of detectors are provided: one type is the detector described above, which is positioned face-to-face with each of the distributed X-ray sources; the other type is positioned on the same side as the distributed X-ray sources. For ease of description, these two types of detectors are referred to as the first sub-detector and the second sub-detector, respectively.

[0102] In other words, in some embodiments of the present invention, by placing multiple target points of the distributed X-ray source and the first sub-detector in the same plane perpendicular to the imaging channel and arranging the second sub-detector on the same side of the X-ray source, the effective imaging area can be expanded, the imaging quality of object edges and corners can be improved, thereby achieving more complete and effective X-ray projection and reception, and improving imaging efficiency.

[0103] For example, some embodiments of the present invention provide a CT imaging system, including: an imaging channel, at least a portion of which extends along a first direction, the imaging channel being used to place an object to be imaged during imaging; M distributed X-ray sources, the M distributed X-ray sources being spaced apart along the circumferential direction of the imaging channel, at least one distributed X-ray source including q target points, the q target points being configured to be activated in a predetermined order to emit X-rays, where M and q are both positive integers greater than or equal to 2; and N detectors, the N detectors being spaced apart along the circumferential direction of the imaging channel, the N detectors being used to detect X-rays emitted from the M distributed X-ray sources and passing through the object to be imaged. N is a positive integer greater than M, wherein the detector includes a first sub-detector and a second sub-detector, the CT imaging system includes multiple imaging components, each imaging component includes at least one distributed X-ray source and at least one first sub-detector, in the same imaging component, the distributed X-ray source and the first sub-detector are arranged face-to-face in the radial direction of the imaging channel, and in the same imaging component, multiple target points of the distributed X-ray source and at least a portion of the first sub-detector are located in the same plane perpendicular to a first direction, the radial direction being perpendicular to the first direction; and in the first direction, at least one second sub-detector is disposed on at least one side of at least one distributed X-ray source.

[0104] In this embodiment, by arranging a second sub-detector on the same side of the X-ray source, the X-rays can be simultaneously received by multiple sub-detectors, including the first and second sub-detectors, after passing through the object to be imaged. This enhances coverage of different angles, reduces data truncation or loss, and improves detection accuracy.

[0105] FIG. 8C A three-dimensional schematic diagram of a CT imaging system according to some exemplary embodiments of the present invention is shown, wherein the detectors include two types of detectors. FIG. 5 Based on some exemplary embodiments of the present invention FIG. 6 A schematic diagram of the imaging optical path of a CT imaging system. FIG. 8A to FIG. 8C This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein two X-ray sources and two detectors are schematically shown. FIG. 5 This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein five X-ray sources and five detectors are schematically shown. FIG. 6 This is a schematic plan view illustrating the arrangement of X-ray sources and detectors in a CT system according to some exemplary embodiments of the present invention, wherein multiple X-ray sources and multiple detectors are schematically shown.

[0106] It should be noted that, unless otherwise specified, the content and features described above can be incorporated into the various embodiments described below. To save space, these descriptions will not be repeated in the embodiments below. For example, in the embodiments described below, a three-segment scanning structure CT imaging system is used as an example to describe the embodiments of the present invention in detail. It should be understood that the following three-segment scanning structure CT imaging system is merely an exemplary structure of a CT imaging system for ease of explanation. Those skilled in the art should understand that the number and position of the X-ray sources and detectors can be adjusted according to specific needs to accommodate objects of different sizes and shapes to be imaged. For example, the scenarios of 3 distributed X-ray sources, 2 distributed X-ray sources, 5 distributed X-ray sources, and M distributed X-ray sources described above can be incorporated into the various embodiments described below.

[0107] Combined with reference FIG. 8A to FIG. 8C , FIG. 5 and FIG. 6 In some exemplary embodiments, the X-ray source of the CT imaging system 200 may include multiple distributed X-ray sources, for example, M distributed X-ray sources, where M is a positive integer greater than or equal to 2. For ease of description herein, the M distributed X-ray sources are respectively numbered as the first distributed X-ray source 210, the second distributed X-ray source 220, the third distributed X-ray source 230, ..., the Mth distributed X-ray source 2M0.

[0108] In some exemplary embodiments, the detection and acquisition device 30 of the CT imaging system 200 may include multiple detectors, for example, N detectors 202, where N is a positive integer greater than or equal to 2. For example, N may be a positive integer greater than or equal to M. In this embodiment, two types of detectors can be provided; that is, detector 202 may include a first sub-detector 2021 and a second sub-detector 2022. For example, the CT imaging system 200 may include N1 first sub-detectors 2021 and N2 second sub-detectors 2022. N equals the sum of N1 and N2, where N1 and N2 are both positive integers greater than or equal to 2.

[0109] For example, N1 can be equal to M, that is, the number of first sub-detectors is equal to the number of distributed radiation sources.

[0110] For ease of description, the N1 first sub-detectors are numbered as First First Sub-Detector 20211, Second First Sub-Detector 20212, Third First Sub-Detector 20213, ... N1 First Sub-Detector 2021N1; and the N2 second sub-detectors are numbered as First Second Sub-Detector 20221, Second Second Sub-Detector 20222, Third Second Sub-Detector 20223, ... N2 Second Sub-Detector 2022N2.

[0111] In other words, in this embodiment, the CT imaging system 200 may include: an imaging channel 80, at least a portion of which extends along a first direction z, for placing the object 70 to be imaged during imaging; M distributed X-ray sources, arranged at intervals along the circumferential direction c of the imaging channel 80, at least one of which includes q target points 2011 configured to be activated in a predetermined order to emit X-rays, where M and q are both positive integers greater than or equal to 2; and N detectors 202, arranged at intervals along the circumferential direction c of the imaging channel 80, for detecting X-rays emitted from the M distributed X-ray sources and passing through the object 70 to be imaged, where N is a positive integer greater than M. The detectors 202 include a first sub-detector 2021 and a second sub-detector 2022. The CT imaging system 200 includes multiple imaging components, each including at least one distributed X-ray source and at least one first sub-detector 2021. In the same imaging component, the distributed X-ray source and the first sub-detector 2021 are arranged face-to-face in the radial direction r of the imaging channel 80. In the same imaging component, at least a portion of the multiple target points 2011 of the distributed X-ray source and the first sub-detector 2021 are located in the same plane perpendicular to a first direction z, where the radial direction r is perpendicular to the first direction z. In the first direction z, at least one second sub-detector 2022 is disposed on at least one side of the at least one distributed X-ray source.

[0112] In this embodiment, the distributed X-ray source and the first sub-detector 2021 are not only spaced apart in the circumferential direction c, but at least a portion of the first sub-detector and the X-ray source target point are in a plane perpendicular to the imaging channel. Furthermore, by introducing a second sub-detector 2022 to work in conjunction with the first detector 2021, X-rays from the distributed X-ray source can be received from different angles or positions, thereby expanding the detection range. This three-dimensional spatial arrangement breaks through the traditional design of circumferential arrangement, enabling the imaging system to detect simultaneously from multiple angles, improving detection accuracy and breadth, and effectively solving the problems of limited-angle scanning and data truncation.

[0113] Reference FIG. 8A to FIG. 8C , FIG. 6 and FIG. 8A to FIG. 8C M distributed X-ray sources 210~2M0 are arranged along the circumferential direction c of the imaging channel 80. For example, the M distributed X-ray sources 210~2M0 are arranged at intervals along the circumferential direction c of the imaging channel 80.

[0114] Continue to refer to FIG. 6 , FIG. 8A to FIG. 8C and FIG. 6N1 first sub-detectors are arranged along the circumferential direction c of the imaging channel 80. For example, the N1 first sub-detectors are arranged at intervals along the circumferential direction c of the imaging channel 80.

[0115] In some exemplary embodiments, M distributed X-ray sources 210~2M0 and N1 first sub-detectors are arranged alternately along the circumferential direction c of the imaging channel 80. For example, the M distributed X-ray sources 210~2M0 are arranged at equal intervals along the circumferential direction c of the imaging channel 80, with one first sub-detector positioned between two adjacent distributed X-ray sources. The N1 first sub-detectors are arranged at equal intervals along the circumferential direction c of the imaging channel 80, with one distributed X-ray source positioned between two adjacent first sub-detectors.

[0116] It should be understood that FIG. 8A and FIG. 8B The diagrams show the planes perpendicular to the first direction z, i.e. FIG. 8C and FIG. 5 The plane of the paper is perpendicular to the first direction z. For example... FIG. 8D and FIG. 8E As shown, in a plane perpendicular to the first direction z, M distributed ray sources 210~2M0 and N1 first sub-detectors enclose and form a closed or nearly closed polygon. For example, in FIG. 5 In the center, three distributed radiation sources 210-230 and three first sub-detectors 20211-20213 form a hexagonal shape; FIG. 8D In the middle, two distributed radiation sources 210-220 and two first sub-detectors 20211-20212 surround and form a quadrilateral; in FIG. 8E In the center, five distributed radiation sources 210-230 and five first sub-detectors 20211-20215 form a decagon; FIG. 5 In the middle, M distributed radiation sources 210~2M0 and N1 first sub-detectors 20211~2021N1 surround and form a (M+N1) polygon.

[0117] The arrangement of the X-ray source and detectors determines the spatial resolution and field of view of CT imaging. This closed or near-closed polygonal geometry optimizes the viewing angle of the imaging system, allowing each detector to receive signals from different angles, effectively increasing the amount of projection data to cover the imaging area to the greatest extent.

[0118] Reference FIG. 6 The distributed radiation source may include a first side 211 and a second side 212 disposed opposite to each other in the first direction z, for example, the first side 211 is downstream of the second side 212.

[0119] In an embodiment of the present invention, for at least one distributed radiation source, one or more second sub-detectors may be provided on at least one side of the first side 211 and the second side 212 of the distributed radiation source in the first direction z.

[0120] FIG. 5 A schematic diagram of the arrangement of a distributed radiation source and a second sub-detector according to some embodiments of the present invention is shown. FIG. 6 A schematic diagram of the arrangement of a distributed radiation source and a second sub-detector according to other embodiments of the present invention is shown.

[0121] Reference FIG. 5 In the first direction z, a second sub-detector 2022 is respectively set on the first side 211 and the second side 212 of the distributed radiation source.

[0122] Reference FIG. 6 In the first direction z, a second sub-detector 2022 is provided on only the first side 211 of the distributed radiation source.

[0123] Reference FIG. 5 In the first direction z, a second sub-detector 2022 is provided on only the second side 212 of the distributed radiation source.

[0124] In an embodiment of the present invention, in the first direction z, each of the M' distributed radiation sources has at least one second sub-detector 2022 disposed on its first side 211; or, in the first direction z, each of the M' distributed radiation sources has at least one second sub-detector 2022 disposed on its second side 212; or, in the first direction z, each of the M' distributed radiation sources has at least one second sub-detector 2022 disposed on its first side 211 and its second side 212, wherein M' is greater than or equal to 1 and less than or equal to M.

[0125] In this embodiment, a second sub-detector 2022 is provided, and its position is flexibly arranged to better coordinate with the first detector 2021. It can receive rays from the distributed radiation source from different angles or positions, thereby expanding the detection range. This three-dimensional spatial arrangement breaks through the traditional design of circumferential arrangement, enabling the imaging system to detect simultaneously from multiple angles, improving detection accuracy and breadth, and effectively solving the problems of limited-angle scanning and data truncation.

[0126] For example, N2 = 2M, meaning the number of second sub-detectors N2 can be equal to twice the number of distributed radiation sources. In other words, a second sub-detector is placed on both sides of each distributed radiation source. This arrangement expands the detection range for each distributed radiation source, improving detection accuracy and breadth, and thus more effectively addressing the problems of finite angle scanning and data truncation.

[0127] In some exemplary embodiments of the present invention, the CT imaging system 200 includes a plurality of imaging components.

[0128] For example, in this embodiment, an imaging assembly may include at least one distributed X-ray source, at least one first sub-detector, and at least a portion of at least one second sub-detector. In the same imaging assembly, the distributed X-ray source and the first sub-detector are arranged face-to-face in the radial direction r of the imaging channel 80, and at least a portion of the distributed X-ray source and the second sub-detector are also arranged face-to-face in the radial direction r of the imaging channel 80. For example, in FIG. 6 and FIG. 6 In the imaging channel 80, the first distributed X-ray source 210 and the first first sub-detector 20211 are arranged face-to-face in the radial direction r. The first distributed X-ray source 210 and a portion of the third and fourth second sub-detectors are arranged face-to-face in the radial direction r. The first distributed X-ray source 210 and a portion of the fifth and sixth second sub-detectors are arranged face-to-face in the radial direction r. These face-to-face arranged components constitute an imaging assembly. Similarly, the second distributed X-ray source 220 and the detector portion arranged face-to-face with it constitute an imaging assembly, and the third distributed X-ray source 230 and the detector portion arranged face-to-face with it constitute an imaging assembly.

[0129] In some exemplary embodiments of the present invention, in the same imaging assembly, multiple target points of the distributed X-ray source and at least a portion of the first sub-detector are located in the same plane perpendicular to the first direction z.

[0130] In some exemplary embodiments of the present invention, at least q target points of a distributed radiation source are arranged at intervals along a straight line. Exemplarily, in conjunction with reference to... FIG. 7 and FIG. 7The q target points of the first distributed X-ray source 210 are arranged at intervals along a first straight line L1. The extension direction of the first straight line L1 can be perpendicular to both the first direction z and the radial direction r. In the same imaging assembly including the first distributed X-ray source 210 and the first first sub-detector 20211, at least a portion of the first straight line L1 and the first first sub-detector 20211 (the portion directly opposite the first distributed X-ray source 210) are located in the same first plane P1 perpendicular to the first direction z.

[0131] In other words, in the embodiments of the present invention, the CT imaging system adopts a source-detector coplanar structure. Specifically, a portion of multiple distributed X-ray sources and multiple first sub-detectors are located in the same plane perpendicular to the first direction z. By simultaneously employing the design of distributed X-ray sources and source-detector coplanarity, more complete data can be obtained under different angles, thereby reducing signal loss, obtaining finer image details, and allowing for faster scanning.

[0132] In some exemplary embodiments of the present invention, the multiple target points of the M distributed X-ray sources included in the CT imaging system are all located in the same plane perpendicular to the first direction z. For example, referring to reference FIG. 6 and FIG. 7 The q target points of the first distributed ray source 210, the q target points of the second distributed ray source 220, and the q target points of the third distributed ray source 230 are all located in the same first plane P1 perpendicular to the first direction z.

[0133] In other words, in the embodiments of the present invention, the source and probe arrangement of the entire CT imaging system adopts a coplanar structure. By simultaneously employing a distributed X-ray source and an overall coplanar source and probe design, the CT imaging system can achieve a compact structure and miniaturization, while allowing for more complete data to be obtained at different angles. This reduces signal loss, yields more detailed image images, and allows for faster scanning.

[0134] In embodiments of the present invention, the controller 50 can adjust the scanning mode of each target point in the distributed X-ray source through several key parameters to achieve optimal image quality and imaging efficiency. For example, the controller 50 can control at least one of the following aspects of each target point according to actual imaging requirements: activation time of each target point, emission range, beam emission sequence, emission intensity, and beam emission combination method of each target point, etc.

[0135] In an embodiment of the present invention, M distributed X-ray sources can be arranged at intervals along the circumferential direction of the imaging channel and distributed at different angles in the imaging area to irradiate the object to be imaged from multiple directions and obtain perspective images from different angles; while N1 first sub-detectors can also be arranged at intervals along the circumferential direction of the imaging channel and are respectively opposite to the M distributed X-ray sources.

[0136] For example, such as FIG. 6 As shown, three distributed X-ray sources are positioned at different angles within the imaging area, arranged in a polygonal pattern. This design allows for X-ray illumination of the object to be imaged from multiple directions, thereby obtaining perspective images from different angles. Opposite to the distributed X-ray sources, three primary detectors are arranged around the imaging area to receive the X-ray signals transmitted through the object. The positional relationship between the detectors and the X-ray sources ensures that the system can obtain high-quality CT projection data.

[0137] like FIG. 5 As shown in the figure, the dashed lines represent the furthest path of the imaging optical path from the distributed X-ray source, through the object to be imaged, to the detector opposite. For example, for the first distributed X-ray source 210 located at the top, optical path LP10 represents the optical path of the X-ray emitted from the first target point located on the far left and incident on the detection unit of a second sub-detector opposite. It should be noted that because a second sub-detector is located opposite the first distributed X-ray source 210, optical path LP10 can illuminate the object to be imaged at a relatively large angle.

[0138] For example, optical path LP20 represents the optical path of a ray emitted from the q-th target point located on the far right and incident on the detection unit of another second sub-detector opposite it. It should still be noted that, since another second sub-detector is arranged opposite the first distributed ray source 210, optical path LP20 can illuminate the object to be imaged at a large angle.

[0139] The two optical paths LP10 and LP20 intersect at point Q10 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP10 and LP20 and the detector surface is the first imaging area.

[0140] For the second distributed X-ray source 220 located on one side, optical path LP30 represents the optical path of the X-ray emitted from the first target point located at the top and incident on the detection unit of a second sub-detector opposite it. Optical path LP40 represents the optical path of the X-ray emitted from the q-th target point located at the bottom and incident on the detection unit of another second sub-detector opposite it. The two optical paths LP30 and LP40 intersect at point Q20 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP30 and LP40 and the detection surface of the detector is the second imaging region.

[0141] For the third distributed X-ray source 230 located on the other side, optical path LP50 represents the optical path of the X-ray emitted from the first target point located at the top and incident on the detection unit of a second sub-detector opposite. Optical path LP60 represents the optical path of the X-ray emitted from the q-th target point located at the bottom and incident on the detection unit of another second sub-detector opposite. The two optical paths LP50 and LP60 intersect at point Q30 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP50 and LP60 and the detection surface of the detector is the third imaging region.

[0142] The overlapping area of ​​the first imaging region, the second imaging region, and the third imaging region constitutes a polygonal region, for example, in FIG. 7 In the example, a triangular region is formed, and the largest inscribed circle of this polygonal region constitutes the effective imaging region S10.

[0143] FIG. 7 This is a schematic diagram of the imaging optical path of a CT imaging system according to some other exemplary embodiments of the present invention. It should be noted that... FIG. 7 The imaging optical path diagram shown can be considered as follows: FIG. 7 The comparative example shown is the imaging optical path diagram, namely, FIG. 7 The CT imaging system targeted and FIG. 7 The targeted CT imaging system (i.e. FIG. 7 The only difference between the CT imaging systems shown is: FIG. 6 The CT imaging system in question does not have the aforementioned second sub-detector.

[0144] like FIG. 9A As shown in the figure, the dashed lines represent the longest imaging optical path from the distributed X-ray source, through the object being imaged, to the detector on the opposite side. It should be noted that... FIG. 9B To simplify the accompanying diagrams, the optical paths of the distributed X-ray sources have been simplified. This is because the optical paths of some distributed X-ray sources overlap. FIG. 9C The dashed lines in the diagram represent each optical path that can indicate some overlapping ray paths.

[0145] For example, such as FIG. 9A-FIG. 9CAs shown, for the first distributed X-ray source 101 located at the top, optical path LP01 represents the optical path of the X-ray emitted from the first target point located on the far left and incident on the rightmost unit of the first detector 301, and optical path LP02 represents the optical path of the X-ray emitted from the qth target point located on the far right and incident on the leftmost unit of the first detector 301. The two optical paths LP01 and LP02 intersect at point Q01 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP01 and LP02 and the detection surface of the first detector 301 is the first imaging area of ​​the imaging component including the first distributed X-ray source 101 and the first detector 301. For the second distributed X-ray source 102 located on one side, optical path LP03 represents the optical path of the X-ray emitted from the first target point located at the top and incident on the bottom unit of the second detector 302, and optical path LP04 represents the optical path of the X-ray emitted from the qth target point located at the bottom and incident on the top unit of the second detector 302. The two optical paths LP03 and LP04 intersect at point Q02 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP03 and LP04 and the detection surface of the second detector 302 is the second imaging region including the imaging component of the second distributed X-ray source 102 and the second detector 302. For the third distributed X-ray source 103 located on the other side, optical path LP05 represents the optical path of the X-ray emitted from the first target point located at the top and incident on the bottommost unit of the third detector 303, and optical path LP06 represents the optical path of the X-ray emitted from the qth target point located at the bottom and incident on the topmost unit of the third detector 303. The two optical paths LP05 and LP06 intersect at point Q03 in the plane P1 where the source and detector are located. The area enclosed by the two optical paths LP05 and LP06 and the detection surface of the third detector 303 is the third imaging region including the imaging assembly of the third distributed X-ray source 103 and the third detector 303. The overlapping area of ​​the first imaging region, the second imaging region, and the third imaging region constitutes a polygonal region, for example, in FIG. 5 In the example, a triangular region is formed, and the largest inscribed circle of this polygonal region constitutes the effective imaging region S1.

[0146] exist FIG. 5 In the process, because no second sub-detector is deployed, only region S1 of the object to be imaged can be completely covered by the detector; outside region S1, there is a data truncation problem (only a portion of the rays can be covered); while... FIG. 10AIn the system shown, a second sub-detector is provided on at least one side of the distributed radiation source. Therefore, the range of radiation angles that can be received by the detector for each radiation source is expanded. In other words, by setting the second sub-detector, the effective imaging area can be expanded from S1 to S10 without changing the position and size of other components, thereby effectively reducing or even avoiding data truncation problems.

[0147] It should be noted that for a system with source probes arranged circumferentially, the rays converge in the central region, forming a polygonal effective imaging area, which is the main imaging area. For ease of explanation and comparison, the tangent circle of this polygon is taken as the effective imaging area.

[0148] In embodiments of the present invention, the detector can be a single-row detector, a multi-row detector, or a surface detector. A suitable detector type can be selected for different application scenarios to optimize imaging efficiency and performance. Specifically, a single-row detector includes multiple detection units arranged along a straight line; a multi-row detector includes multiple rows of detector units, each row containing multiple detector units, forming a matrix or grid structure; and a surface detector covers a large planar area with densely arranged detection units forming a continuous detection surface.

[0149] In embodiments of the present invention, a flexible detector layout design is also provided, applicable to the first sub-detector 2021 and the second sub-detector 2022. That is, different arrangements can be designed to meet different imaging requirements.

[0150] FIG. 10B A schematic diagram of a densely arranged detector layout design according to some embodiments of the present invention is shown; FIG. 10A A schematic diagram of a sparsely arranged detector layout design according to other embodiments of the present invention is shown; FIG. 10B A schematic diagram of a layout design for a hybrid arrangement of detectors according to yet another embodiment of the present invention is shown.

[0151] Combined with reference FIG. 10A For example, the first sub-detector 2021 may include multiple rows of detector units DU, which are densely arranged along the first direction z; or, the first sub-detector 2021 may include multiple rows of detector units DU, which are sparsely arranged along the first direction z; or, the first sub-detector 2021 may include multiple rows of detector units DU, in the middle region of the first sub-detector 2021, a portion of the multiple rows of detector units DU are densely arranged along the first direction z, and in the two side regions of the first sub-detector 2021, another portion of the multiple rows of detector units DU are sparsely arranged along the first direction z.

[0152] Similarly, the second sub-detector 2022 may include multiple rows of detector units DU, which are densely arranged along the first direction z; or, the second sub-detector 2022 may include multiple rows of detector units DU, which are sparsely arranged along the first direction z; or, the second sub-detector 2022 may include multiple rows of detector units DU, in the middle region of the second sub-detector 2022, a portion of the multiple rows of detector units DU are densely arranged along the first direction z, and in the two side regions of the second sub-detector 2022, another portion of the multiple rows of detector units DU are sparsely arranged along the first direction z.

[0153] According to embodiments of the present invention, in a densely arranged configuration, the detector can acquire more X-ray information, thereby enhancing image detail, which is particularly useful in imaging small areas or where high-precision observation is required. This layout is suitable for high-resolution imaging, such as the detection of fine structures or medical applications requiring precise measurements; a sparse arrangement can reduce cost and complexity, or provide sufficient image quality when high-resolution imaging is not required, making it suitable for large-area imaging or applications with high imaging speed requirements; for applications that require consideration of cost, imaging range, and detailed imaging of the central region, such as certain types of medical diagnostics or industrial inspections, the advantages of the first two configurations can be combined, using a dense arrangement in the middle region of the detector to ensure high resolution in the central imaging region, while a sparse arrangement on both sides can expand the imaging range while controlling cost and the complexity of data processing.

[0154] In embodiments of the present invention, the aforementioned multi-row detector unit may further include an intermediate row detector unit, which is located at the middle position of the multi-row detector unit in the first direction z. In the same imaging assembly, the multiple target points of the distributed X-ray source and the intermediate row detector unit of the first sub-detector are located in the same plane perpendicular to the first direction. That is, the multiple target points of the distributed X-ray source and the intermediate row detector unit of the first sub-detector can be located in the same plane, thereby ensuring precise alignment between the X-ray source and the detector, and improving imaging quality and consistency.

[0155] According to embodiments of the present invention, the CT imaging system may further include multiple source detector components, each including a distributed X-ray source and at least one second sub-detector 2022. These multiple source detector components can be flexibly combined and arranged to meet different imaging requirements. For example, the CT imaging system can adapt to imaging requirements of different sizes, shapes, or resolutions by increasing or decreasing the number of source detector components.

[0156] For example, an odd number of source probe components can be set, such as... FIG. 10AThe three shown could also be five, etc. Using an odd number of source probes can create a balance between symmetry and geometric center. This symmetry helps optimize ray distribution, allowing the imaging system to achieve more uniform coverage at different angles. At the same time, an odd number of sources can distribute rays evenly, providing more consistent exposure in different directions of the object to be imaged, thereby reducing imaging errors caused by angular deviations.

[0157] In embodiments of the present invention, the orthogonal projections of the distributed X-ray source and at least one second sub-detector 2022 of the same source-detector assembly along the first direction z can at least partially overlap. That is, in the CT imaging system according to embodiments of the present invention, the arrangement of the distributed X-ray source and the second sub-detector relative to the object to be imaged should ensure that they have good geometric alignment during imaging to achieve good detection results.

[0158] Furthermore, within the same source probe component, such as FIG. 10B As shown, the dimension d11 of the distributed X-ray source along the extension direction of the first straight line L1 and the dimension d12 of the second sub-detector 2022 along the extension direction of the first straight line L1 can be substantially equal (each distributed X-ray source has the same size). This design ensures that the X-rays emitted by the X-ray source can be effectively captured by the detector along the entire length of the imaging channel.

[0159] FIG. 10B A schematic diagram of the ray angle coverage range in a CT imaging system according to some embodiments of the present invention is shown; FIG. 10A A schematic diagram of the ray angle coverage range in a CT imaging system according to other embodiments of the present invention is shown. It should be noted that, in FIG. 10B and FIG. 10A The CT imaging systems shown in the diagram do not have a second sub-detector.

[0160] Taking the arrangement of three distributed radiation sources as an example, such as... FIG. 10B As shown in the figure, the ray angle coverage range is represented by the line connecting the center point of the polygon and the edge of the distributed ray source. Among them, FIG. 11A Each displayed X-ray source covers an angle of 30°, providing a total scanning coverage of 90°; for example FIG. 11B As shown, FIG. 11A Each X-ray source covers an angle of 54°, providing a total scanning coverage of 162°.

[0161] Combined with reference FIG. 11B and FIG. 11AWith factors such as the relative positions of the sources and the distance between them remaining constant, the radiation coverage angle range of each distributed radiation source can be altered by changing the size of the radiation source or the size ratio of the radiation source to the detector, thereby changing the scanning coverage range of the CT imaging system. For example, while keeping factors such as the relative positions of the sources and the distance between them constant, increasing the size of the distributed radiation sources (e.g., from a single distributed radiation source...) FIG. 11B The dimensions shown are increased to FIG. 11A By increasing the size of the distributed radiation source (as shown), or by increasing the ratio of the size of the distributed radiation source to the size of the detector, the radiation coverage angle range of a single distributed radiation source can be increased, for example, from 30° to 54°. Accordingly, the scanning coverage range of the CT imaging system increases from 90° to 162°.

[0162] FIG. 11B A schematic diagram of the effective imaging area in a CT imaging system according to some embodiments of the present invention is shown; FIG. 10A to FIG. 11B A schematic diagram of the effective imaging area in a CT imaging system according to other embodiments of the present invention is shown. It should be noted that, in FIG. 5 and FIG. 6 The CT imaging systems shown in the diagram do not have a second sub-detector.

[0163] Combined with reference FIG. 8A to FIG. 8E and FIG. 6 With factors such as the relative positions of the sources and the distance between them remaining constant, the imaging area of ​​each distributed X-ray source can be altered by changing the size of the X-ray source or the size ratio of the X-ray source to the detector, thereby changing the effective imaging area of ​​the CT imaging system. For example, while keeping factors such as the relative positions of the sources and the distance between them constant, the size of the distributed X-ray sources can be reduced (e.g., from a single distributed X-ray source...). FIG. 8A to FIG. 8C The dimensions shown are reduced to FIG. 12 By increasing the size of the distributed X-ray source (as shown), or by reducing the ratio of the size of the distributed X-ray source to the size of the detector, the imaging area of ​​a single distributed X-ray source can be increased, and correspondingly, the effective imaging area of ​​the CT imaging system increases from Sa to Sb.

[0164] In other words, in conjunction with reference FIG. 1 With factors such as the relative positions of the sources and detectors and the distance between them remaining constant, reducing the size of the distributed X-ray source or the ratio of the size of the distributed X-ray source to the size of the detector can increase the effective imaging area of ​​the CT imaging system, but it will reduce the scanning coverage of the CT imaging system; conversely, increasing the size of the distributed X-ray source or the ratio of the size of the distributed X-ray source to the size of the detector can increase the scanning coverage of the CT imaging system, but it will reduce the effective imaging area of ​​the CT imaging system.

[0165] In an embodiment of the present invention, by arranging a second sub-detector located on the side of the radiation source, the effective imaging area and the scanning coverage area can be increased simultaneously, that is, the effective imaging area and the scanning coverage area can be taken into account, thereby effectively improving the imaging quality.

[0166] Return to reference FIG. 12 , FIG. 13A and FIG. 13A In an embodiment of the present invention, by arranging a second sub-detector located on the side of the radiation source, the radiation angle coverage range of the M distributed radiation sources can reach 90°-120°; or the radiation angle coverage range of the M distributed radiation sources can reach 120°-150°; or the radiation angle coverage range of the M distributed radiation sources can reach 140°-160°.

[0167] In an embodiment of the present invention, within the same imaging assembly, the distributed X-ray source has a first dimension a1 extending along the first straight line L1, and the first sub-detector 2021 has a second dimension a2 extending parallel to the first straight line L1, wherein the first dimension a1 is smaller than the second dimension a2. That is, the effective coverage area of ​​the detector is greater than the length of the target line array, thereby helping to ensure that the X-ray beam emitted from each target point can be completely received by the detector, increasing the effective imaging area.

[0168] By employing different processing methods for moving and stationary objects, embodiments of the present invention also provide a way to optimize detector size to ensure the acquisition of complete image data under various imaging conditions. For moving objects, the detector needs to consider the object's movement distance and ray magnification ratio to ensure coverage of all possible ranges of motion; for stationary objects, the detector needs to ensure coverage of the region of interest.

[0169] Specifically, for a moving object, the minimum size required for the detector can be calculated based on the object's velocity and the ray geometry. The dimensions of the first sub-detector 2021 in the first direction z satisfy the following relationship:

[0170] LD = d * p (1)

[0171] Where LD is the dimension of the first sub-detector in the first direction, d is the distance the object to be imaged moves in the first direction within one exposure cycle, and p is the X-ray magnification ratio. The X-ray magnification ratio is defined as the ratio between the image size on the detector and the actual size of the object, describing the degree to which the image is magnified during the imaging process due to the different distances between the object and the detector.

[0172] For stationary objects, the size of the first sub-detector 2021 in the first direction z can be greater than or equal to the size of the region of interest of the object to be imaged in the first direction z, so as to ensure that the detector can completely cover the region to be imaged, thereby obtaining complete projection data and avoiding loss of image information.

[0173] In embodiments of the present invention, such as FIG. 13A and FIG. 13A As shown, in a plane perpendicular to the first direction z, M distributed X-ray sources 210~2M0 and N1 first sub-detectors enclose and form a closed or nearly closed polygon. The effective imaging region S1 of the CT imaging system 200 can be located in the middle region of the aforementioned polygon. It should be noted that the term "middle region" here refers to the region where the geometric center of the polygon is located and / or the region formed by radially extending the region where the geometric center is located outward by a predetermined distance. With this arrangement, the center of the imaging region coincides with or substantially coincides with the geometric center of the polygon, which allows the X-rays to uniformly cover the region of interest of the object to be imaged, thereby avoiding the loss of edge data.

[0174] In an embodiment of the invention, the conveying mechanism 40 is located in the middle region of the aforementioned polygon. This layout supports the coordinated operation of the effective imaging area of ​​the CT imaging system and the conveying mechanism. The conveying mechanism can move the object to be imaged to the middle region of the polygon, ensuring that the object remains in the ideal imaging position throughout the imaging process, further improving the accuracy and consistency of the imaging. Furthermore, the conveying mechanism can be controlled to ensure that the object moves stably and smoothly during the imaging process, reducing or even avoiding problems such as image blurring or distortion caused by positional deviation or irregular movement.

[0175] FIG. 13A This is a three-dimensional schematic diagram of a CT imaging system according to some exemplary embodiments of the present invention, wherein the target points of the distributed X-ray sources are tilted.

[0176] like FIG. 13B and FIG. 13A As shown, the CT imaging system 300 may include: an imaging channel, at least a portion of which extends along a first direction z, for placing an object to be imaged during imaging; M distributed X-ray sources 310, which are spaced apart along the circumferential direction of the imaging channel, at least one of which includes q target points 3011, which are configured to be activated in a predetermined order to emit X-rays, where M and q are both positive integers greater than or equal to 2; and N detectors 402, which are spaced apart along the circumferential direction of the imaging channel, for detecting X-rays emitted from the M distributed X-ray sources 310 and passing through the object to be imaged, where N is a positive integer greater than or equal to M.

[0177] FIG. 13B This is a schematic diagram of a distributed X-ray source for a CT imaging system according to some exemplary embodiments of the present invention.

[0178] In some exemplary embodiments, detector 402 includes a first sub-detector 4021, or detector 402 includes only the first sub-detector 4021. That is, in this embodiment, as... FIG. 13A As shown, the aforementioned second sub-detector is not installed on the upper or lower side of the distributed radiation source 310.

[0179] In this embodiment, the CT imaging system 300 includes a plurality of imaging components, each including at least one distributed X-ray source 310 and at least one first sub-detector 4021. In the same imaging component, the distributed X-ray source 310 and the first sub-detector 4021 are arranged face-to-face in the radial direction r of the imaging channel. In the same imaging component, at least one target point 3011 of the distributed X-ray source and at least a portion of the first sub-detector 4021 are located in the same plane perpendicular to the first direction z, and the radial direction is perpendicular to the first direction z. At least one of the M distributed X-ray sources includes q target points that are arranged at an angle relative to the first direction z.

[0180] The applicant discovered through research that movement of an object during data acquisition can cause inconsistencies between consecutive image frames, potentially leading to motion artifacts. According to an embodiment of the present invention, when the object to be imaged moves relative to the CT imaging system (e.g., a transport mechanism moves the object), at least q target points from one of M distributed X-ray sources are arranged at an angle relative to a first direction z, i.e., the arrangement direction of the target points has a certain angle with the first direction z (see reference). FIG. 13A Using the angle θ in the image can reduce or even avoid motion artifacts, thereby improving image quality.

[0181] In an embodiment of the present invention, the CT imaging system 300 further includes a controller configured to control the beam interval time of a plurality of target points and control the movement speed of the object to be imaged.

[0182] like FIG. 13A As shown, the q target points 3011 of the distributed radiation source can be arranged at intervals along a first straight line L1. For example, the tilt angle θ of the first straight line L1 relative to the first direction z can satisfy the following relationship:

[0183] cosθ=v*t / s (2)

[0184] Where s is the distance between two adjacent target points along the extension direction of the first straight line L1 among the q target points, v is the moving speed of the object to be imaged, and t is the beam exit interval time of the distributed X-ray source.

[0185] like FIG. 13B As shown, within the beam emission interval t, the object to be imaged 70 moves a distance v*t along the first direction z. The i-th target point and the (i+1)-th target point are two adjacent target points, and the distance between them along the extension direction of the first straight line L1 is s. During the movement of the object to be imaged 70 along the first direction z, the i-th target point and the (i+1)-th target point emit beams sequentially according to the beam emission interval t. By setting s*cosθ=v*t, the rays emitted by the i-th target point and the (i+1)-th target point scan the same cross section of the object to be imaged 70 perpendicular to the first direction z. That is, when imaging the moving object to be imaged 70, by designing the tilt angle of the target points, the distance between the target points, the beam emission interval, and the moving speed, multiple target points and the object to be imaged are relatively stationary along the direction of movement, so as to obtain a higher spatial resolution of the current scanning area.

[0186] FIG. 13A This is a schematic diagram of a distributed X-ray source for a CT imaging system according to some other exemplary embodiments of the present invention.

[0187] According to embodiments of the present invention, the target point can be tilted relative to the first direction z through different design methods, thereby obtaining an tilted target point.

[0188] Reference FIG. 13A and FIG. 13C to FIG. 13E The distributed radiation source 301 includes a radiation source body 3012 and q target points 3011 installed on the radiation source body.

[0189] like FIG. 13C As shown, the X-ray source body 3012 can be perpendicular to the first direction z, that is, the two surfaces of the X-ray source body 3012 along the first direction z ( FIG. 13D The upper and lower surfaces of the target points 3011 mounted on the radiation source body 3012 are perpendicular to the first direction z. The target points 3011 are positioned relative to the two surfaces of the radiation source body 3012 along the first direction z. FIG. 13E The upper and lower surfaces of the target points are arranged at an angle, such that the q target points 3011 are arranged at an angle relative to the first direction z. In this embodiment, the multiple target points can be flexibly arranged at an angle relative to the X-ray source body to improve the design freedom of the system.

[0190] like FIG. 13C As shown, q target points 3011 mounted on the radiation source body are relative to the two surfaces of the radiation source body 3012 along the first direction z. FIG. 13CThe upper and lower surfaces of the radiation source body 3012 are arranged in parallel. The radiation source body 3012 can be arranged at an angle relative to the first direction z, that is, the two surfaces of the radiation source body 3012 along the first direction z (the upper and lower surfaces of the radiation source body 3012) are arranged in parallel. FIG. 13D The upper and lower surfaces of the target (3011) are arranged at an angle relative to the first direction z. In this way, the q target points 3011 are arranged at an angle relative to the first direction z. In this embodiment, the entire radiation source body can be tilted directly, which is simpler and makes it easier to ensure the tilt consistency of all target points.

[0191] In an embodiment of the present invention, the q target points 3011 of the M distributed X-ray sources 310 can also be arranged at an angle relative to the first direction z. The angled arrangement of the q target points of each distributed X-ray source can better adapt to the geometry and motion state of the object to be imaged.

[0192] In embodiments of the present invention, the q target points 3011 of the M distributed X-ray sources 310 may also have equal tilt angles relative to the first direction z. Equal tilt angles of the q target points of each distributed X-ray source ensure that the X-ray sources provide consistent coverage throughout the entire imaging area.

[0193] In an embodiment of the present invention, each of the q target points 3011 of the M distributed X-ray sources 310 can have a z-axis position coordinate in the first direction z. The z-axis position coordinates of the i-th target point of the M distributed X-ray sources 301 can be equal to each other; the z-axis position coordinates of the i-th target point of the M distributed X-ray sources 310 can also be unequal to each other, 1 ≤ i ≤ q. That is, according to specific imaging requirements, the z-axis position of the target point can be adjusted to optimize the projection angle and distribution density of the X-rays.

[0194] Furthermore, the controller can be configured to simultaneously emit beams from multiple target points with equal z-axis position coordinates from M distributed X-ray sources 310. Equal z-axis coordinates mean that these target points are located on the same horizontal plane in the z-direction, or in other words, they are located at the same height in the CT scan area. Therefore, this design ensures that the X-rays emitted from these target points pass through the same imaging cross-section, thereby ensuring that multi-angle data of the same cross-section can be acquired simultaneously. This helps to improve the detail and accuracy of the cross-sectional image and also reduces blurring and distortion caused by object movement.

[0195] In an embodiment of the present invention, detector 402 may further include a second sub-detector 4022, wherein at least one second sub-detector 4022 is provided on at least one side of at least one distributed radiation source 310 in the first direction z.

[0196] FIG. 13D Schematic diagrams of the arrangement of distributed radiation sources and second sub-detectors according to some embodiments of the present invention are shown respectively, wherein, FIG. 13EThis shows that a second sub-detector is installed on both sides of the distributed radiation source. FIG. 13E The diagram shows a second sub-detector positioned above the distributed radiation source. FIG. 14A The diagram shows a second sub-detector positioned below the distributed radiation source.

[0197] Reference FIG. 14B In the first direction z, on the first and second sides of the distributed ray source ( FIG. 13C to FIG. 13E The upper and lower sides of the detector are respectively equipped with a second sub-detector 4022.

[0198] Reference FIG. 14A In the first direction z, on only the first side 211 of the distributed ray source ( FIG. 14B The second sub-detector 4022 is located on the upper side (in the middle).

[0199] Reference FIG. 15 In the first direction z, on only the second side 212 of the distributed ray source ( FIG. 15 The second sub-detector 4022 is located on the lower side (in the middle).

[0200] In an embodiment of the present invention, multiple target points of at least one distributed radiation source are inclined relative to a first direction z. Furthermore, in the first direction z, at least one second sub-detector 4022 is provided on the first side 211 of each of the M' distributed radiation sources; or, at least one second sub-detector 4022 is provided on the second side 212 of each of the M' distributed radiation sources in the first direction z; or, at least one second sub-detector 4022 is provided on the first side 211 and the second side 212 of each of the M' distributed radiation sources in the first direction z, wherein M' is greater than or equal to 1 and less than or equal to M.

[0201] In this embodiment, by tilting the multiple target points of the distributed X-ray source and incorporating a second sub-detector 4022, the position of the second sub-detector can be flexibly arranged to better coordinate with the first detector 4021. This allows the system to receive X-rays from the distributed X-ray source from different angles or positions, thereby expanding the detection range. This three-dimensional spatial arrangement breaks through the traditional design of circumferential arrangement, enabling the imaging system to detect simultaneously from multiple angles, improving detection accuracy and breadth, and effectively solving the problems of limited-angle scanning and data truncation.

[0202] For example, N2 = 2M, meaning the number of second sub-detectors N2 can be equal to twice the number of distributed radiation sources. In other words, a second sub-detector is placed on both sides of each distributed radiation source. This arrangement expands the detection range for each distributed radiation source, improving detection accuracy and breadth, and thus more effectively addressing the problems of finite angle scanning and data truncation.

[0203] FIG. 16 A schematic diagram illustrating the arrangement of the second sub-detectors according to some embodiments of the present invention is shown. FIG. 16 A schematic diagram of the arrangement of the second sub-detectors according to other embodiments of the present invention is shown.

[0204] Reference FIG. 17 With the X-ray source body 3012 arranged perpendicular to the first direction z, the second sub-detector 4022 can be arranged perpendicular to the first direction z. That is, the X-ray source body 3012 and the second sub-detector 4022 are arranged parallel to each other.

[0205] Reference FIG. 17 When the X-ray source body 3012 is arranged at an angle relative to the first direction z, the second sub-detector 2022 can be arranged parallel to the X-ray source body 3012, that is, the second sub-detector 2022 is arranged at an angle relative to the first direction z. In other words, both surfaces of the second sub-detector 2022 in the first direction z are arranged at an angle relative to the first direction z.

[0206] Reference FIG. 18A When the X-ray source body 3012 is arranged at an angle relative to the first direction z, the second sub-detector 4022 may not be arranged parallel to the X-ray source body 3012, and at least one of the two surfaces of the second sub-detector 4022 in the first direction z is perpendicular to the first direction z.

[0207] According to embodiments of the present invention, the choice between an inclined or vertical arrangement depends on the specific imaging target, the nature of the object, and the desired imaging effect. Arranging the second sub-detector at an angle relative to the first direction z can optimize the detector's coverage of a specific area, especially in scenarios requiring the capture of the motion trajectory of dynamic objects or irregular shapes, but may require more complex calibration and algorithm adjustments; a vertical arrangement is generally simpler, easier to implement, and does not require complex angle calibration.

[0208] It should be noted that the technical solution of the CT imaging system 300 provided in this embodiment of the invention can be combined with relevant features of the CT imaging system 200, and this combination is not limited to specific forms and methods, aiming to achieve better technical effects through various possible combinations. Based on this, the combination between the two systems can be flexibly adjusted and optimized according to actual application scenarios.

[0209] Embodiments of the present invention also provide an imaging method for a CT imaging system. FIG. 18B A flowchart of an imaging method for a CT imaging system according to some exemplary embodiments of the present invention is shown.

[0210] like FIG. 18A As shown, the imaging method may include steps S110-S140. It should be noted that steps S110-S140 are not a restriction on the order of the imaging method. Where there is no conflict, the imaging method may be executed in parallel or in a different order than that described in this document.

[0211] In step S110, the object to be imaged is placed in the imaging channel.

[0212] In embodiments of the present invention, the object to be imaged can be controlled to move at a predetermined speed in the imaging channel.

[0213] In step S120, at least q target points of at least one of the M distributed X-ray sources are controlled to emit X-ray beams in a predetermined beam emission sequence and at a predetermined beam emission time interval to form an imaging region.

[0214] Furthermore, to reduce image artifacts caused by object motion, the CT imaging system 300, specifically the q target points included in at least one of the M distributed X-ray sources, can be used to control the beam interval time to ensure continuous image acquisition. Specifically, the beam interval time can be determined based on the tilt angle of the q target points relative to the first direction z.

[0215] In embodiments of the present invention, at any given time, only one of the M distributed radiation sources may generate X-rays. Alternatively, multiple target points may generate X-rays from the same distributed radiation source at the same time. Or, multiple distributed radiation sources may generate X-rays from the same target point at the same location at the same time.

[0216] For example, when the object to be imaged is located in the imaging region, the target point of at least two of the M distributed X-ray sources can be controlled to emit beams simultaneously, 1 ≤ k ≤ q. Here, "simultaneous beam emission" means that during the imaging process, the emission of the X-ray beam can be precisely controlled within milliseconds or less, thereby controlling the target points of at least two or more of the M distributed X-ray sources to emit X-ray beams at almost the same time. Simultaneous beam emission can acquire a large amount of data in a very short time, thus significantly reducing imaging time.

[0217] FIG. 18B A schematic diagram of the projection plane of a CT imaging system with simultaneous beam emission from multiple targets according to some exemplary embodiments of the present invention is shown.

[0218] like FIG. 19As shown, when the object to be imaged is located in the imaging region, multiple target points can be controlled to emit beams in the following order: When j takes values ​​from 1 to q-1, the j-th target point of each of the M distributed X-ray sources emits beams simultaneously; then, the (j+1)-th target point of each of the M distributed X-ray sources emits beams simultaneously. Specifically, in the first direction z, the (j+1)-th target point is located downstream of the j-th target point.

[0219] For example, the beam exit sequence could be: the first target point of all distributed X-ray sources, the second target point of all distributed X-ray sources, ..., and so on. Here, "first" and "second" are only used to indicate the positional relationship between X-ray sources or target points. The beam exit time interval can be determined based on the following relationship:

[0220] t=s*cosθ / v (3)

[0221] Where t is the beam emission time interval, s is the distance between two adjacent target points in the q target points, v is the moving speed, and θ is the tilt angle of the q target points relative to the first direction.

[0222] In embodiments of the present invention, when the object to be imaged is located in the imaging region, at least two of the M distributed X-ray sources can be controlled to emit beams at the k-th target point in a time-division manner. Here, "time-division beam emission" corresponds to "simultaneous beam emission," meaning that during the imaging process, X-ray beams from different distributed X-ray sources can be emitted sequentially according to a predetermined beam emission order and a predetermined beam emission time interval, thereby separating the beam emission in the time dimension. This time-division beam emission method can reduce mutual interference between different X-ray beams, reduce signal overlap and noise, thereby improving the clarity and contrast of the image.

[0223] FIG. 19 A schematic diagram of the projection plane of a multi-target time-division beam output CT imaging system according to some embodiments of the present invention is shown.

[0224] like FIG. 19 As shown, when the object to be imaged is located in the imaging region, multiple target points can be controlled to emit beams in the following order: when j takes values ​​from 1 to q-1, the j-th target point of the M distributed X-ray sources emits beams sequentially in a time-sharing manner; then, the (j+1)-th target point of the M distributed X-ray sources emits beams sequentially in a time-sharing manner, wherein, in the first direction, the (j+1)-th target point is located downstream of the j-th target point.

[0225] For example, the beam emission sequence can be as follows: the first target point of the first distributed X-ray source, the first target point of the second distributed X-ray source, ..., the first target point of the Nth distributed X-ray source, the second target point of the first distributed X-ray source, the second target point of the second distributed X-ray source, ..., the second target point of the Nth distributed X-ray source, and so on. The beam emission time interval can be determined based on the following relationship:

[0226] t=s*cosθ / (M*v) (4)

[0227] Where t is the beam emission time interval, s is the distance between two adjacent target points in the q target points, v is the moving speed, and θ is the tilt angle of the q target points relative to the first direction.

[0228] In an embodiment of the present invention, the beam-out time interval satisfies the following: during the imaging time, along the first direction, q target points and the object to be imaged are in a relatively stationary state, so as to obtain a higher spatial resolution of the current scanning area.

[0229] By controlling the tilt of the X-ray source, multiple X-ray beams can scan the same cross-section as the object moves. Thus, even though the object's position in space changes, the imaging process captures a relatively "stationary" viewpoint because the X-rays are always aligned with a specific part of the object. Therefore, this relative stillness ensures that the captured image does not shift position due to the object's movement. Since the X-rays consistently illuminate the same interface or path of the object, the continuity of image acquisition is maintained, significantly reducing artifacts caused by motion.

[0230] In embodiments of the present invention, the beam exit time interval of the CT imaging system can reach the microsecond level; the single acquisition time of the detector can be 30-150 microseconds; and the imaging resolution of the imaging method can be 1-30 milliseconds.

[0231] In step S130, at least one detector is used to detect rays emitted from at least one distributed ray source and passing through the object to be imaged, and projection data is generated based on the detected rays.

[0232] In embodiments of the present invention, when rays pass through the object to be imaged, tissues or substances of different densities and compositions have different effects on the absorption and scattering of the rays, which are then converted into projection data. This data is a two-dimensional representation of the object's internal structure, containing information about the object being imaged from different angles.

[0233] In step S140, a computed tomography image of the object to be imaged is generated based on the projection data. Algorithms (such as backprojection, iterative reconstruction, etc.) can be used to convert the two-dimensional projection data into a three-dimensional image.

[0234] In embodiments of the present invention, precise timing control and data acquisition of the imaging process are achieved by employing a predetermined beam emission sequence and time interval determined based on the tilt angle of the target point relative to a first direction. The tilted target point and precise beam emission time interval provide richer angular data, increasing data redundancy and contributing to subsequent image reconstruction and artifact reduction. The imaging method provided by this invention not only significantly improves imaging accuracy and quality and optimizes the synchronization of beam emission and data acquisition in dynamic imaging, but also effectively reduces image distortion and artifacts caused by object movement.

[0235] ​ It is an image obtained using imaging systems and imaging methods in related technologies. ​ The images are obtained using the imaging system and imaging method provided in the embodiments of the present invention. (Refer to reference...) ​ and ​ In an embodiment of the present invention, during the imaging time, along the first direction, q target points and the object to be imaged are in a relatively stationary state, which can better avoid motion artifacts and obtain higher quality images.

[0236] ​ A block diagram of an electronic device suitable for implementing the methods described above, according to an embodiment of the present invention, is shown schematically. ​ The electronic device shown is merely an example and should not be construed as limiting the functionality and scope of the embodiments of the present invention.

[0237] like ​ As shown, an electronic device 1900 according to an embodiment of the present invention includes a processor 1901, which can perform various appropriate actions and processes according to a program stored in a read-only memory (ROM) 1902 or a program loaded from a storage portion 1908 into a random access memory (RAM) 1903. The processor 1901 may include, for example, a general-purpose microprocessor (e.g., a CPU), an instruction set processor and / or an associated chipset and / or a special-purpose microprocessor (e.g., an application-specific integrated circuit (ASIC)), etc. The processor 1901 may also include onboard memory for caching purposes. The processor 1901 may include a single processing unit or multiple processing units for performing different actions of the method flow according to an embodiment of the present invention.

[0238] RAM 1903 stores various programs and data required for the operation of electronic device 1900. Processor 1901, ROM 1902, and RAM 1903 are interconnected via bus 1904. Processor 1901 executes various operations of the method flow according to embodiments of the present invention by executing programs in ROM 1902 and / or RAM 1903. It should be noted that the programs may also be stored in one or more memories other than ROM 1902 and RAM 1903. Processor 1901 may also execute various operations of the method flow according to embodiments of the present invention by executing programs stored in said one or more memories.

[0239] According to an embodiment of the present invention, the electronic device 1900 may further include an input / output (I / O) interface 1905, which is also connected to a bus 1904. The electronic device 1900 may also include one or more of the following components connected to the input / output (I / O) interface 1905: an input section 1906 including a keyboard, mouse, etc.; an output section 1907 including a cathode ray tube (CRT), liquid crystal display (LCD), etc., and a speaker, etc.; a storage section 1908 including a hard disk, etc.; and a communication section 1909 including a network interface card such as a LAN card, modem, etc. The communication section 1909 performs communication processing via a network such as the Internet. A drive 1910 is also connected to the input / output (I / O) interface 1905 as needed. A removable medium 1911, such as a magnetic disk, optical disk, magneto-optical disk, semiconductor memory, etc., is installed on the drive 1910 as needed so that computer programs read from it can be installed into the storage section 1908 as needed.

[0240] According to embodiments of the present invention, the method flow according to embodiments of the present invention can be implemented as a computer software program. For example, embodiments of the present invention include a computer program product comprising a computer program carried on a computer-readable storage medium, the computer program containing program code for performing the method shown in the flowchart. In such embodiments, the computer program can be downloaded and installed from a network via communication section 1909, and / or installed from removable medium 1911. When the computer program is executed by processor 1901, it performs the functions defined in the system of the embodiments of the present invention. According to embodiments of the present invention, the systems, devices, apparatuses, modules, units, etc., described above can be implemented by computer program modules.

[0241] The present invention also provides a computer-readable storage medium, which may be included in the device / apparatus / system described in the above embodiments; or it may exist independently and not assembled into the device / apparatus / system. The computer-readable storage medium carries one or more programs, which, when executed, implement the method according to the embodiments of the present invention.

[0242] According to embodiments of the present invention, a computer-readable storage medium may be a non-volatile computer-readable storage medium. Examples include, but are not limited to: portable computer disks, hard disks, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EQROM or flash memory), portable compact disk read-only memory (CD-ROM), optical storage devices, magnetic storage devices, or any suitable combination thereof. In this invention, a computer-readable storage medium may be any tangible medium containing or storing a program that can be used by or in conjunction with an instruction execution system, apparatus, or device.

[0243] For example, according to embodiments of the present invention, a computer-readable storage medium may include one or more memories other than the ROM 1902 and / or RAM 1903 described above and / or ROM 1902 and RAM 1903.

[0244] Embodiments of the present invention also include a computer program product comprising a computer program containing program code for performing the methods provided in the embodiments of the present invention. When the computer program product is run on an electronic device, the program code is used to enable the electronic device to implement the methods provided in the embodiments of the present invention.

[0245] When the computer program is executed by the processor 1901, it performs the functions defined in the system / apparatus of this embodiment of the invention. According to embodiments of the invention, the systems, apparatuses, modules, units, etc., described above can be implemented by computer program modules.

[0246] In one embodiment, the computer program may rely on a tangible storage medium such as an optical storage device or a magnetic storage device. In another embodiment, the computer program may also be transmitted and distributed in the form of signals over a network medium, and may be downloaded and installed via the communication section 1909, and / or installed from a removable medium 1911. The program code contained in the computer program can be transmitted using any suitable network medium, including but not limited to: wireless, wired, etc., or any suitable combination thereof.

[0247] According to embodiments of the present invention, program code for executing the computer programs provided in the embodiments of the present invention can be written in any combination of one or more programming languages. Specifically, these computational programs can be implemented using high-level procedural and / or object-oriented programming languages, and / or assembly / machine languages. Programming languages ​​include, but are not limited to, languages ​​such as Java, C++, Qython, "C", or similar programming languages. The program code can be executed entirely on the user's computing device, partially on the user's device, partially on a remote computing device, or entirely on a remote computing device or server. In cases involving remote computing devices, the remote computing device can be connected to the user's computing device via any type of network, including a local area network (LAN) or a wide area network (WAN), or it can be connected to an external computing device (e.g., via the Internet using an Internet service provider).

[0248] The flowcharts and block diagrams in the accompanying drawings illustrate the architecture, functionality, and operation of possible implementations of systems, methods, and computer program products according to various embodiments of the present invention. In this regard, each block in a flowchart or block diagram may represent a module, segment, or portion of code containing one or more executable instructions for implementing a specified logical function. It should also be noted that in some alternative implementations, the functions indicated in the blocks may occur in a different order than those indicated in the drawings. For example, two consecutively indicated blocks may actually be executed substantially in parallel, and they may sometimes be executed in reverse order, depending on the functions involved. It should also be noted that each block in a block diagram or flowchart, and combinations of blocks in a block diagram or flowchart, may be implemented using a dedicated hardware-based system that performs the specified function or operation, or using a combination of dedicated hardware and computer instructions. Those skilled in the art will understand that the features described in the various embodiments of the present invention can be combined and / or combined in various ways, even if such combinations or combinations are not explicitly described in the present invention. In particular, the features described in the various embodiments of the present invention can be combined and / or combined in various ways without departing from the spirit and teachings of the present invention. All such combinations and / or pairings fall within the scope of this invention.

[0249] The embodiments of the present invention have been described above. However, these embodiments are merely illustrative and not intended to limit the scope of the invention. Although various embodiments have been described above, this does not mean that the measures in the various embodiments cannot be used advantageously in combination. Various substitutions and modifications can be made by those skilled in the art without departing from the scope of the invention, and all such substitutions and modifications should fall within the scope of the invention.

Claims

1. A CT imaging system, characterized in that, The CT imaging system includes: An imaging channel, at least a portion of which extends along a first direction z, the imaging channel being used to place an object to be imaged during the imaging process; M distributed X-ray sources are arranged at circumferential intervals along the imaging channel, and at least one of the distributed X-ray sources includes q target points configured to emit X-rays, where M and q are both positive integers greater than or equal to 2; and N detectors are arranged at circumferential intervals along the imaging channel. These N detectors are used to detect rays emitted from the M distributed radiation sources and passing through the object to be imaged. N is a positive integer greater than or equal to M. The detector includes a first sub-detector, and the CT imaging system includes multiple imaging components. Each imaging component includes at least one distributed X-ray source and at least one first sub-detector. Within the same imaging component, the distributed X-ray source and the first sub-detector are arranged face-to-face in the radial direction of the imaging channel. Furthermore, within the same imaging component, at least one target point of the distributed X-ray source and at least a portion of the first sub-detector are located in the same plane perpendicular to the first direction z, where the radial direction is perpendicular to the first direction z. At least one of the M distributed radiation sources includes q target points arranged at an angle relative to the first direction z. The CT imaging system includes a controller configured to control the beam interval time of multiple target points and control the movement speed of the object to be imaged, such that during the imaging time, along the first direction z, the q target points and the object to be imaged are in a relatively stationary state.

2. The system according to claim 1, characterized in that, In at least one of the M distributed radiation sources, the q target points of the same distributed radiation source are arranged at intervals along a first straight line, the extension direction of the first straight line being inclined relative to the first direction z.

3. The system according to claim 2, characterized in that, At least one of the M distributed radiation sources includes a radiation source body and q target points mounted on the radiation source body, wherein the radiation source body is tilted relative to the first direction z.

4. The system according to claim 2, characterized in that, At least one of the M distributed radiation sources includes a radiation source body and q target points mounted on the radiation source body. The radiation source body is perpendicular to the first direction z, and the q target points mounted on the radiation source body are arranged at an angle relative to the first direction z.

5. The system according to claim 2, characterized in that, The q target points of the M distributed radiation sources are respectively arranged at an angle relative to the first direction z, and the first straight line containing at least two of the q target points has an unequal angle of inclination relative to the first direction z.

6. The system according to claim 2, characterized in that, The first straight line containing the q target points of the M distributed radiation sources has an equal angle of inclination relative to the first direction z.

7. The system according to any one of claims 2-4, characterized in that, The angle of inclination θ between the extension direction of the first straight line and the first direction z satisfies the following relationship: cosθ = v * t / s Where s is the distance between two adjacent target points along the extension direction of the first straight line among the q target points, v is the moving speed of the object to be imaged, and t is the beamout interval time.

8. The system according to claim 1, characterized in that, The M distributed radiation sources each include q target points, and the q target points of the M distributed radiation sources each have z-axis position coordinates in the first direction z; and The z-axis position coordinates of the i-th target point of the M distributed radiation sources are equal to each other, where 1≤i≤q.

9. The system according to any one of claims 1-6, characterized in that, The M distributed radiation sources each include q target points, and the q target points of the M distributed radiation sources each have z-axis position coordinates in the first direction z; and The z-axis position coordinates of the i-th target point of the M distributed radiation sources are not equal to each other, where 1≤i≤q.

10. The system according to claim 8, characterized in that, The controller is configured to control multiple target points with equal z-axis position coordinates of the M distributed ray sources to emit beams simultaneously.

11. The system according to any one of claims 1-6, characterized in that, The detector further includes a second sub-detector, and at least one second sub-detector is provided on at least one side of at least one of the distributed radiation sources in the first direction z.

12. The system according to any one of claims 1-6, characterized in that, The M distributed X-ray sources are uniformly arranged at equal intervals along the circumference of the imaging channel; and / or, The CT imaging system includes M first sub-detectors, which are evenly arranged at equal intervals along the circumference of the imaging channel.

13. The system according to any one of claims 1-6, characterized in that, The M distributed radiation sources cover an angle range of 90°-120°; or The M distributed radiation sources cover an angle range of 120°-150°; or The radiation angle coverage range of the M distributed radiation sources is 140°-160°.

14. The system according to any one of claims 1-6, characterized in that, The CT imaging system includes M first sub-detectors, and the M distributed X-ray sources and the M first sub-detectors are arranged alternately circumferentially along the imaging channel.

15. The system according to claim 11, characterized in that, The second sub-detector is arranged at an angle relative to the first direction z; or, The second sub-detector is arranged perpendicular to the first direction z.

Images