Radiation detector assembly and medical imaging device

Abstract

The embodiment of the utility model provides a radiation detector assembly and medical imaging equipment, and the radiation detector assembly comprises a supporting frame which comprises a plurality of supporting surfaces arranged at one side facing a ray radiation source, and the plurality of supporting surfaces are tangent to an arc with the radiation source as the circle center; and the plurality of radiation detector modules are respectively arranged on the plurality of supporting surfaces so as to receive the rays attenuated by the detected object and convert the rays into electric signals.

Description

TECHNICAL FIELD

[0001] Embodiments of the present application relate to the technical field of imaging equipment, and particularly relate to a radiation detector assembly and a medical imaging equipment. BACKGROUND

[0002] Imaging equipment is used to scan a subject (such as a patient or a workpiece) in a non-invasive or non-destructive manner, so as to obtain an internal structure image of an anatomical tissue or a part of interest of the subject, to assist in diagnosis. The imaging equipment usually includes a circular scanning hole for the subject to move in or out, and a detector installed along the entire circumference or a partial arc of the circular hole, which includes a plurality of detector assemblies installed on a gantry.

[0003] For example, a computed tomography (CT) device is usually used as a kind of medical imaging equipment to scan a patient to obtain a tomographic image of a part of interest of the patient to assist a doctor in diagnosis. The CT device includes a plurality of detector assemblies that receive X-rays emitted from an X-ray tube and pass through the patient, and the form and number of each detector assembly depend on the clinical requirements and the design of the CT system.

[0004] The detector in the CT device is composed of a plurality of radiation detector assemblies, which are installed on a guide rail that is integrally formed and has a certain arc plate structure and can be installed on a gantry (or a rotating gantry). The plurality of radiation detector assemblies are sequentially arranged on the guide rail along the extension direction of the guide rail, and are installed on the guide rail by a certain mounting method, such as a mounting hole provided on the guide rail and a mechanical mounting method. The plurality of radiation detector assemblies are arranged on the gantry by being installed on the guide rail, and rotate with the movement of the gantry. Each detector cell or pixel of the radiation detector assembly is usually arranged to face the direction of the ray source, so that the rays passing through the scanning object are fully absorbed, thereby providing imaging quality. In order to make each detector cell or pixel of the radiation detector assembly accurately face the ray source, each radiation detector assembly usually has a small size in the direction of rotation or the extension direction of the guide rail, and accordingly, the number of radiation detector assemblies is large, and the cost of the CT device is also increased. If the size of each radiation detector assembly in the direction of rotation or the extension direction of the guide rail is increased, the quality of the ray signal acquired by the radiation detector assembly will be poor, and accordingly, the CT device needs to be specially calibrated in geometry and the reconstructed image quality is also poor.

[0005] It should be noted that the above introduction to the technical background is only for the convenience of clearly and completely describing the technical solutions of the present application, and for the convenience of understanding by those skilled in the art. Practical new type content

[0006] In order to solve at least one of the above technical problems or other similar problems, the embodiments of the present application provide a radiation detector assembly and a medical imaging device. A plurality of support surfaces are arranged on a support frame of the radiation detector assembly, and the plurality of support surfaces are tangent to an arc with a radiation source as a center. On one hand, the radiation detector assembly is arranged to be close to the arc with the radiation source as the center, that is, the units or pixels of each radiation detector module are more accurately directed to the radiation source, and the gap between adjacent radiation detector modules is reduced, thereby simplifying the geometric calibration processing of the signals acquired by the radiation detector assembly, reducing the image reconstruction complexity while ensuring the image quality. On the other hand, the same support frame can carry a plurality of radiation detector modules, thereby reducing the manufacturing cost of the radiation detector assembly.

[0007] According to an aspect of the embodiments of the present application, a radiation detector assembly is provided, comprising:

[0008] a support frame comprising a plurality of support surfaces arranged on a side facing a radiation source, the plurality of support surfaces being tangent to an arc with the radiation source as a center;

[0009] a plurality of radiation detector modules arranged on the plurality of support surfaces respectively to receive rays attenuated by a detected object and convert the rays into electrical signals.

[0010] According to another aspect of the embodiments of the present application, a medical imaging device is provided, comprising:

[0011] a gantry;

[0012] a radiation source arranged on the gantry;

[0013] the aforementioned radiation detector assembly arranged on the gantry and configured to receive rays attenuated by a detected object.

[0014] Specific embodiments of the present application are disclosed in detail in the following description and accompanying drawings, indicating the ways in which the principles of the present application can be employed. It should be understood that the embodiments of the present application are not limited in scope in terms of the appended claims and their equivalents. The embodiments of the present application include many changes, modifications and equivalents within the spirit and scope of the appended claims. BRIEF DESCRIPTION OF DRAWINGS

[0015] The accompanying drawings, which are included to provide a further understanding of the application and are incorporated in and constitute a part of this specification, illustrate embodiments of the application and together with the description serve to explain the principles of the application. In the drawings:

[0016] Figure 1 is a schematic diagram of a CT device according to an embodiment of the application;

[0017] Figure 2 is a schematic diagram of a CT imaging system according to an embodiment of the application;

[0018] Figure 3 is a schematic diagram of a radiation detector assembly according to an embodiment of the application;

[0019] Figure 4 is a schematic diagram of a radiation detector according to an embodiment of the application;

[0020] Figure 5 is a schematic diagram of a radiation detector according to an embodiment of the application;

[0021] Figure 6 is a schematic diagram of a support frame according to an embodiment of the application;

[0022] Figure 7 is a schematic diagram of a support frame according to an embodiment of the application;

[0023] Figure 8 is a schematic diagram of a support frame according to an embodiment of the application;

[0024] Figure 9 is a schematic diagram of a support frame according to an embodiment of the application;

[0025] Figure 10 is a schematic diagram of a radiation detector module according to an embodiment of the application;

[0026] Figure 11 is a schematic diagram of a radiation detector module according to an embodiment of the application;

[0027] Figure 12 is a schematic diagram of a radiation detector assembly according to an embodiment of the application;

[0028] Figure 13 is a schematic diagram of a radiation detector assembly according to an embodiment of the application;

[0029] Figure 14 is a schematic diagram of a radiation detector assembly according to an embodiment of the application;

[0030] Figure 15 is a schematic diagram of a radiation detector assembly according to an embodiment of the application;

[0031] Figure 16 is a schematic diagram of a radiation detector assembly according to an embodiment of the application. DETAILED DESCRIPTION

[0032] The foregoing and other features of the present embodiments will become apparent to those skilled in the art upon consideration of the following description of specific embodiments of the application, taken in conjunction with the accompanying drawings. In the description of embodiments of the application, specific terminology is employed for the sake of clarity. However, the application is not intended to be limited to the specific embodiments described. Rather, the application is intended to include all modifications, equivalents, and alternatives that fall within the scope of the appended claims.

[0033] In the present embodiments, the terms “first”, “second”, and the like are used to distinguish different elements from one another, but do not indicate spatial arrangement or temporal order of the elements, and the elements should not be limited by these terms. The term “and / or” includes any one and all combinations of the associated listed terms. The terms “comprise”, “include”, “have”, and the like, mean the presence of stated features, elements, components, or assemblies, but do not preclude the presence or addition of one or more other features, elements, components, or assemblies.

[0034] In the present embodiments, the singular forms “a”, “an”, and “the” include plural referents unless the context clearly dictates otherwise. The term “said” is understood to mean “at least one” unless the context clearly dictates otherwise. In addition, the term “according to” is understood to mean “based at least in part on”, and the term “based on” is understood to mean “based at least in part on” unless the context clearly dictates otherwise.

[0035] Features described and / or illustrated with respect to one implementation can be used in one or more other implementations in the same or similar manner, in combination with or in place of the features of the other implementations. The term “comprise / comprising” is used herein to mean the presence of stated features, integers, steps, or components, but does not preclude the presence or addition of one or more other features, integers, steps, components, or groups thereof.

[0036] The medical imaging device described in the present application can be suitable for various medical imaging modalities, including but not limited to CT (Computed Tomography) imaging devices, PET (Positron Emission Computed Tomography)-CT or any other suitable medical imaging device.

[0037] The system for obtaining medical image data can include the aforementioned medical imaging device, can include a separate computer device connected to the medical imaging device, and can also include a computer device connected to the Internet cloud, which is connected to the medical imaging device or a memory storing medical images through the Internet. The imaging method can be implemented independently or jointly by the aforementioned medical imaging device, the computer device connected to the medical imaging device, and the computer device connected to the Internet cloud. For example, the system for obtaining medical image data can be a CT imaging system or the like.

[0038] Exemplarily, the embodiments of the present application are described below in combination with an X-ray computed tomography (CT) imaging device. Those skilled in the art will understand that the embodiments of the present application can also be applicable to other medical imaging devices.

[0039] Figure 1 is a schematic diagram of a CT device according to an embodiment of the present application, which schematically shows a case of the CT device 100. As shown in Figure 1 , the CT device 100 includes a scan gantry 101 and a patient table 102; the scan gantry 101 has an X-ray source 103, which projects an X-ray beam toward a detector assembly or a collimator 104 on the opposite side of the scan gantry 101. A detected object 105 can lie on the patient table 102 and move into the scan gantry opening 106 with the patient table 102; by scanning of the X-ray source 103, medical image data of the detected object 105 can be obtained.

[0040] Figure 2 is a schematic diagram of a CT imaging system according to an embodiment of the present application, which schematically shows a block diagram of the CT imaging system 10. As shown in Figure 2 , the system 10 includes a scan gantry 12, on which an X-ray source 14 and a detector 18 are oppositely arranged, the detector 18 is composed of a plurality of detector assemblies 20 and a data acquisition system (DAS) 26, the DAS 26 is used to convert sampled analog data into digital signals for subsequent processing.

[0041] In some embodiments, the system 10 is used to collect projection data of an object to be examined at different angles, therefore, the components on the gantry 12 are used to rotate around the rotation center 24 to collect the projection data. During the rotation, the X-ray radiation source 14 is used to project X-rays 16 penetrating the detected object toward the detector 18, the attenuated X-ray beam data is preprocessed as projection data of the target volume of the object, based on which an image of the detected object can be reconstructed, and the reconstructed image can show internal features of the detected object, including, for example, lesions, sizes, shapes, etc. of body tissue structures. The rotation center 24 of the gantry also defines the center of the scan domain 80.

[0042] In some embodiments, the system 10 includes a control mechanism 30. The control mechanism 30 can include an x-ray controller 34 for providing power and timing signals to the x-ray radiation source 14. The control mechanism 30 can also include a gantry controller 32 for controlling the rotational speed and / or position of the gantry 12 based on imaging requirements. The control mechanism 30 can also include a couch controller 36 for driving the couch 28 to move to a suitable position to position an object under examination in the gantry 12, perform a scout scan or axial scan or bolt scan or other scan modality, etc. to acquire projection data of a target volume of the object under examination. Further, the couch 28 includes a driving device, and the couch controller 36 can control the couch 28 by controlling the driving device.

[0043] The system 10 further includes an image reconstruction module 50. As described above, the DAS 26 samples and digitizes the projection data acquired by the plurality of detector assemblies 20. Then, the image reconstruction module 50 performs high-speed image reconstruction based on the sampled and digitized projection data described above. In some embodiments, the image reconstruction module 50 stores the reconstructed images in a storage device or mass memory 46. Alternatively, the image reconstruction module 50 transmits the reconstructed images to the computer 40 for generating patient information for diagnosis, evaluation, etc. For example, a first scout image and diagnostic cross-sectional images are generated based on the projection data acquired by a scout scan or axial scan or bolt scan or other scan modality, etc.

[0044] Although Figure 2 Although the image reconstruction module 50 is illustrated as a separate entity in FIG. 1, in certain embodiments, the image reconstruction module 50 can form part of the computer 40. Alternatively, the image reconstruction module 50 can not exist in the system 10, or the computer 40 can perform one or more functions of the image reconstruction module 50. In addition, the image reconstruction module 50 can be located at a local or remote location and can be connected to the system 10 using a wired or wireless network. In some embodiments, computing resources centralized in a cloud network can be used for the image reconstruction module 50.

[0045] In some embodiments, the system 10 further includes a computer 40 to which the data sampled and digitized by the DAS 26 and / or the images reconstructed by the image reconstruction module 50 are transmitted for processing. In some embodiments, the computer 40 stores the data and / or images in a storage device, such as a mass memory 46. The mass memory 46 can include a hard disk drive, a floppy disk drive, a compact disk read / write (CD-R / W) drive, a digital versatile disk (DVD) drive, a flash drive, and / or a solid-state storage device, etc. The processor in the computer 40 determines a predicted cross-sectional image from the first scout image.

[0046] In some embodiments, the computer 40 transmits the reconstructed images and / or other information to a display 42, which is communicatively coupled to the computer 40 and / or the image reconstruction module 50. The computer 40 can be connected to local or remote displays, printers, workstations, and / or similar devices, e.g., such devices of a medical facility or hospital, or remote devices via one or more configured wires or wireless networks such as the Internet and / or virtual private networks. For example, the display displays the predicted profile images and corresponding scan parameters.

[0047] Further, the computer 40 can be based on user-provided and / or system-defined commands and parameters to provide to the DAS 26, and the control mechanisms 30 (including the gantry controller 32, the x-ray controller 34, and the support couch controller 36), etc., to control system operations, e.g., data acquisition and / or processing. In some embodiments, the computer 40 controls system operations based on user input, e.g., the computer 40 can receive user input, including commands, scan protocols, and / or scan parameters, via an operator console 48 connected thereto. The operator console 48 can include a keyboard (not shown) and / or a touch screen to allow user input / selection of commands, scan protocols, and / or scan parameters.

[0048] In some embodiments, the system 10 can include or be connected to an image storage and transmission system (PACS) (not shown). In some embodiments, the PACS is further connected to remote systems, e.g., a radiology information system, a hospital information system, and / or an internal or external network (not shown), to allow operators located at different sites to provide commands and parameters, and / or access image data.

[0049] The computer 40 can be set up and / or arranged to be used in different ways. For example, in some implementations, a single computer 40 can be used; in other implementations, multiple computers 40 are configured to work together (e.g., based on a distributed processing configuration) or separately, each computer 40 being configured to handle particular aspects and / or functions, and / or to process data for generating models for use with only particular systems 10. In some implementations, the computer 40 can be local (e.g., co-located with one or more systems 10, e.g., within the same facility and / or the same local network); in other implementations, the computer 40 can be remote, and thus only accessible via a remote connection (e.g., via the Internet or other available remote access technology). In particular implementations, the computer 40 can be configured in a cloud-like manner, and can be accessed and / or used in substantially similar ways as other cloud-based systems are accessed and used.

[0050] The above illustrates the device and system for obtaining medical image data (or also referred to as medical image or medical image data) of the embodiments of the present application, but the present application is not limited thereto. The medical imaging device can be a CT device, a PET-CT or any other suitable imaging device. The storage device can be located in the medical imaging device, in a server outside the medical imaging device, in a separate medical image storage system (e.g., a PACS, Picture Archiving and Communication System) and / or in a remote cloud storage system.

[0051] In addition, the medical imaging workstation can be located locally to the medical imaging device, i.e., the medical imaging workstation is located adjacent to the medical imaging device, and both can be located together in a scanning room, an imaging department or the same hospital. The medical image cloud platform analysis system can be located remotely from the medical imaging device, e.g., at a cloud end in communication with the medical imaging device.

[0052] As an example, after the medical imaging device is used by a medical institution to complete an imaging scan, the scanned data is stored in the storage device; the medical imaging workstation can directly read the scanned data and perform image processing through the processor thereof. As another example, the medical image cloud platform analysis system can read the medical image in the storage device through remote communication to provide "Software as a Service" (SaaS). The SaaS can exist between hospitals, between a hospital and an imaging center, or between a hospital and a third-party online diagnosis service provider.

[0053] The above illustrates the medical image scanning, and the embodiments of the present application are specifically described below with reference to the accompanying drawings. In the following embodiments, the medical imaging device is taken as an example of a CT device, and the description is also applicable to other medical imaging devices. However, the embodiments of the present application are not limited thereto.

[0054] The embodiments of the present application provide a radiation detector assembly.

[0055] Figure 3 is a schematic diagram of a radiation detector assembly of the embodiments of the present application. As shown in Figure 3 The radiation detector assembly 400 includes:

[0056] a support frame 401 including a plurality of support surfaces 4011-1, 4011-2, …, 4011-N arranged on a side facing a radiation source, the plurality of support surfaces being tangent to a circular arc with the radiation source as a center;

[0057] A plurality of radiation detector modules 4021-1, 4021-2, …, 4021-M are arranged on the plurality of support surfaces 4011-1, 4011-2, …, 4011-N respectively to receive the rays attenuated by the detected object and convert the rays into electrical signals.

[0058] In some embodiments, the radiation detector can include a plurality of radiation detector assemblies arranged along a circular arc with the radiation source as the center, and the radiation detector assemblies can have a flat panel form factor, i.e., the support frame and the radiation detector modules constituting the radiation detector assemblies have a flat panel form factor. The flat panel form factor means that the size of the radiation receiving plane of the support frame and the radiation detector modules receiving the rays or facing the radiation source is much larger or several times larger than the size parallel to the ray propagation path, for example, the length or width of the support frame or the radiation detector module is much larger than the thickness.

[0059] Figure 4 is a perspective view of a radiation detector according to an embodiment of the present application, Figure 5 is a cross-sectional view of a radiation detector according to an embodiment of the present application viewed in the z direction. As Figure 4 and Figure 5 indicated, the z direction is the direction in which the channel of the radiation detector assembly extends, i.e., the direction in which the detected object 105 or the patient table 102 moves forward and backward or moves into and out of the opening 106 of the scanning gantry, the direction in which the detected object moves in the medical imaging device); the x direction is the direction in which the circular arc with the radiation source as the center extends, i.e., the direction in which the detected object 105 or the patient table 102 moves left and right or moves laterally, or the direction in which the radiation detector assembly rotates and moves; and the y direction is the direction perpendicular to both the x direction and the z direction, i.e., the direction in which the detected object 105 or the patient table 102 moves up and down. Figure 1 Figure 1 Figure 1 Figure 4 and Figure 5 In the above embodiments, the radiation detector 51 includes a plurality of radiation detector assemblies 400 arranged along the circular arc, and one of the radiation detector assemblies is described in the following embodiments, and the structures of the other radiation detector assemblies are similar to that of the described radiation detector assembly.

[0060] Figure 6 is a perspective view of a support frame 401 according to an embodiment of the present application, Figure 7 is a cross-sectional view of a support frame 401 according to an embodiment of the present application viewed in the z direction. As Figure 6 and Figure 7 ​​​As shown, the upper surface of the support frame includes multiple support surfaces 4011-1, 4011-2, ..., 4011-N arranged on the side facing the radiation source. These support surfaces 4011-1, 4011-2, ..., 4011-N are tangent to (or parallel to the tangent direction of) a circular arc centered on the radiation source. In other words, the support surfaces are arranged approximately along the direction of the arc's extension, i.e., along the direction of rotation and movement of the radiation detector assembly. Different radiation detector assemblies are located at different positions on the arc, and different support surfaces of the support frame for the same radiation detector assembly correspond to different positions on the arc. Each support surface is tangent to the corresponding circular arc in the direction facing the radiation source. For example, the point of intersection between the perpendicular line from the center to a support surface and the arc is the point of tangency, and the support surface is parallel to the tangent line (tangent direction) passing through this point. Furthermore, the number and inclination of the support surfaces in the support frames of different radiation detector assemblies are the same.

[0061] For example, such as Figure 7 As shown, the intersection point of the perpendicular line from the center of the circle to the support surface 4011-1 and the arc is A1. The support surface 4011-1 is parallel to the tangent direction passing through A1. The intersection point of the perpendicular line from the center of the circle to the support surface 4011-2 and the arc is A2. The support surface 4011-2 is parallel to the tangent direction passing through A2. The intersection point of the perpendicular line from the center of the circle to the support surface 4011-3 and the arc is A3. The support surface 4011-3 is parallel to the tangent direction passing through A3.

[0062] In some embodiments, such as Figure 6 and Figure 7 As shown, the multiple support surfaces include at least two side support surfaces 4011-1 and 4011-2 formed at both ends of the support frame. These two side support surfaces 4011-1 and 4011-2 are inclined from the ends towards the center with the same inclination, and the inclination direction is consistent with the tangent direction of the arc at the corresponding position of the support surface center. The two side support surfaces 4011-1 and 4011-2 allow the arrangement of the radiation detector modules disposed on the side support surfaces 4011-1 and 4011-2 to approximate an arc centered on the radiation source. This makes the detector cells or pixels on the radiation detector modules more accurately oriented towards the radiation source and reduces the gaps between adjacent radiation detector modules. This simplifies the geometric calibration processing of the radiation signals acquired by the radiation detector assembly, reducing image reconstruction complexity while ensuring image quality.

[0063] In some embodiments, optionally, such as Figure 6 and Figure 7As shown, the plurality of support surfaces can further include a central support surface 4011-3 located in the middle of the support frame. By arranging three support surfaces, the arrangement of the radiation detector modules located on each support surface can be made to be closer to the circular arc with the radiation source as the center.

[0064] In some embodiments, the plurality of support surfaces can include more than three support surfaces arranged along the direction of the rotational movement of the radiation detector assembly. Figure 8 is a cross-sectional view of the support frame 401 of the embodiments of the present application viewed in the z direction, as shown in Figure 8 As shown, the plurality of support surfaces includes two side support surfaces 4011-1 and 4011-2 formed at the two ends of the support frame, and a central support surface 4011-3 located in the middle of the support frame. The plurality of support surfaces can further include a support surface 4011-4 located between the support surface 4011-1 and the support surface 4011-3, and a support surface 4011-5 located between the support surface 4011-2 and the support surface 4011-3, the two support surfaces 4011-4 and 4011-5 are inclined from the end to the center, and the inclination is consistent. The inclination is smaller than the inclination of the support surfaces 4011-1 and 4011-2. The embodiments of the present application do not limit the number of support surfaces, which will not be exemplified one by one here.

[0065] In some embodiments, the support frame is a one-piece structure, and the support frame includes a plurality of support portions arranged along the direction of the rotational movement of the radiation detector assembly, each support portion having a support surface facing the radiation source. As shown in Figure 7 As shown, the support frame is integrally formed, including three support portions 81, 82 and 83, the support portion 81 has a support surface 4011-1 facing the radiation source, the support portion 82 has a support surface 4011-2 facing the radiation source, and the support portion 83 has a support surface 4011-3 facing the radiation source.

[0066] In some embodiments, the support frame includes a frame body portion and a plurality of support portions, each support portion having a support surface facing the radiation source, the support portions are fixedly connected to the frame body portion by means of glue or screws, and the support portions are in the shape of a triangular prism, and the frame body portion is in the shape of a flat plate, such as a cuboid. Figure 9 is a schematic view of the support frame of the embodiments of the present application, as shown in Figure 9 As shown, the support frame includes a frame body portion 1001 and two support portions 1002-1 and 1002-2, the two support portions are in the shape of a right triangular prism, and one side of the right triangular prism serves as a support surface. The support portions 1002-1 and 1002-2 have support surfaces 1003-1 and 1003-2 facing the radiation source, respectively.

[0067] In some embodiments, the radiation detector module is fixed on the support surface of the support frame by screws or glue or buckles or the like. The number M of the plurality of radiation detector modules is equal to the number N of the support surfaces, and M and N are integers greater than 1. The plurality of radiation detector modules 4021-1, 4021-2, …, 4021-M are respectively and one-to-one arranged on the plurality of support surfaces 4011-1, 4011-2, …, 4011-N, and the widths of the plurality of support surfaces in the tangential direction of the circular arc are substantially the same. The structure of one radiation detector module is described below, and the structures of other radiation detector modules are similar to it.

[0068] Figure 10 is a schematic diagram of a radiation detector module according to an embodiment of the present application, as shown in Figure 10 The radiation detector module 1100 includes:

[0069] a radiation detector element 1101 configured to receive radiation emitted by the radiation source and convert the radiation into an electrical signal;

[0070] a detector circuit board 1102 having a first side on which the radiation detector element 1101 is mounted; and

[0071] a processing circuit chip 1103 disposed on a second side of the detector circuit board 1102 and in communication with the radiation detector element 1101.

[0072] In some embodiments, the detector circuit board 1102 can be a printed circuit board, the radiation detector element 1101 that is exposed to radiation can include a photoelectric conversion device 11011 (such as a backlit photodiode) and a scintillator 11012 having a plurality of scintillator pixels configured to receive attenuated radiation for converting the radiation into visible light, the photoelectric conversion device 11011 being optically coupled to the scintillator and configured to detect light output from the corresponding scintillator pixels and convert the light into an electrical signal. The radiation detector element 1101 can be located on the upper side of the detector circuit board 1102 (i.e., the side of the detector circuit board 1102 that is directly exposed to radiation). The above is only an example of the radiation detector element 1101, and the embodiments of the present application are not limited thereto. For example, the radiation detector element 1101 can not include a scintillator, but can include a photon counting detector element or other direct conversion detector element. Figure 10

[0073] ​In some embodiments, the processing circuit chip 1103 can receive the signals generated by the detector elements 313, including application specific integrated chip (ASIC), field programmable gate array (FPGA), power supply chip, etc., can be located on the other side (i.e. the lower side) of the detector circuit board 1102, i.e. the side of the detector circuit board 1102 which is not directly exposed to the radiation. Figure 10

[0074] Thus, the radiation detector elements and the processing circuit chip can be connected through the conductive paths through the circuit board, so that the connection is shorter and the connection is simpler and more integrated.

[0075] In some embodiments, the radiation detector module further comprises a radiation shielding component disposed between the detector circuit board 1102 and the processing circuit chip 1103. Figure 11 is a schematic diagram of a radiation detector module according to an embodiment of the present application, as Figure 11 shown, which Figure 10 differs from the above in that a radiation shielding component 1201 is further disposed between the detector circuit board 1102 and the processing circuit chip 1103, which can be a plate-shaped structure made of tungsten, lead, molybdenum or similar high X-ray attenuation metal material alloy, for absorbing the rays penetrating the detector circuit board to improve the image imaging quality and prevent the generation of artifacts in the image caused by the circuit board, etc.

[0076] In some embodiments, the radiation detector module further comprises a height compensation component disposed between the detector circuit board 1102 and the support frame, the height of the height compensation component being greater than or equal to the height of the processing circuit chip, which can be a gasket or other cylindrical structure, and the present application is not limited thereto. Figure 16 is a schematic diagram of a radiation detector assembly according to an embodiment of the present application, as Figure 16 shown, in which a height compensation component 1701 is disposed between each detector circuit board 1102 and the support frame 401, the height compensation component being disposed on both sides of the processing circuit chip and having a height greater than or equal to the height of the processing circuit chip, for protecting the processing circuit chip.

[0077] In some embodiments, the radiation detector assembly further comprises a collimator disposed on the radiation detector element, the collimator being configured to collimate the rays emitted by the radiation source to the radiation detector element.

[0078] ​In some implementations, the collimator includes a plurality of collimator modules, each of which includes a surface parallel to the support surface of the corresponding radiation detector module, i.e., each radiation detector module is provided with a collimator module covering the radiation detector elements, the upper and lower surfaces of the collimator module are parallel to the support surface, i.e., the upper and lower surfaces of the collimator module are parallel to the tangents of the corresponding position circle arcs. The plurality of collimator modules can be M independent 3D printed collimator modules.

[0079] Figure 12 is a schematic diagram of a radiation detector assembly according to an embodiment of the present application, as shown in Figure 12 The collimator includes a plurality of collimator modules 1301-1, 1301-2, …, 1301-M, a collimator module 1301-1 covers the radiation detector elements of the radiation detector module 4021-1, the upper and lower surfaces of the collimator module 1301-1 are parallel to the support surface 4011-1, a collimator module 1301-2 covers the radiation detector elements of the radiation detector module 4021-2, the upper and lower surfaces of the collimator module 1301-2 are parallel to the support surface 4011-2, and so on, a collimator module 1301-M covers the radiation detector elements of the radiation detector module 4021-M, the upper and lower surfaces of the collimator module 1301-M are parallel to the support surface 4011-M. Through the above implementation, each collimator module can have a dedicated angle towards the radiation source, which can reduce the shadow area of the two side channels, improve the signal-to-noise ratio, and reduce the variance of the two side channels compared to the middle channel. In addition, by providing a plurality of independent collimator modules, the number of low performing pixels (LPP) can be reduced, and the yield can be improved.

[0080] In some implementations, the collimator includes a one-piece collimator integrally covering all of the plurality of radiation detector modules, the upper and lower surfaces of the collimator are respectively a plane. The collimator can be a 3D printed one-piece collimator. Figure 14 is a schematic diagram of a radiation detector assembly according to an embodiment of the present application, as shown in Figure 14 The collimator 1501 integrally covers M radiation detector modules, and the upper and lower surfaces of the collimator are respectively a plane. Through the above implementation, compared with Figure 12 The one-piece collimator can reduce the gap between adjacent radiation detector modules (collimator modules) in the tangential direction of the circle arc, which can cause artifacts after image reconstruction, and further improve the image quality.

[0081] In some implementations, the collimator includes one integral collimator that integrally covers all of the plurality of radiation detector modules, and the collimator includes a surface parallel to the plurality of support surfaces. That is, the collimator is integral, and the upper and lower surfaces of the collimator are not planar, but also include a plurality of surfaces that respectively correspond to the plurality of support surfaces of the support frame and are parallel to each other. That is, the plurality of surfaces of the upper and lower surfaces of the collimator are parallel to the tangents of the corresponding position circles, and the collimator can be a 3D-printed integral collimator.

[0082] Figure 13 is a schematic diagram of a radiation detector assembly according to an embodiment of the present application, as Figure 13 shown, the collimator 1401 integrally covers the M radiation detector modules, and the upper surface of the collimator 1401 includes a plurality of surfaces 1401-1, 1401-2, …, 1401-M, the surface 1401-1 is parallel to the support surface 4011-1, the surface 1401-2 is parallel to the support surface 4011-2, and so on, and the surface 1401-M is parallel to the support surface 4011-M. Through the above implementation, the collimator can have a dedicated angle towards the radiation source, which can reduce the shadow area of the two side channels, improve the signal-to-noise ratio, and reduce the variance of the two side channels compared to the middle channel. In addition, the integral collimator can reduce the gap between adjacent radiation detector modules in the x direction, which can cause artifacts after image reconstruction, and further improve the image quality.

[0083] In some embodiments, the radiation detector assembly further includes a signal processing circuit board in communication with the detector circuit boards, and the signal processing circuit board is disposed on the side of the support frame opposite to the detector circuit boards. The signal processing circuit board can be in communication with all of the detector circuit boards of the plurality of radiation detector modules disposed on the support frame. The signal processing circuit board can receive the signals generated by the detector elements via the processing circuit chips, or receive the signals processed by the processing circuit chips. For example, the signal processing circuit board can be the aforementioned DAS 26, but the embodiments of the present application are not limited thereto.

[0084] Figure 15 is a schematic diagram of a radiation detector assembly according to an embodiment of the present application, and Figure 3 the difference is that, as Figure 15 shown, the signal processing circuit board 1601 is disposed on the lower side of the support frame 401, and the detector circuit board 1102 is disposed on the upper side of the support frame 401. The signal processing circuit board 1601 and each of the detector circuit boards 1102 can be in communication through a connection line 1602 (for example, a Flex connection line). The connection line is connected to the edge of the detector circuit board 1102.

[0085] In some embodiments, the support frame can be made of a metal heat conductive material (e.g., aluminum or aluminum alloy), and the support frame is thermally coupled to the detector circuit board and the signal processing circuit board, respectively, to dissipate heat. Since the detector circuit board and the signal processing circuit board generate a large amount of heat during operation, the support frame releases the heat generated by the detector circuit board and the signal processing circuit board to the surrounding air.

[0086] As can be seen from the above embodiments, by arranging the plurality of support surfaces on the support frame of the radiation detector assembly, the plurality of support surfaces are tangent to the circular arc with the radiation source as the center, so that the radiation detector assembly is arranged to approach the circular arc with the radiation source as the center as much as possible, that is, the units or pixels of each radiation detector module are more accurately directed toward the radiation source, and the gap between adjacent radiation detector modules is also reduced, thereby simplifying the geometric calibration processing of the signals acquired by the radiation detector assembly, reducing the image reconstruction complexity while ensuring image quality.

[0087] The embodiments of the present application also provide a medical imaging device. The medical imaging device of the present application is, for example, a CT (Computed Tomography) imaging device, a PET-CT or any other suitable medical imaging device. The medical imaging device comprises a gantry; a radiation source arranged on the gantry; a plurality of radiation detector assemblies, which can have a substantially flat panel form factor, the plurality of radiation detector assemblies being mounted on a guide rail, which is integrally formed and has a plate structure with a certain curvature, and which can be mounted on the gantry (or rotating gantry). The plurality of radiation detector assemblies are arranged on the guide rail in sequence along the extension direction of the guide rail, and are mounted on the guide rail by a certain mounting method, such as being arranged on the guide rail by means of fixing holes arranged on the guide rail and using a mechanical mounting method. The plurality of radiation detector assemblies are arranged on the gantry by being mounted on the guide rail, and rotate with the movement of the gantry. However, the embodiments of the present application are not limited thereto, and the implementation of each radiation detector assembly can refer to the radiation detector assembly in the foregoing embodiments. The medical imaging device projects the rays emitted by the radiation source onto the detected object, the plurality of radiation detector assemblies receive the attenuated rays of the detected object, and convert the rays into electrical signals, and performs tomographic imaging of the detected object according to the electrical signals generated by the plurality of radiation detector assemblies. The specific structure of the medical imaging device can refer to the implementation of the medical imaging device in the foregoing embodiments of the present application, and will not be described here. Figure 1

[0088] ​The various embodiments in the specification are described in a progressive manner, and each embodiment focuses on the difference from other embodiments, and the same and similar parts between various embodiments can be referred to each other. The above embodiments are only for illustrating the technical concept and characteristics of the utility model, and the purpose is to enable persons skilled in the art to understand the content of the utility model and implement it, and cannot limit the protection scope of the utility model. Any equivalent changes or modifications made according to the spirit and essence of the utility model shall be covered within the protection scope of the utility model.

Claims

1. A radiation detector assembly, characterized by, The radiation detector module includes: a radiation detector element that receives the rays emitted by the radiation source and converts the rays into an electrical signal; a detector circuit board having the radiation detector element mounted on a first side thereof; and 2. The radiation detector assembly of claim 1, wherein, a processing circuit chip disposed on a second side of the detector circuit board and in communication with the radiation detector element.

3. The radiation detector assembly of claim 1, wherein, The radiation detector module further includes a radiation shielding member disposed between the detector circuit board and the processing circuit chip.

4. The radiation detector assembly of claim 1, wherein, The radiation detector module further includes a height compensating member disposed between the detector circuit board and the support frame, the height compensating member having a height greater than or equal to a height of the processing circuit chip.

5. The radiation detector assembly of claim 1, wherein, The radiation detector assembly further includes a signal processing circuit board in communication with the detector circuit board, the signal processing circuit board disposed on a side of the support frame opposite the detector circuit board.

6. The radiation detector assembly of claim 1, wherein, The support frame is thermally coupled to the detector circuit board and the signal processing circuit board to dissipate heat.

7. The radiation detector assembly of claim 1, wherein, The number of radiation detector modules is equal to the number of support surfaces. The radiation detector assembly further includes a collimator disposed on the radiation detector element, the collimator configured to collimate the rays emitted by the radiation source to the radiation detector element. The collimator includes a single collimator that integrally covers all of the radiation detector modules, the collimator including a surface parallel to the support surfaces. The collimator includes a plurality of collimator modules that each cover a respective radiation detector module, the plurality of collimator modules each including a surface parallel to a support surface of the respective radiation detector module.

8. The radiation detector assembly of claim 7, wherein, The radiation detector assembly includes:

9. The radiation detector assembly of claim 7, wherein, a support frame including a plurality of support surfaces disposed on a side of the support frame facing the radiation source, the plurality of support surfaces being tangent to a circular arc having the radiation source as a center; 10. The radiation detector assembly of claim 7, wherein, a plurality of radiation detector modules disposed on the plurality of support surfaces to receive the rays attenuated by the object under examination and to convert the rays into electrical signals.

11. The radiation detector assembly of claim 10, wherein, The plurality of support surfaces includes at least two side support surfaces formed at two ends of the support frame.

12. The radiation detector assembly of claim 1, wherein, The plurality of support surfaces further includes a center support surface disposed in a middle of the support frame.

13. The radiation detector assembly of claim 7, wherein, The support frame and the plurality of radiation detector modules have a flat plate configuration.

14. The radiation detector assembly of claim 13, wherein, The support frame is a unitary structure including a plurality of support portions each having a support surface facing the radiation source.

15. The radiation detector assembly of claim 13, wherein, The support frame includes a frame body portion and a plurality of support portions each having a support surface facing the radiation source.

16. A medical imaging apparatus, characterized by The radiation detector module includes: a radiation detector element that receives the rays emitted by the radiation source and converts the rays into an electrical signal; a detector circuit board having the radiation detector element mounted on a first side thereof; and a processing circuit chip disposed on a second side of the detector circuit board and in communication with the radiation detector element. The radiation detector module further includes a radiation shielding member disposed between the detector circuit board and the processing circuit chip. The radiation detector module further includes a height compensating member disposed between the detector circuit board and the support frame, the height compensating member having a height greater than or equal to a height of the processing circuit chip. The radiation detector assembly further includes a signal processing circuit board in communication with the detector circuit board, the signal processing circuit board disposed on a side of the support frame opposite the detector circuit board. The support frame is thermally coupled to the detector circuit board and the signal processing circuit board to dissipate heat. The number of radiation detector modules is equal to the number of support surfaces. The radiation detector assembly further includes a collimator disposed on the radiation detector element, the collimator configured to collimate the rays emitted by the radiation source to the radiation detector element. The collimator includes a single collimator that integrally covers all of the radiation detector modules, the collimator including a surface parallel to the support surfaces. The collimator includes a plurality of collimator modules that each cover a respective radiation detector module, the plurality of collimator modules each including a surface parallel to a support surface of the respective radiation detector module. The radiation detector assembly includes: a support frame including a plurality of support surfaces disposed on a side of the support frame facing the radiation source, the plurality of support surfaces being tangent to a circular arc having the radiation source as a center; a plurality of radiation detector modules disposed on the plurality of support surfaces to receive the rays attenuated by the object under examination and to convert the rays into electrical signals.

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