Radiation detector module, radiation detector, and imaging apparatus

Abstract

The embodiment of the utility model provides a radiation detector module, a radiation detector and imaging equipment. The radiation detector module comprises a detector circuit board which is provided with a detector element for converting received rays emitted by a radiation source into electric signals, and the detector circuit board is provided with a first positioning hole; the collimator assembly is arranged on a transmission path of the rays and collimates the rays radiated to the detector element, and the collimator assembly is provided with a second positioning hole corresponding to the first positioning hole in position; and the frame supports the detector circuit board and the collimator assembly, the frame is provided with a positioning column, and the positioning column penetrates through the first positioning hole and the second positioning hole. According to the radiation detector module, the difficulty of alignment operation can be reduced, accumulation of alignment errors generated in multiple times of alignment operation is reduced, the alignment precision of all the components is improved, and then the detection precision of the radiation detector module is improved.

Description

Technical Field

[0001] The embodiments of the present application relate to the technical field of imaging devices, and in particular to a radiation detector module, a radiation detector, and an imaging device. Background Art

[0002] Imaging equipment is used to scan an examination object (such as a patient or a workpiece) in a non-invasive or non-destructive manner, thereby obtaining images of the internal structure of the anatomical tissue or part of interest of the examination object to assist in diagnosis.

[0003] An imaging device typically includes a circular scanning aperture for a subject to be scanned and examined to enter or exit, and a detector subsystem mounted along the entire circumference or a portion of the circular aperture. The detector subsystem includes multiple detector modules mounted on a gantry. For example, a computed tomography (CT) device is commonly used as a medical imaging device to scan a patient and obtain tomographic medical images of the patient's area of ​​interest to assist doctors in diagnosis.

[0004] The CT device includes a plurality of radiation detector modules that receive X-rays emitted from the X-ray tube and passing through the patient. The shape and number of each radiation detector module depend on clinical needs and the design of the CT system, and communication connections are established between each radiation detector module. Each radiation detector module of the CT device generally includes a pixelated scintillator and a photoelectric conversion device arranged in sequence along the direction of ray transmission. The scintillator is used to receive the X-rays passing through the patient and generate light, and the photoelectric conversion device (for example, a photodiode) converts the light generated by the scintillator into an electrical signal. Each radiation detector module also includes a collimator for collimating the X-rays passing through the patient to a specific direction to avoid or reduce interference between the pixels of the scintillator. Each radiation detector module also includes a signal processing circuit for processing the electrical signal generated by the photoelectric conversion device, and a frame for supporting the collimator, scintillator, photoelectric conversion device, circuit board and heat dissipation device.

[0005] The CT device also includes a computer subsystem that reconstructs the processed electrical signals to generate medical tomographic images for auxiliary diagnosis.

[0006] It should be noted that the above introduction to the technical background is only intended to provide a clear and complete description of the technical solution of the present application and to facilitate understanding by those skilled in the art. Utility Model Content

[0007] In a radiation detector module, components such as a circuit board on which detector elements are mounted, a collimator assembly, and a frame need to be precisely aligned to ensure the detection accuracy of the radiation detector module.

[0008] The inventors have discovered that in existing radiation detector modules, the components are aligned in pairs using alignment portions. For example, the collimator assembly and the circuit board are aligned using a first alignment portion, and the circuit board and the frame are aligned using a second alignment portion. As a result, multiple alignment operations are required when assembling the radiation detector module. Not only is the assembly process complicated, but the alignment errors generated in each alignment operation may accumulate, affecting the alignment accuracy between the components and thereby reducing the detection accuracy of the radiation detector module.

[0009] In response to at least one of the above technical issues or other similar issues, embodiments of the present application provide a radiation detector module, a radiation detector, and an imaging device. In the radiation detector module, positioning posts on a frame extend through the detector circuit board and the collimator assembly. Thus, the positioning posts enable alignment between the detector circuit board, the collimator assembly, and the frame, reducing the difficulty of alignment operations and the accumulation of alignment errors resulting from multiple alignment operations. This improves the alignment accuracy between components and, consequently, the detection accuracy of the radiation detector module.

[0010] According to one aspect of an embodiment of the present application, a radiation detector module is provided, comprising:

[0011] A detector circuit board, the detector circuit board being equipped with a detector element for converting received radiation emitted by a radiation source into an electrical signal, the detector circuit board having a first positioning hole;

[0012] a collimator assembly, the collimator assembly being disposed in a transmission path of the ray and collimating the ray radiated to the detector element, the collimator assembly having a second positioning hole corresponding to a position of the first positioning hole; and

[0013] A frame supports the detector circuit board and the collimator assembly. The frame is provided with an alignment pin, which passes through the first positioning hole and the second positioning hole.

[0014] In some embodiments, the number of the positioning posts is more than two, the number of the first positioning holes is more than two, and the number of the second positioning holes is more than two.

[0015] In some embodiments, the positioning post and the frame are integrally formed components; or

[0016] The positioning post and the frame are separate components, and the positioning post is installed on the frame.

[0017] In some embodiments, the end of the positioning post has a chamfered shape.

[0018] In some embodiments, the collimator assembly is a three-dimensional printed component.

[0019] In some embodiments, the radiation detector module further comprises:

[0020] A height compensation component is provided between the detector circuit board and the collimator assembly. The height compensation component has a third positioning hole, and the positioning column passes through the third positioning hole.

[0021] In some embodiments, the height of the height compensation component is equal to the height of the detector element.

[0022] According to another aspect of an embodiment of the present application, a radiation detector is provided, comprising a guide rail and two or more radiation detector modules as described in any one of the above embodiments supported on the guide rail.

[0023] In some embodiments, the guide rail has a fourth positioning hole, and the positioning column of the frame of the radiation detector module is installed in the fourth positioning hole.

[0024] According to another aspect of an embodiment of the present application, an imaging device is provided, which has the radiation detector described in the above embodiment and an image reconstruction device, and the image reconstruction device performs image reconstruction based on the electrical signal obtained by the radiation detector module of the radiation detector to generate a tomographic image of the inspection object.

[0025] With reference to the following description and drawings, specific implementations of the embodiments of the present application are disclosed in detail, indicating how the principles of the embodiments of the present application can be employed. It should be understood that the embodiments of the present application are not limited in scope. Within the spirit and scope of the appended claims, the embodiments of the present application include many variations, modifications, and equivalents. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] The included drawings are used to provide a further understanding of the embodiments of the present application, which constitute a part of the specification, are used to illustrate the implementation methods of the present application, and together with the text description, explain the principles of the present application. Obviously, the drawings described below are only some embodiments of the present application. For those skilled in the art, other implementation methods can be obtained based on these drawings without inventive work. In the drawings:

[0027] Figure 1 is a schematic diagram of a CT device according to an embodiment of the present application;

[0028] Figure 2 is a schematic diagram of a CT imaging system according to an embodiment of the present application;

[0029] Figure 3is a cross-sectional schematic diagram of a radiation detector module according to an embodiment of the present application;

[0030] Figure 4 is another cross-sectional schematic diagram of a radiation detector module according to an embodiment of the present application;

[0031] Figure 5 is a three-dimensional assembly diagram of a radiation detector module according to an embodiment of the present application;

[0032] Figure 6 is a three-dimensional schematic diagram of a radiation detector module according to an embodiment of the present application;

[0033] Figure 7 is a three-dimensional schematic diagram of a radiation detector according to an embodiment of the present application;

[0034] Figure 8 It is a schematic diagram of the composition of the imaging device of an embodiment of the present application. DETAILED DESCRIPTION

[0035] The foregoing and other features of the embodiments of the present application will become apparent through the following description with reference to the accompanying drawings. In the description and drawings, specific embodiments of the present application are disclosed in detail, which illustrate some embodiments in which the principles of the embodiments of the present application can be adopted. It should be understood that the present application is not limited to the described embodiments. On the contrary, the embodiments of the present application include all modifications, variations and equivalents that fall within the scope of the appended claims.

[0036] In the embodiments of the present application, the terms "first", "second", etc. are used to distinguish different elements from the name, but do not indicate the spatial arrangement or temporal order of these elements, and these elements should not be limited by these terms. The term "and / or" includes any one and all combinations of one or more of the associated listed terms. The terms "comprising", "including", "having", etc. refer to the presence of the stated features, elements, components or components, but do not exclude the presence or addition of one or more other features, elements, components or components.

[0037] In the embodiments of this application, the singular forms "a," "the," etc. include plural forms and should be broadly understood to mean "a" or "a type" rather than being limited to "one." Furthermore, the term "said" should be understood to include both singular and plural forms, unless the context clearly indicates otherwise. Furthermore, the term "according to" should be understood to mean "at least in part based on...", and the term "based on" should be understood to mean "at least in part based on...", unless the context clearly indicates otherwise.

[0038] Features described and / or illustrated for one embodiment may be used in the same or similar manner in one or more other embodiments, combined with features in other embodiments, or substituted for features in other embodiments. The term "include / comprise" as used herein refers to the presence of a feature, an integral part, a step, or a component, but does not exclude the presence or addition of one or more other features, integral parts, steps, or components.

[0039] In each embodiment of the present application, "above" and "below" include the number itself. For example, "above two" includes two and more than two, and "below two" includes two and less than two.

[0040] The imaging device described in this application is, for example, a medical imaging device, which is suitable for various medical imaging modalities, including but not limited to CT (computed tomography) imaging equipment, PET (positron emission tomography)-CT or any other suitable medical imaging equipment.

[0041] The system for obtaining medical imaging data may include the aforementioned medical imaging device, a separate computer device connected to the medical imaging device, or a computer device connected to an internet cloud, wherein the computer device is connected to the medical imaging device or a storage device storing medical images via the internet. The imaging method may be performed independently or in combination by the aforementioned medical imaging device, the computer device connected to the medical imaging device, or the computer device connected to the internet cloud. For example, the system for obtaining medical imaging data may be a CT imaging system, etc.

[0042] For example, the following describes the embodiments of the present application in conjunction with an X-ray computed tomography (CT) imaging device. Those skilled in the art will appreciate that the embodiments of the present application may also be applicable to other medical imaging devices.

[0043] Figure 1 FIG. 1 is a schematic diagram of a CT device according to an embodiment of the present application, schematically illustrating the CT device 100. Figure 1 As shown, CT apparatus 100 includes a scanning gantry 101 and a patient table 102. The scanning gantry 101 has an X-ray source 103 that projects an X-ray beam toward a detector assembly or collimator 104 on the opposite side of the scanning gantry 101. A subject 105 can lie flat on the patient table 102 and move into a scanning gantry opening 106 along with the patient table 102. Medical imaging data of the subject 105 can be obtained through scanning by the X-ray source 103.

[0044] Figure 2 FIG is a schematic diagram of a CT imaging system according to an embodiment of the present application, schematically showing a block diagram of a CT imaging system 200. Figure 2As shown, the detector assembly 104 includes a plurality of detector units 104 a and a data acquisition system (DAS) 104 b . The plurality of detector units 104 a sense the projected X-rays that pass through the inspection object 105 .

[0045] The DAS 104b converts the collected information into projection data for subsequent processing based on the sensing of the detector unit 104a. During a scan to acquire X-ray projection data, the scanning gantry 101 and the components mounted thereon rotate around the rotation center 101c.

[0046] The rotation of the gantry 101 and the operation of the X-ray source 103 are controlled by a control mechanism 203 of the CT imaging system 200. The control mechanism 203 includes an X-ray controller 203a, which provides power and timing signals to the X-ray source 103, and a gantry motor controller 203b, which controls the rotational speed and position of the gantry 101. An image reconstruction device 204 receives projection data from the DAS 104b and performs image reconstruction. The reconstructed image is transmitted as input to a computer 205, which stores the image in a mass storage device 206.

[0047] The computer 205 also receives commands and scan parameters from an operator via a console 207. The console 207 has some form of operator interface, such as a keyboard, mouse, voice activated controller, or any other suitable input device. An associated display 208 allows the operator to observe the reconstructed image and other data from the computer 205. The commands and parameters provided by the operator are used by the computer 205 to provide control signals and information to the DAS 104b, the x-ray controller 203a, and the scan gantry motor controller 203b. In addition, the computer 205 operates the patient table motor controller 209, which controls the patient table 102 to position the subject 105 and the scan gantry 101. In particular, the patient table 102 moves the subject 105, in whole or in part, through the scan gantry 101. Figure 1 The scanning gantry opening 106 is provided.

[0048] The above schematically illustrates the device and system for acquiring medical imaging data (or medical images or medical image data) according to an embodiment of the present application, but the present application is not limited thereto. The medical imaging device may be a CT device, a PET-CT device, or any other suitable imaging device. The storage device may be located within the medical imaging device, within a server external to the medical imaging device, within an independent medical imaging storage system (e.g., PACS, Picture Archiving and Communication System), and / or within a remote cloud storage system.

[0049] Furthermore, the medical imaging workstation can be located locally on the medical imaging device, meaning it can be located near the device. Both can be co-located in the examination room, the imaging department, or within the same hospital. The medical image cloud platform analysis system can be located remotely from the medical imaging device, for example, in a cloud-based environment that communicates with the device.

[0050] For example, after a medical institution completes an imaging scan using medical imaging equipment, the scanned data is stored in a storage device; a medical imaging workstation can directly read the scanned data and perform image processing through its processor. As another example, a medical image cloud platform analysis system can read medical images in a storage device via remote communication to provide "Software as a Service" (SaaS). SaaS can exist between hospitals, between hospitals and imaging centers, or between hospitals and third-party online diagnosis and treatment service providers.

[0051] The above schematically illustrates medical image scanning, and the following specifically describes the embodiments of the present application in conjunction with the accompanying drawings. In the following embodiments, the imaging device is described as a CT device, and the description is also applicable to other medical imaging devices.

[0052] In each embodiment of the present application: the Y direction is, for example, Figure 1 The tangent direction of the arc with the X-ray source 103 as the center is shown, and the arc can represent the extension trajectory of the guide rail 71 described later, for example, the Y direction, that is, Figure 1 The up and down directions of the scanning gantry 101 or the patient table 102 are shown; the X direction is, for example, Figure 1 Each point of the arc shown above points to the direction of the X-ray source 103, that is, the X direction Figure 1 The scanning gantry 101 or the patient table 102 shown is in the horizontal or left-right direction; the Z direction is, for example, Figure 1 The patient table 102 is shown in the direction it is moved into or out of relative to the scan gantry opening 106 .

[0053] An embodiment of the present application provides a radiation detector module.

[0054] Figure 3 FIG is a cross-sectional schematic diagram of a radiation detector module, showing a cross section of the radiation detector module observed along the Y direction. Figure 3 As shown, the radiation detector module 300 includes a detector circuit board 31 , a collimator assembly 32 and a frame 33 .

[0055] A detector element 34 is mounted on the detector circuit board 31. The detector element 34 receives radiation from a radiation source (eg, Figure 1 and Figure 2The X-ray source 103 shown in FIG. 1A ) emits rays and converts the rays into electrical signals.

[0056] In some examples, the detector element 34 includes a scintillator 341 and a photoelectric conversion element 342. The scintillator 341 and the photoelectric conversion element 342 can be arranged correspondingly in the X-direction or the radiation direction of the X-rays. For example, the scintillator 341 is closer to the radiation source than the photoelectric conversion element 342. The scintillator 341 receives the radiation emitted by the radiation source and generates light (e.g., visible light). The photoelectric conversion element 342 receives the light generated by the scintillator 341 and converts the received light into an electrical signal. The photoelectric conversion element 342 can be a photodiode, such as a backlit photodiode.

[0057] In other examples, the detector element 34 may include a photoelectric conversion element 342 instead of a scintillator 341. Thus, the photoelectric conversion element 342 can directly receive radiation emitted by the radiation source and generate an electrical signal. The photoelectric conversion element 342 may be a photon counting detector or a direct conversion detector.

[0058] In the present application, the electrical signal generated by the detector element 34 (e.g., the electrical signal generated by the photoelectric conversion element 342) can be transmitted via the detector circuit board 31 to a processing circuit chip (not shown), which processes the received electrical signal. For example, if the electrical signal received by the processing circuit chip is an analog signal, the processing circuit chip converts the analog signal into a digital signal, i.e., performs analog-to-digital conversion. The processing circuit chip and the detector element 34 can be mounted on the same side of the detector circuit board 31, or the processing circuit chip and the detector element 34 can be mounted on different sides of the detector circuit board 31.

[0059] The collimator assembly 32 is disposed in the transmission path of the radiation emitted by the radiation source and collimates the radiation emitted to the detector element 34. For example, the collimator assembly 32 is closer to the radiation source than the detector element 34. Thus, the radiation emitted by the radiation source is collimated by the collimator assembly 32 and then irradiated to the detector element 34. In some examples, the collimator assembly 32 is a three-dimensional (3D) printed component.

[0060] The frame 33 supports the detector circuit board 31 and the collimator assembly 32 .

[0061] like Figure 3As shown, the detector circuit board 31 has a first positioning hole 311, the collimator assembly 32 has a second positioning hole 321, and the frame 33 has an alignment pin 331. The first positioning hole 311, the second positioning hole 321 and the alignment pin 331 are positioned correspondingly.

[0062] The positioning post 331 passes through the first positioning hole 311 and the second positioning hole 321. Thus, the positioning post 331 can realize the alignment among the detector circuit board 31, the collimator assembly 32 and the frame 33, thereby reducing the difficulty of the alignment operation, and reducing the accumulation of alignment errors generated in multiple alignment operations, thereby improving the alignment accuracy between the components, and thus improving the detection accuracy of the radiation detector module 300.

[0063] In the present application, the positioning post 331 extends from the main body 330 of the frame 33 toward the direction where the detector circuit board 31 and the collimator assembly 32 are provided, so that the positioning post 331 can pass through the first positioning hole 311 and the second positioning hole 321 .

[0064] In some examples, such as Figure 3 As shown, the collimator assembly 32, the detector circuit board 31 and the frame 33 are sequentially arranged along the ray transmission path, that is, the collimator assembly 32 and the detector circuit board 31 are closer to the radiation source than the main body 330 of the frame 22, and the positioning post 331 extends from the main body 330 toward the radiation source. Figure 3 In the example, the main body 330 may be in a plate shape.

[0065] In other examples, the collimator assembly 32 , the detector circuit board 31 , and the frame 33 may be arranged in other orders.

[0066] Figure 4 is another cross-sectional diagram of the radiation detector module. Figure 4 In the example shown, the frame 33, the collimator assembly 32, and the detector circuit board 31 are sequentially arranged along the radiation transmission path, that is, the main body 330 of the frame 22 is closer to the radiation source than the collimator assembly 32 and the detector circuit board 31, and the positioning post 331 extends from the main body 330 in a direction away from the radiation source (that is, toward the collimator assembly 32 and the detector circuit board 31). Figure 4 In the example, the main body 330 may be a hollow frame structure. For example, the main body 330 is a rectangular frame structure, and the positions of the collimator assembly 32 and the detector element 34 correspond to the positions of the hollow area of ​​the main body 330.

[0067] Thus, the radiation emitted by the radiation source can pass through the hollow area of ​​the main body 330 and be emitted toward the collimator assembly 32 and the detector circuit board 31 .

[0068] Next, combine Figure 3 , further description of the radiation detector module 300 is given. Figure 3 The contents of the description also apply to Figure 4 The radiation detector module is shown in the example.

[0069] like Figure 3 As shown, in some embodiments, the radiation detector module 300 further includes a height compensation component 35. The height compensation component 35 is disposed between the detector circuit board 31 and the collimator assembly 32. The height compensation component 35 can be used to at least partially support the collimator assembly 32, thereby preventing excessive pressure from being generated between the collimator assembly 32 and the detector elements 34 mounted on the detector circuit board 31, thereby improving the reliability of the radiation detector module 300.

[0070] In some examples, the height of the height compensation component 35 (i.e., its dimension along the X-direction) is equal to the height of the detector element 34, thereby avoiding or reducing pressure exerted by the collimator assembly 32 on the detector element 34. Due to variations in machining accuracy, it is understood that the height of the height compensation component 35 being equal to the height of the detector element 34 includes the height of the height compensation component 35 being slightly or slightly greater than the height of the detector element 34. For example, if the detector element 34 includes a scintillator 341 and a photoelectric conversion element 342, the height of the height compensation component 35 is equal to the sum of the heights of the scintillator 341 and the photoelectric conversion element 342. For another example, if the detector element 34 includes the photoelectric conversion element 342 but not the scintillator 341, the height of the height compensation component 35 is equal to the height of the photoelectric conversion element 342.

[0071] like Figure 3 As shown, the height compensation component 35 has a third positioning hole 351, and the positioning column 331 passes through the third positioning hole 351. Therefore, the height compensation component 35 can be positioned with the frame 33, the collimator assembly 32 and the detector circuit board 31 through the cooperation between the positioning column 331 and the third positioning hole 351.

[0072] In the present application, the height compensation component 35 may be in the form of a sheet, for example, a gasket. Furthermore, the shape of the height compensation component 35 is not limited thereto, for example, the height compensation component 35 may be in the form of a cylinder, a hollow frame, or other shapes.

[0073] The height compensation component 35 can be made of a metal material or a non-metal material.

[0074] like Figure 3As shown, in some embodiments, the number of positioning posts 331 can be more than two, the number of first positioning holes 311 can be more than two, the number of second positioning holes 321 can be more than two, and the number of third positioning holes 351 can be more than two, and the number of positioning posts 331, first positioning holes 311, second positioning holes 321, and third positioning holes 351 corresponds to each other. Thus, positioning at more than two positions can further ensure the reliability of positioning.

[0075] In some embodiments of the present application, the positioning post 331 and the frame 33 are integrally formed components.

[0076] In other embodiments, the positioning post 331 and the frame 33 are separate components, and the positioning post 331 is mounted on the frame 33. In some examples, the positioning post 331 is detachably mounted on the frame 33, for example, the positioning post 331 is detachably mounted on the frame 33 using screws or other structures. In other examples, the positioning post 331 is fixedly mounted on the frame 33, for example, the positioning post 331 is welded to the frame 33.

[0077] like Figure 3 As shown, the end portion 331 a of the positioning post 331 has a chamfered shape, which can guide the positioning post 331 to be inserted into the first positioning hole 311 , the second positioning hole 321 or the third positioning hole 351 .

[0078] In the present application, when viewed along the extension direction of the positioning post 331, the cross-section of the end portion 331a of the positioning post 331 can be circular, elliptical, N-gonal (N is a natural number greater than or equal to 3), or other shapes formed by at least one of a curved segment and a straight line segment. The cross-section of at least one of the first positioning hole 311, the second positioning hole 321, and the third positioning hole 351 has a corresponding shape to the cross-section of the positioning post 331, thereby enabling the positioning post 331 to be accommodated in the first positioning hole 311, the second positioning hole 321, and the third positioning hole 351.

[0079] Figure 5 is a three-dimensional assembly diagram of the radiation detector module of the embodiment of the present application, and Figure 3 The radiation detector module 300 corresponds to the embodiment of the present invention. Figure 6 3 is a schematic perspective view of the radiation detector module according to an embodiment of the present application, showing a schematic perspective view of the radiation detector module 300 as viewed from the ray incident surface of the collimator assembly 32 .

[0080] like Figure 5 and Figure 6 As shown, the radiation detector module 300 includes a detector circuit board 31 , a collimator assembly 32 and a frame 33 .

[0081] The collimator assembly 32 is disposed on the surface of the radiation detector element 34 and is used to collimate radiation emitted by the radiation source toward the radiation detector element 34. In some examples, the radiation detector element 34 includes a scintillator 341 for receiving radiation and a photoelectric conversion element 342 for converting light generated by the scintillator 341 into an electrical signal. Radiation emitted by the radiation source (e.g., X-rays) is collimated by the collimator assembly 32 and then irradiated by the scintillator 341. The light generated by the scintillator 341 is converted by the photoelectric conversion element 342 into an electrical signal. The electrical signal generated by the photoelectric conversion element 342 is used to perform tomographic imaging of the object. Furthermore, as previously described, the radiation detector element 34 may not include the scintillator 341. Thus, radiation emitted by the radiation source (e.g., X-rays) is collimated by the collimator assembly 32 and then irradiated by the photoelectric conversion element 342, which then generates an electrical signal.

[0082] like Figure 5 As shown, the frame 33 may include a main body portion 330 in the middle and heat dissipation portions 332 on both sides of the main body portion 330 ( Figure 3 The main body 330 may be in the form of a plate. A processing circuit chip 312 ( Figure 3 and Figure 4 In the case where the detector circuit board 31 is not mounted on the detector circuit board 31 (not shown), the main body 330 can contact the processing circuit chip 312; in addition, in the case where the processing circuit chip 312 is not mounted on the detector circuit board 31, the main body 330 can contact the detector circuit board 31. The heat dissipation portion 332 can have a fin structure to facilitate heat dissipation. The frame 33 can be made of a material with high thermal conductivity, such as a metal material (for example, aluminum or stainless steel). Thus, the frame 33 can not only support the detector circuit board 31 and the collimator assembly 32, but also dissipate heat for the detector circuit board 31 and the components mounted thereon, thereby improving reliability.

[0083] also, Figure 5 and Figure 6 Also shown is the data collection circuit board 36 ( Figure 3 not shown) and the housing member 37 ( Figure 3 (Not shown) The data collection circuit board 36 can receive electrical signals generated by the detector elements 34 or the processing circuit chip 312 on the detector circuit board 31 via the cable 313. A housing component 37 is mounted to the frame 33 and covers the data collection circuit board 36. The housing component 37 is made of a metal material to shield electromagnetic radiation and thereby improve the performance of the data collection circuit board 36, such as the signal-to-noise ratio. Figure 5 and Figure 6The data collection circuit board 36 is also shown with a heat sink 361 mounted thereon for thermal management. The housing component 37 is provided with an opening 371 corresponding to the shape of the heat sink 361, through which the heat sink 361 extends. In some embodiments, the housing component 37 is also thermally coupled to the data collection circuit board 36 to increase the heat dissipation area of ​​the data collection circuit board 36. The housing component 37 can further be thermally coupled to the heat sink 361. Thus, the housing component 37 is thermally coupled to the frame 33, the data collection circuit board 36, and its heat sink 361, thereby improving the thermal management of the radiation detector module 300.

[0084] An embodiment of the present application also provides a radiation detector.

[0085] Figure 7 FIG is a three-dimensional schematic diagram of a radiation detector according to an embodiment of the present application. Figure 7 As shown, the radiation detector 700 includes: Figure 3 The radiation detector module 300 and the guide rail 71 are shown. The radiation detector module 300 is supported on the guide rail 71. The radiation detector modules 300 are arranged along the direction in which the guide rail 71 extends. The number of the radiation detector modules 300 can be more than 2, for example, 3 to 15.

[0086] The positional relationship between each radiation detector module 300 and the guide rail 71 in the radiation detector 700 can be as follows: Figure 3 As shown, the guide rail 71 has a fourth positioning hole 711 , and the positioning column 331 of the frame 33 of the radiation detector module 300 is installed in the fourth positioning hole 711 .

[0087] In the radiation detector 700 of the present application, the positioning posts 331 of the frame 33 of the radiation detector module 300 can be used to position the detector circuit board 31, collimator assembly 32, and frame 33 within the radiation detector module 300. Furthermore, the positioning posts 331 are used to position the radiation detector module 300 and the guide rail 71. This reduces the difficulty of aligning the components within the radiation detector module 300 and the alignment between the radiation detector module 300 and the guide rail 71, improves alignment accuracy, and thereby improves the detection accuracy of the radiation detector.

[0088] An embodiment of the present application further provides an imaging device, which is, for example, a medical imaging device.

[0089] Figure 8 This is a schematic diagram of the composition of an imaging device. Figure 8 As shown, the imaging device 800 includes Figure 7The radiation detector 700 and the image reconstruction device 801 are shown. The image reconstruction device 801 is based on the radiation detector module 300 (such as Figure 7 The electrical signals generated by the detector elements in FIG. 1 are used to perform tomographic imaging of the object.

[0090] In some examples, the image reconstruction device 801 may utilize, for example, Figure 5 The image is reconstructed based on the data collected by the data collection circuit board 36. For detailed description of the image reconstruction device 801, reference can be made to the relevant art.

[0091] The imaging device 800 of the present application is, for example, a CT (computed tomography) imaging device, a PET-CT or any other suitable imaging device.

[0092] The above embodiments are merely exemplary of the present invention, but the present invention is not limited thereto. Appropriate modifications may be made based on the above embodiments. For example, the above embodiments may be used alone, or one or more of the above embodiments may be combined.

[0093] The present application has been described above with reference to specific embodiments. However, those skilled in the art should understand that these descriptions are merely illustrative and are not intended to limit the scope of protection of the present application. Those skilled in the art may make various modifications and variations to the present application based on the principles of the present application, and such modifications and variations are also within the scope of the present application.

Claims

1. A radiation detector module, characterized in that: The radiation detector module comprises: A detector circuit board, the detector circuit board being equipped with a detector element for converting received radiation emitted by a radiation source into an electrical signal, the detector circuit board having a first positioning hole; a collimator assembly, the collimator assembly being disposed in a transmission path of the ray and collimating the ray radiated to the detector element, the collimator assembly having a second positioning hole corresponding to a position of the first positioning hole; and A frame supports the detector circuit board and the collimator assembly, and the frame is provided with a positioning column, which passes through the first positioning hole and the second positioning hole.

2. The radiation detector module according to claim 1, wherein The number of the positioning columns is more than two, The number of the first positioning holes is two or more, The number of the second positioning holes is two or more.

3. The radiation detector module according to claim 1, wherein: The positioning column and the frame are integrally formed components; or The positioning post and the frame are separate components, and the positioning post is installed on the frame.

4. The radiation detector module according to claim 1, wherein: The end of the positioning column has a chamfered shape.

5. The radiation detector module according to claim 1, wherein: The collimator assembly is a three-dimensionally printed component.

6. The radiation detector module according to claim 1, wherein: The radiation detector module further includes: A height compensation component is provided between the detector circuit board and the collimator assembly. The height compensation component has a third positioning hole, and the positioning column passes through the third positioning hole.

7. The radiation detector module according to claim 6, wherein: The height of the height compensation component is equal to the height of the detector element.

8. A radiation detector, characterized in that: The radiation detector includes a guide rail and two or more radiation detector modules according to any one of claims 1 to 7 supported on the guide rail.

9. The radiation detector according to claim 8, characterized in that The guide rail has a fourth positioning hole, and the positioning column of the frame of the radiation detector module is installed in the fourth positioning hole.

10. An imaging device, characterized in that: The imaging device comprises a radiation detector according to any one of claims 8 to 9 and an image reconstruction device, wherein the image reconstruction device performs image reconstruction based on electrical signals acquired by a radiation detector module of the radiation detector to generate a tomographic image of an inspection object.

Images