Radiation detector module, radiation detector and imaging device

Abstract

The embodiment of the utility model provides a radiation detector module, a radiation detector and imaging equipment. In the radiation detector module, the arrangement number of the radiation detector elements in the Z direction of the circuit substrate is 4N rows or 4N + 1 rows, and N is an integer greater than or equal to 1, so that the radiation detector elements can be reduced in a central symmetry manner relative to the circuit substrate in the Z direction under the scene that part of the radiation detector elements need to be reduced, for example, the radiation detector elements can be reduced in the Z direction. According to the invention, 2N rows of radiation detector elements are reduced, so that the central positions of the remaining radiation detector elements in the Z direction are kept unchanged, the positions of the remaining radiation detector elements and the focus position of a radiation source (such as an X-ray source) do not need to be adjusted, the rack structure does not need to be changed, and additional mechanical vibration is not brought. And imaging quality is ensured.

Description

TECHNICAL FIELD

[0001] Embodiments of the present application relate to the technical field of imaging equipment, and in particular, to a radiation detector module, a radiation detector, and an imaging equipment. BACKGROUND

[0002] Imaging equipment is used to scan a subject (e.g., a patient, a workpiece) in a non-invasive or non-destructive manner, so as to acquire an internal structure image of an anatomical tissue or a part of interest of the subject, to assist in diagnosis.

[0003] Imaging equipment usually includes a circular scanning hole (e.g., a scanning gantry opening) for a scanning subject to move in or out, and a detector subsystem mounted along an entire circumference or a partial arc of the circular hole, which includes a plurality of detector modules mounted on a gantry. For example, a computed tomography (CT) device is usually used as a kind of medical imaging equipment to scan a patient to acquire a tomographic image of a part of interest of the patient to assist a doctor in diagnosis.

[0004] A CT device includes a plurality of radiation detector modules that receive X-rays emitted from an X-ray tube and passing through a patient, the form and number of each radiation detector module depend on clinical requirements and the design of the CT system, and a communication connection is established between each radiation detector module. Each radiation detector module of the CT device usually includes a radiation detector element, which may, for example, include a pixelated scintillator and a photoelectric conversion device arranged in sequence along a ray transmission direction, the scintillator is used to receive X-rays passing through the patient and generate light, and the photoelectric conversion device (e.g., a photodiode) converts the light generated by the scintillator into an electrical signal. Each 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 each pixel of the scintillator. Each 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, the scintillator, the photoelectric conversion device, the circuit board, and the heat dissipation device.

[0005] The CT device also includes a computer subsystem for reconstructing based on the processed electrical signal to generate a medical tomographic image for assisting in diagnosis.

[0006] It should be noted that the above introduction to the technical background is only to facilitate a clear and complete description of the technical solutions of the present application, and to facilitate the understanding of those skilled in the art. CONTENT OF THE INVENTION

[0007] In a CT device, the number of images per exposure of a radiation detector module depends on the number of radiation detector elements in the module arranged in the Z direction (i.e. the direction in which the examination object enters or exits the CT device through a scan hole) and the number of ray transmission channels each radiation detector element has in the Z direction. Generally, the more radiation detector elements arranged in the Z direction, the shorter the examination time, which is more suitable for examinations of body parts that are prone to motion. In some use scenarios (e.g. for examinations of relatively static body parts), the number of radiation detector elements arranged in the Z direction can be less, thereby saving costs.

[0008] The inventors have found that in an imaging device such as a CT device, if the number of radiation detector elements in the Z direction in a radiation detector module is reduced (e.g. by half), the center position of the remaining radiation detector elements in the Z direction can shift, so that the position of the focal spot of the X-ray source in the Z direction needs to be adjusted, or the position of the remaining radiation detector elements in the Z direction needs to be adjusted, so that the focal spot of the X-ray source is located at the center position of the remaining radiation detector elements in the Z direction. Such adjustment of the position of the focal spot of the X-ray source can affect the design of the gantry structure of the imaging device or mechanical vibrations, and thus affect the imaging quality.

[0009] To address at least one of the above technical problems or other similar problems, embodiments of the present application provide a radiation detector module, a radiation detector and an imaging device. In the radiation detector module, the number of radiation detector elements arranged in the Z direction of the circuit substrate is 4N rows or 4N+1 rows, N being an integer greater than or equal to 1. Thus, in scenarios where some radiation detector elements need to be reduced, the radiation detector elements can be reduced in a manner symmetrical to the center of the circuit substrate in the Z direction, e.g. 2N rows of radiation detector elements are reduced. In this way, the center position of the remaining radiation detector elements in the Z direction remains unchanged, so that the positions of the remaining radiation detector elements do not need to be adjusted, and the position of the focal spot of the radiation source (e.g. the X-ray source) does not need to be adjusted, and thus the gantry structure does not need to be changed and no additional mechanical vibrations are caused, thereby ensuring the imaging quality.

[0010] According to an aspect of embodiments of the present application, a radiation detector module is provided for detecting a ray signal passing through an examination object in an imaging device, the examination object entering or exiting the imaging device in a first direction, the radiation detector module comprising:

[0011] a radiation detector element receiving a ray emitted by a radiation source and converting the ray into an electrical signal;

[0012] a circuit substrate having a first side on which a plurality of the radiation detector elements are mounted, the plurality of the radiation detector elements being arranged in 4N rows or 4N+1 rows in the first direction of the circuit substrate, N being an integer greater than or equal to 1; and

[0013] a processing circuit chip disposed on a second side of the circuit substrate and in communication with the radiation detector elements.

[0014] Thus, the radiation detector can support image imaging of a specific row number, and directly remove 2N rows of radiation detector elements and related components arranged in the center of the Z direction on the circuit substrate, thereby supporting image imaging of about half the row number while keeping the center position of the radiation detector in the Z direction unchanged, so that the structure of the detector, gantry and other devices or equipment does not need to be changed, thereby reducing manufacturing costs.

[0015] In some embodiments, in the first direction, the plurality of radiation detector elements are symmetrically arranged relative to the center position of the circuit substrate in the first direction.

[0016] In some embodiments, each of the radiation detector elements has 16 rows of ray transmission channels distributed along the first direction.

[0017] In some embodiments, in the second direction of the circuit substrate, the plurality of radiation detector elements are arranged in one column or more than two columns.

[0018] In some embodiments, in the area of the circuit substrate covered by each of the radiation detector elements, one or more processing circuit chips are disposed.

[0019] In some embodiments, the radiation detector elements are electrically connected to the processing circuit chips through conductive paths penetrating the circuit substrate.

[0020] In some embodiments, the radiation detector elements include a scintillator that converts received rays into light and a photoelectric conversion element that converts the light generated by the scintillator into an electrical signal, the photoelectric conversion element including a backlit photodiode.

[0021] In some embodiments, the radiation detector module has a flat plate configuration.

[0022] In some embodiments, the radiation detector module further includes:

[0023] a data collection circuit board electrically connected to the circuit substrate by a wire and receiving data processed by the processing circuit chip.

[0024] In some embodiments, the radiation detector module further includes:

[0025] a collimator assembly arranged at a surface of the radiation detector element, the collimator assembly collimating the rays emitted by the radiation source towards the radiation detector element.

[0026] According to yet another aspect of the embodiments of the present application, a radiation detector is provided, the radiation detector comprising:

[0027] a guide rail and two or more radiation detector modules according to any one of the preceding embodiments supported by the guide rail.

[0028] According to still another aspect of the embodiments of the present application, an imaging apparatus is provided, the imaging apparatus comprising a scanning space for accommodating an examination object, the examination object entering or exiting the scanning space in a first direction, the imaging apparatus having a radiation detector according to the embodiments described above and an image reconstruction device for performing image reconstruction to generate a tomographic image of the examination object based on electrical signals generated by the radiation detector elements in the radiation detector modules of the radiation detector.

[0029] Specific embodiments of the present application are disclosed in detail in the following description and claims. Specific embodiments of the present application may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the application to those skilled in the art. In the drawings, like reference numerals refer to like elements in the several embodiments of the present application. BRIEF DESCRIPTION OF DRAWINGS

[0030] The accompanying drawings are included to provide a further understanding of the present application and are incorporated in and constitute a part of this specification, illustrate embodiments of the present application and together with the description serve to explain the principles of the present application. In the drawings:

[0031] Figure 1 is a schematic view of a CT apparatus according to an embodiment of the present application;

[0032] Figure 2 is a schematic view of a CT imaging system according to an embodiment of the present application;

[0033] Figure 3 is a schematic view of a cross section of a radiation detector module as a comparison;

[0034] Figure 4 is a schematic view of a radiation detector module as a comparison from above;

[0035] Figure 5 is a schematic view of a radiation detector module according to an embodiment of the present application;Figure 3 a schematic view of a cross section of a radiation detector module with some of the radiation detector elements of the radiation detector module of

[0036] Figure 6 is a top view of the radiation detector module of Figure 5

[0037] Figure 7 is another schematic view of a cross section of a radiation detector module with some of the radiation detector elements of the radiation detector module of Figure 3

[0038] Figure 8 is a top view of the radiation detector module of Figure 7

[0039] Figure 9 is a schematic view of a cross section of a radiation detector module according to an embodiment of the present application;

[0040] Figure 10 is a top view of a radiation detector module according to an embodiment of the present application;

[0041] Figure 11 is a schematic view of a radiation detector module with some of the radiation detector elements of the radiation detector module of Figure 9

[0042] Figure 12 is a schematic view of a radiation detector module with some of the radiation detector elements of the radiation detector module of Figure 10

[0043] Figure 13 is another top view of a radiation detector module according to an embodiment of the present application;

[0044] Figure 14 is a schematic view of a radiation detector module with some of the radiation detector elements of the radiation detector module of Figure 13

[0045] Figure 15 is another schematic view of a radiation detector module with some of the radiation detector elements of the radiation detector module of Figure 13

[0046] Figure 16 is a perspective view of a radiation detector according to an embodiment of the present application;

[0047] Figure 17 is a schematic view of a component of an imaging device;

[0048] Figure 18 is a method of manufacturing a radiation detector according to an embodiment of the present application. DETAILED DESCRIPTION

[0049] ​​​​​​​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 the present embodiments taken in conjunction with the accompanying drawings. In the drawings, specific embodiments of the present application are disclosed herein and are indicative of the principles of the present application in which the principles of the present application can be employed. It is further understood that the present application is not limited to the described embodiments but is applicable to all modifications, variations and equivalents that fall within the scope of the appended claims.

[0050] 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 are meant to be interpreted inclusively rather than exclusively, indicating the presence of the stated features, elements, integers, or components, but not excluding the presence or addition of one or more other features, elements, integers, or components.

[0051] 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 "any one or more" of the enumerated features 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.

[0052] 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 features in other implementations, or in the absence of features in other implementations. The term "comprise / comprising" is used herein to mean the presence of stated features, integers, steps, or components, but not to the exclusion of one or more other features, integers, steps, or components that are also present or that can be added.

[0053] In the present embodiments, "above" and "below" include the number itself. For example, two or more includes two and more than two, and two or less includes two and less than two.

[0054] The medical imaging device described in the present application can be applied to 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.

[0055] 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 an 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.

[0056] 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.

[0057] In the embodiments of the present application: the X direction is, for example, a direction in which the X-ray source 103 is located, that is, a direction in which the X-ray source 103 is directed; Figure 1 Each point of the aforementioned arc line shown points to the direction of the X-ray source 103, that is, the X direction is a direction in which the X-ray source 103 is located, that is, a direction in which the X-ray source 103 is directed; Figure 1 The scanning gantry 101 or the patient table 102 shown is a transverse direction or a left-right direction; the Y direction is, for example, a tangential direction of the arc line shown with the X-ray source 103 as the center, which can represent an extension trajectory of the guide rail 1201 described below, that is, the Y direction is a direction in which the scanning gantry 101 or the patient table 102 moves along the arc line shown with the X-ray source 103 as the center; Figure 1 The scanning gantry 101 or the patient table 102 shown is a transverse direction or a left-right direction; the Y direction is, for example, a tangential direction of the arc line shown with the X-ray source 103 as the center, which can represent an extension trajectory of the guide rail 1201 described below, that is, the Y direction is a direction in which the scanning gantry 101 or the patient table 102 moves along the arc line shown with the X-ray source 103 as the center; Figure 1 The scanning gantry 101 or the patient table 102 shown is a transverse direction or a left-right direction; the Y direction is, for example, a tangential direction of the arc line shown with the X-ray source 103 as the center, which can represent an extension trajectory of the guide rail 1201 described below, that is, the Y direction is a direction in which the scanning gantry 101 or the patient table 102 moves along the arc line shown with the X-ray source 103 as the center; Figure 1 The scanning gantry 101 or the patient table 102 shown is a transverse direction or a left-right direction; the Y direction is, for example, a tangential direction of the arc line shown with the X-ray source 103 as the center, which can represent an extension trajectory of the guide rail 1201 described below, that is, the Y direction is a direction in which the scanning gantry 101 or the patient table 102 moves along the arc line shown with the X-ray source 103 as the center; Figure 1 The scanning gantry 101 or the patient table 102 shown is a transverse direction or a left-right direction; the Y direction is, for example, a tangential direction of the arc line shown with the X-ray source 103 as the center, which can represent an extension trajectory of the guide rail 1201 described below, that is, the Y direction is a direction in which the scanning gantry 101 or the patient table 102 moves along the arc line shown with the X-ray source 103 as the center;

[0058] Figure 1 is a schematic diagram of a CT device of 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 scanning gantry 101 and a patient table 102; the scanning 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 scanning gantry 101. An examination object 105 can lie on the patient table 102 and move into a scanning gantry opening 106 along with the patient table 102; through scanning of the X-ray source 103, medical image data of the examination object 105 can be obtained.

[0059] Figure 2 is a schematic diagram of a CT imaging system of an embodiment of the present application, which schematically shows a block diagram of the CT imaging system 200. As shown in Figure 2As shown, the detector assembly 104 includes a plurality of detector elements 104a and a data acquisition system (DAS) 104b. The plurality of detector elements 104a sense the projected X-rays that pass through the examination object 105.

[0060] The DAS 104b converts the collected information into projection data for subsequent processing according to the sensing of the detector elements 104a. During a scan in which X-ray projection data is acquired, the gantry 101 and the components mounted thereto rotate about the rotation center 101c.

[0061] 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 that provides power and timing signals to the X-ray source 103, and a gantry motor controller 203b that controls the rotational speed and position of the gantry 101. An image reconstruction device 204 receives the projection data from the DAS 104b and performs image reconstruction. The reconstructed images are transferred as input to a computer 205, which stores the images in a mass storage device 206.

[0062] 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 images 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 gantry motor controller 203b. In addition, the computer 205 operates a patient table motor controller 209 to control the patient table 102 to position the examination object 105 and the gantry 101. In particular, the patient table 102 moves the examination object 105 entirely or partially through the gantry opening 106. Figure 1

[0063] The above illustrates schematically the apparatus and system of the present embodiments for acquiring medical imaging data (or also referred to as medical images or medical image data), but the present embodiments are not limited thereto. The medical imaging apparatus can be a CT apparatus, a PET-CT or any other suitable imaging apparatus. The storage apparatus can be located within the medical imaging apparatus, within a server external to the medical imaging apparatus, within a standalone medical imaging storage system (e.g. a PACS, Picture Archiving and Communication System) and / or within a remote cloud storage system.

[0064] ​In addition, the medical imaging workstation can be set locally to the medical imaging device, i.e. the medical imaging workstation is set close to the medical imaging device, and both can be located in a scanning room, an imaging department or in the same hospital. The medical image cloud platform analysis system can be located remotely from the medical imaging device, for example, set at a cloud end in communication with the medical imaging device.

[0065] 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 a 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 medical service provider.

[0066] The above illustrates the medical image scanning schematically, and the embodiments of the present application are described in detail below in combination with the drawings. In each of the embodiments described below, the imaging device is taken as an example of a CT device, and the description is also applicable to other medical imaging devices.

[0067] Figure 3 is a schematic view of a cross section of a contrast radiation detector module, which is observed along the Y direction. Figure 4 is a schematic view of a top view of the contrast radiation detector module, which is observed along the X direction. As shown in Figure 3 and Figure 4 As shown in the contrast, the radiation detector module 300 is used to detect the ray signal passing through the examination object 105 (as shown in Figure 1 ) in the imaging device in the Z direction entering or exiting the imaging device.

[0068] The radiation detector module 300 includes a radiation detector element 301, a processing circuit chip 302 and a circuit substrate 303. The radiation detector element 301 receives the radiation from a radiation source (for example, Figure 1The circuit substrate 303 is configured to detect radiation emitted by an X-ray source 103 (shown) and convert the radiation into electrical signals. Multiple radiation detector elements 301 are mounted on a first side of the circuit substrate 303 (e.g., the side facing the radiation source in the X direction). In the Z direction of the circuit substrate 303, the multiple radiation detector elements 301 are arranged in two rows. The center of the radiation detector module 300 in the Z direction (e.g., the geometric center of the multiple radiation detector elements 301) is located at the position of the dashed line 3071, i.e., the focal point of the radiation projected by the radiation source toward the radiation detector module 300. A processing circuit chip 302 is disposed on a second side of the circuit substrate 303 (e.g., the side facing away from the radiation source in the X direction) and communicates with the radiation detector elements 301.

[0069] In some examples, the radiation detector element 301 includes a scintillator 3011 and a photoelectric conversion element 3012 .

[0070] The radiation detector module 300 also includes a data collection circuit board 306 , a flexible circuit 304 , and a connecting circuit 305 .

[0071] Figure 3 and Figure 4 The radiation detector module 300 can, for example, capture images of 64 rows of channels. If it needs to be modified to capture images of 32 rows of channels, the number of radiation detector elements 301 distributed in the Z direction can be reduced by half, for example, reducing the two rows of radiation detector elements 301 arranged in the Z direction to one row. In order to keep the focus of the radiation source at the center position of the remaining radiation detector elements 301 in the Z direction, the position of the focus of the X-ray source in the Z direction can be adjusted, or the positions of the remaining radiation detector elements in the Z direction can be adjusted, such as Figures 5-8 shown.

[0072] Figure 5 It will Figure 3 FIG1 is a schematic diagram of a cross section of a radiation detector module after some radiation detector elements are removed, the cross section being observed along the Y direction. Figure 6 yes Figure 5 Top view, viewed along the X direction Figure 5 Get. Figure 5 and Figure 6 As shown, removing half of the radiation detector elements 301 of the radiation detector module along the Z direction can reduce the number of rows of collected images, but the center of the radiation detector along the Z direction is offset from the dotted line 3071 to the dotted line 3072. The offset distance is, for example, half of the length of the radiation detector element 301 along the Z direction. Figure 5 and Figure 6In this case, the focusing position of the X-ray source 103 on the Z axis also needs to be readjusted to the dotted line 3072, and this adjustment of the focusing position of the X-ray source 103 can affect the rack structure or mechanical vibration of the imaging device, thereby affecting the imaging quality.

[0073] Figure 7 is another schematic view of a cross section of the radiation detector module after part of the radiation detector elements of Figure 3 is obtained by observing the radiation detector module along the Y direction. Figure 8 is a top view of the radiation detector module of Figure 7 is obtained by observing the radiation detector module along the X direction. Figure 7 As shown in Figure 7 and Figure 8 , on the basis of removing half of the radiation detector elements 301 of the radiation detector module along the Z direction, the positions of the remaining radiation detector elements 301 on the surface of the circuit board 303 are further adjusted, so that the center positions of the remaining radiation detector elements 301 along the Z direction are kept at the dotted line 3071. In this way, although the focusing position of the X-ray source 103 on the Z axis does not need to be adjusted, the positions of the remaining radiation detector elements 301 on the surface of the circuit board 303 need to be adjusted, the radiation detector elements 301 need to be rearranged or wired, and even the circuit board 303 or the entire radiation detector module needs to be replaced, thereby increasing the cost.

[0074] To solve the above problem or at least similar problems, an embodiment of the present application provides a radiation detector module.

[0075] Figure 9 is a schematic view of a cross section of the radiation detector module of the embodiment of the present application, which is obtained by observing the radiation detector module along the Y direction. Figure 10 is a top view of the radiation detector module of the embodiment of the present application, which can be obtained by observing the radiation detector module along the X direction. Figure 9 .

[0076] As shown in Figure 9 and Figure 10 , the radiation detector module 900 of the embodiment of the present application is used to detect a ray signal passing through an examination object 105 (as shown in Figure 1 ) in an imaging device, and the examination object 105 enters or exits the imaging device in the Z direction.

[0077] The radiation detector module 900 includes a radiation detector element 901, a processing circuit chip 902, and a circuit board 903.

[0078] The radiation detector element 901 receives a ray (for example, an X-ray) emitted by a radiation source (for example, the X-ray source 103 shown in Figure 1 ) and converts the ray into an electrical signal.

[0079] In some examples, the radiation detector element 901 includes a scintillator 9011 and a photoelectric conversion element 9012, which can be arranged in the radiation direction of the X-rays, for example, the scintillator 9011 is closer to the radiation source than the photoelectric conversion element 9012. The scintillator 9011 receives the rays emitted by the X-ray source and generates light, for example, visible light. The photoelectric conversion element 9012 receives the light generated by the scintillator 9011 and converts the received light into an electrical signal. The photoelectric conversion element 9012 can be a photodiode, for example, a backlit photodiode.

[0080] In other examples, the radiation detector element 901 can not have a scintillator 9011, whereby the radiation detector element 901 can directly receive the rays emitted by the radiation source and generate an electrical signal. The radiation detector element 901 can be a photon counting detector or a direct conversion detector, etc.

[0081] The first side of the circuit substrate 903 (for example, the side facing the radiation source in the X direction) is mounted with a plurality of radiation detector elements 901. In the Z direction of the circuit substrate 903, the plurality of radiation detector elements 901 are arranged in 4N rows, N being an integer greater than or equal to 1. For example, in the example shown in FIG. 10, N = 1, i.e., there are 4 radiation detector elements 901 arranged in the Z direction of the circuit substrate 903. Figure 10 In the example shown in FIG. 10, N = 1, i.e., there are 4 radiation detector elements 901 arranged in the Z direction of the circuit substrate 903.

[0082] The processing circuit chip 902 is arranged on the second side of the circuit substrate 903 (for example, the side away from the radiation source in the X direction) and communicates with the radiation detector elements 901.

[0083] Figure 13 is another top view of the radiation detector module of the embodiments of the present application. Figure 13 shows another arrangement of the plurality of radiation detector elements 901 on the surface of the circuit substrate 903. As shown in FIG. 11, in the Z direction of the circuit substrate 903, the plurality of radiation detector elements 901 are arranged in 4N+1 rows, N being an integer greater than or equal to 1. For example, in the example shown in FIG. 11, N = 1, i.e., there are 5 radiation detector elements 901 arranged in the Z direction of the circuit substrate 903. Figure 13 In the example shown in FIG. 11, N = 1, i.e., there are 5 radiation detector elements 901 arranged in the Z direction of the circuit substrate 903. Figure 13

[0084] According to Figure 9 , Figure 10 and Figure 13 ​In the example, in the Z direction of the circuit substrate 903, the plurality of radiation detector elements 901 are arranged in 4N rows or 4N+1 rows. Thus, when some radiation detector elements 901 in the Z direction are reduced, the center positions of the remaining radiation detector elements in the Z direction can remain unchanged. Therefore, there is no need to adjust the positions of the remaining radiation detector elements 901, thereby reducing costs. In addition, there is no need to adjust the focal position of the radiation source (for example, an X-ray source), thereby eliminating the need to change the frame structure of the imaging device and introducing no additional mechanical vibration, thereby ensuring the imaging quality of the imaging device.

[0085] like Figure 9 、 Figure 10 and Figure 13 In the Z direction, the plurality of radiation detector elements 901 are arranged symmetrically relative to the center position 9071 of the circuit substrate 903 in the Z direction. Figure 10 In the example shown, the circuit substrate 903 has two radiation detector elements 901 on either side of the center position 9071 in the Z direction. Figure 13 In the example shown, the center position 9071 of the circuit substrate 903 in the Z direction coincides with the center position of the radiation detector element 901 arranged in the middle in the Z direction, and there are two radiation detector elements 901 on each side of the radiation detector element 901 arranged in the middle.

[0086] In addition, in the Z direction, the focal position of the radiation source can be located at the center position 9071 of the circuit substrate 903 in the Z direction.

[0087] In this application, Figure 9 or Figure 13 In the radiation detector module 900 shown, each radiation detector element 901 has M rows of ray transmission channels distributed along the Z direction, where M can be a natural number equal to or greater than 1. In one example, M=16.

[0088] In some examples, such as Figure 9 As shown, four rows of radiation detector elements 901 are arranged along the Z direction, and the radiation detector module 900 has 16*4=64 rows of channels along the Z direction.

[0089] In some examples, such as Figure 13 As shown, 5 rows of radiation detector elements 901 are arranged along the Z direction, and the radiation detector module 900 has 16*5=80 rows of channels along the Z direction.

[0090] Figure 9 and Figure 10The radiation detector module 900 shown can collect 64-row channel images, and if it is required to adjust to collect 32-row channel images, several rows (for example, two rows) of the radiation detector elements 901 symmetrically arranged relative to the central position 9071 can be removed.

[0091] Figure 11 and Figure 12 are schematic diagrams of removing part of the radiation detector elements from Figure 9 and Figure 10 . As shown in Figure 11 and Figure 12 , the outermost two rows of the radiation detector elements 901 and the corresponding processing circuit chips 902 in Figure 9 and Figure 10 may be removed, thereby the scanning width of the remaining radiation detector elements 901 of the radiation detector module 900 in the Z direction is reduced by half, the number of channels for collecting images is reduced by half, and the central position of the remaining radiation detector elements 901 in the Z direction remains unchanged, so that neither the position of the remaining radiation detector elements 901 nor the focal point position of the radiation source (for example, an X-ray source) needs to be adjusted, thereby saving costs and ensuring the imaging quality of the imaging device.

[0092] Figure 13 The radiation detector module 900 shown can collect 80-row channel images, and if it is required to adjust to collect 48-row channel images, several rows (for example, two rows) of the radiation detector elements 901 symmetrically arranged relative to the central position 9071 can be removed.

[0093] Figure 14 is a schematic diagram of removing part of the radiation detector elements from Figure 13 . As shown in Figure 14 , the outermost two rows of the radiation detector elements 901 and the corresponding processing circuit chips 902 in Figure 13 may be removed, thereby the scanning width of the remaining radiation detector elements 901 of the radiation detector module 900 in the Z direction is reduced by nearly half, for example, the scanning width of two radiation detector elements 901 in the Z direction is reduced, the number of channels for collecting images is reduced by nearly half, for example, the number of channels for collecting images of two radiation detector elements 901 in the Z direction is reduced, and the central position of the remaining radiation detector elements 901 in the Z direction remains unchanged, so that neither the position of the remaining radiation detector elements 901 nor the focal point position of the radiation source (for example, an X-ray source) needs to be adjusted, thereby saving costs and ensuring the imaging quality of the imaging device.

[0094] For Figure 13The radiation detector module 900 shown can be further adjusted to collect images of 16 rows of channels if needed, and more rows (for example, four rows) of radiation detector elements 901 symmetrically arranged relative to the central position 9071 can be removed.

[0095] Figure 15 is another schematic diagram of removing part of the radiation detector elements from Figure 13 . As shown in Figure 15 , four rows of radiation detector elements 901 and the corresponding processing circuit chips 902 located at the outermost side in Figure 13 may be removed, and one row of radiation detector elements 901 and the corresponding processing circuit chips 902 located in the middle in the Z direction are retained, thereby further reducing the scanning width of the remaining radiation detector elements 901 of the radiation detector module 900 in the Z direction and the number of channels for collecting images, and the central position of the remaining radiation detector elements 901 in the Z direction remains unchanged, so that neither the position of the remaining radiation detector elements 901 nor the focal position of the radiation source (for example, an X-ray source) needs to be adjusted, thereby saving costs and ensuring the imaging quality of the imaging device.

[0096] In the present application, as shown in Figure 10 or Figure 13 , in the Y direction of the circuit substrate 903, a plurality of radiation detector elements 901 are arranged in one column (as shown in Figure 10 ) or two or more columns, for example, three columns (as shown in Figure 13 ).

[0097] In the present application, in the area of the circuit substrate 903 covered by each radiation detector element 901, one (as shown in Figure 9 ) or two or more processing circuit chips 902 are arranged.

[0098] In the present application, as shown in Figure 9 and Figure 11 , the radiation detector elements 901 are electrically connected to the corresponding processing circuit chips 902 through conductive paths 909 penetrating the circuit substrate 903.

[0099] The radiation detector module further comprises a collimator assembly 908. The collimator assembly 908 is arranged on the surface of the radiation detector element 901. The collimator assembly 908 collimates the rays emitted by the radiation source to the radiation detector element 901.

[0100] In some examples, the radiation emitted by the radiation source (e.g., X-rays) is collimated by the collimator assembly 908 and then irradiated onto the scintillator 9011. The light generated by the scintillator 9011 after being irradiated by the radiation is converted into an electrical signal by the photoelectric conversion element 9012. The electrical signal generated by the photoelectric conversion element 9012 is used to perform tomographic imaging of the object.

[0101] In addition, in other examples, the radiation detector element 901 may not include the scintillator 9011, whereby the rays emitted by the radiation source (e.g., X-rays) are collimated by the collimator assembly 908 and then irradiated onto the photon counting or direct conversion radiation detector element 901, and the radiation detector element 901 generates an electrical signal.

[0102] In the present application, the electrical signal generated by the radiation detector element 901 (e.g., the electrical signal generated by the photoelectric conversion element 9012) is transmitted to the processing circuit chip 902 via the circuit substrate 903. The processing circuit chip 902 processes the received electrical signal. For example, if the electrical signal received by the processing circuit chip 902 is an analog signal, the processing circuit chip 902 converts the analog signal into a digital signal, that is, performs analog-to-digital conversion.

[0103] Radiation detector module 900 has a flat panel form factor. The flat panel form factor of radiation detector module 900 means that the size of the radiation detector module's radiation receiving plane, which receives radiation or faces the radiation source, is significantly larger than, or several times larger than, the size of the radiation detector module parallel to the radiation propagation path. For example, if the radiation detector module has a rectangular radiation receiving plane, the length or width is significantly larger than its thickness.

[0104] Radiation detector module 900 also includes a data collection circuit board 906. Data collection circuit board 906 is electrically connected to circuit substrate 903 via flexible circuit 904 and connecting circuit 905. Signals (e.g., digital signals) processed by processing circuit chip 902 are transmitted to data collection circuit board 906 via flexible circuit 904 and connecting circuit 905.

[0105] An embodiment of the present application also provides a radiation detector.

[0106] Figure 16 FIG is a three-dimensional schematic diagram of a radiation detector according to an embodiment of the present application. Figure 16 As shown, the radiation detector 1600 includes: a guide rail 1601, and two or more radiation detector modules 900 as in any of the previous embodiments supported on the guide rail 1601, and the radiation detector module 900 arranges 4N or 4N+1 radiation detector elements 301 in the Z direction.

[0107] The radiation detector modules 900 are arranged along the Y direction in which the guide rail 1601 extends, and the number of the radiation detector modules 900 is 3 to 15. For example, the radiation detector includes 9 radiation detector modules 900, and the scanning field of view (FOV) of the radiation detector in the Y direction is 50 centimeters (cm). For example, the radiation detector includes 11 radiation detector modules 900, and the scanning field of view (FOV) of the radiation detector in the Y direction is 60 centimeters (cm).

[0108] In the radiation detector provided in the present application, the radiation detector module 900 can have a large area, so that the number of columns of the radiation detector module 900 can be reduced to 1 or more than 2, and the interconnection complexity between the radiation detector modules can be reduced, while ensuring that the radiation detector reaches a predetermined scanning field of view in the Y direction.

[0109] The present application also provides an imaging device, for example, a medical imaging device, which includes a scanning space for accommodating an examination object, and the examination object enters or exits the scanning space in the Z direction.

[0110] Figure 17 is a schematic diagram of an imaging device. As shown in Figure 17 , the imaging device 1700 includes Figure 16 the radiation detector 1600 shown in and the image reconstruction device 1701. The image reconstruction device 1701 performs tomographic imaging of the object according to the electrical signals generated by the photoelectric conversion elements 9012 in the radiation detector modules of the radiation detector, for example, as shown in Figure 9 .

[0111] In some examples, the image reconstruction device 1701 can perform image reconstruction using the data collected by the data collection circuit board 906, for example. Figure 9 The detailed description of the image reconstruction device 1701 can refer to related technologies.

[0112] The imaging device provided in the present application is, for example, a CT (Computed Tomography) imaging device, a PET-CT, or any other suitable imaging device.

[0113] The present application also provides a manufacturing method of a radiation detector, as shown in Figure 18 , the manufacturing method includes:

[0114] 1801. Mounting two or more radiation detector modules 900 on the guide rail 1601.

[0115] In operation 1801, the number of the radiation detector modules 900 is, for example, 3 to 15.

[0116] In operation 1801, two or more radiation detector modules 900 are arranged along the extension direction of the guide rail 1601, for example, along the Y direction.

[0117] In the present application, as shown in Figure 18 the manufacturing method can further include:

[0118] 1802, removing part of the radiation detector elements 901 of the radiation detector module 900, or adding part of the radiation detector elements 901 in the radiation detector module 900.

[0119] For example, in operation 1802, part of the radiation detector elements 901 on both sides of the central position 9071 in the first direction (Z direction) can be removed or a predetermined number of radiation detector elements 901 can be installed on both sides of the central position 9071 in a symmetrical manner relative to the central position 9071 of the circuit substrate 903 in the first direction.

[0120] The above embodiments are only exemplary descriptions of the embodiments of the present application, but the present application is not limited thereto, and appropriate modifications can be made on the basis of the above embodiments. For example, each of the above embodiments can be used alone, or one or more of the above embodiments can be combined.

[0121] The present application has been described above in conjunction with specific embodiments, but it should be clear to those skilled in the art that these descriptions are exemplary and not limiting the scope of protection of the present application. Those skilled in the art can make various modifications and changes to the present application according to the principles of the present application, and these modifications and changes are also within the scope of the present application.

Claims

1. A radiation detector module for detecting a radiation signal passing through an examination object entering or exiting an imaging device in a first direction, characterized by The radiation detector module comprises: a radiation detector element receiving a ray emitted by a radiation source and converting the ray into an electric signal; a circuit substrate having a first side on which a plurality of the radiation detector elements are mounted, in the first direction of the circuit substrate, the plurality of the radiation detector elements are arranged in 4N rows or 4N+1 rows, N being an integer greater than or equal to 1; and a processing circuit chip arranged on a second side of the substrate and in communication with the radiation detector elements.

2. The radiation detector module according to claim 1, wherein in the first direction, the plurality of the radiation detector elements are arranged symmetrically with respect to a central position of the circuit substrate in the first direction.

3. The radiation detector module according to claim 1, wherein each of the radiation detector elements has 16 rows of ray transmission channels distributed along the first direction.

4. The radiation detector module according to claim 1, wherein in a second direction of the circuit substrate, the plurality of the radiation detector elements are arranged in one column or more than two columns.

5. The radiation detector module according to claim 1, wherein in an area of the circuit substrate covered by each of the radiation detector elements, one or more of the processing circuit chips are arranged.

6. The radiation detector module according to claim 1, wherein the radiation detector elements are electrically connected to the processing circuit chip through a conductive path penetrating the circuit substrate.

7. The radiation detector module of claim 1, wherein, The radiation detector element comprises a scintillator and a photoelectric conversion element, the scintillator receives a ray and generates light, the photoelectric conversion element converts the light generated by the scintillator into an electric signal, and the photoelectric conversion element comprises a backlit photodiode.

8. The radiation detector module of claim 1, wherein, The radiation detector module has a flat plate configuration.

9. The radiation detector module of claim 1, wherein, The radiation detector module further comprises: a data collection circuit board electrically connected to the circuit substrate through a wire and receiving data processed by the processing circuit chip.

10. The radiation detector module of claim 1, wherein, The radiation detector module further comprises: a collimator assembly arranged on a surface of the radiation detector element, the collimator assembly collimates a ray emitted by a radiation source towards the radiation detector element.

11. A radiation detector, characterized by The radiation detector comprises a guide rail and two or more radiation detector modules as claimed in any one of claims 1 to 10 supported by the guide rail.

12. An image forming apparatus characterized by comprising: The imaging device comprises a scanning space accommodating an examination object, and the examination object enters or exits the scanning space in the first direction, the imaging device has a radiation detector as claimed in claim 11 and an image reconstruction device, the image reconstruction device performs image reconstruction to generate a tomographic image of the examination object according to the electric signals generated by the radiation detector elements in the radiation detector modules of the radiation detector.

Images