Collimator assembly, detector module and imaging device

Abstract

The embodiment of the utility model provides a collimator assembly, a detector module and imaging equipment. The collimator assembly comprises a collimator which is of an integrated structure and comprises a collimation main body part located in the middle and an extension part located on the outer side of the collimation main body part and connected with the collimation main body part, and the collimation main body part is provided with a channel allowing rays to penetrate in the preset direction; the supporting part is connected with the extending part and used for supporting the collimator, one of the extending part and the supporting part is provided with at least one shading part, and the other one of the extending part and the supporting part is provided with an accommodating part for accommodating the at least one shading part. In the collimator assembly, the light shielding part and the accommodating part for accommodating the light shielding part are formed at the joint of the collimator and the supporting part, so that the possibility of light leakage at the joint is reduced through mutual matching of the light shielding part and the accommodating part.

Description

Technical Field

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

[0002] Imaging devices are used to scan an examination subject (such as a patient or workpiece) in a non-invasive or non-destructive manner, thereby acquiring images of the internal structure of the subject's anatomical tissue or region of interest to assist in diagnosis. Imaging devices typically include a circular scanning aperture through which the scanned subject can enter and exit, and a detector subsystem mounted along the entire circumference or a portion of the circular aperture. The detector subsystem comprises multiple detector assemblies mounted on a gantry.

[0003] For example, computed tomography (CT) equipment is commonly used as a medical imaging device to scan patients and obtain cross-sectional medical images of areas of interest to assist doctors in diagnosis. CT equipment includes multiple detector assemblies that receive X-rays emitted by an X-ray tube and passed through the patient. The configuration and number of each detector assembly depend on clinical needs and the design of the CT system.

[0004] Each detector assembly in a CT device typically includes a pixelated scintillator and a photoelectric conversion device arranged in sequence along the direction of ray transmission. The scintillator is used to receive X-rays passing through the patient and generate light. The photoelectric conversion device (such as a photodiode) converts the light generated by the scintillator into an electrical signal. Each detector assembly also includes a collimator for collimating the X-rays passing through the patient in a specific direction to avoid or reduce interference between the scintillator pixels. Each detector assembly also includes a signal processing circuit for processing the electrical signals generated by the photoelectric conversion device, as well as a frame for supporting the collimator, scintillator, photoelectric conversion device, circuit board, and heat sink.

[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] The inventors discovered that there are gaps between the collimator of a detector assembly and its supporting structure or between the collimators of multiple detectors. Light generated by the scintillator receiving X-rays or light from other sources (especially visible light) can propagate or leak in the gaps. The leaked light may illuminate a specific photoelectric conversion element and may cause the specific photoelectric conversion element to generate an erroneous electrical signal, thereby affecting the medical imaging effect of the CT equipment.

[0008] In response to at least one of the above-mentioned technical problems or other similar problems, an embodiment of the present application provides a collimator assembly, a detector module and an imaging device. In the collimator assembly, a light-shielding portion and a receiving portion for accommodating the light-shielding portion are formed at the connection between the collimator and the support portion. Thus, through the mutual cooperation between the light-shielding portion and the receiving portion, the possibility of light leakage at the connection is reduced.

[0009] According to one aspect of an embodiment of the present application, a collimator assembly is provided for collimating radiation emitted from a radiation source toward a radiation sensor. The collimator assembly includes:

[0010] A collimator having an integrated structure and comprising a collimating body portion located in the middle and an extension portion outside the collimating body portion and connected to the collimating body portion, wherein the collimating body portion has a channel allowing rays to pass through in a predetermined direction; and

[0011] A support portion is connected to the extension portion and supports the collimator, wherein one of the extension portion and the support portion has at least one light shielding portion, and the other of the extension portion and the support portion has a receiving portion for accommodating the at least one light shielding portion.

[0012] In the collimator assembly, a light shielding portion and a receiving portion for accommodating the light shielding portion are formed at the connection between the collimator and the support portion. Thus, through the mutual cooperation between the light shielding portion and the receiving portion, the possibility of light leakage at the connection is reduced, thereby preventing the leaked light from irradiating the photoelectric conversion element and affecting the medical imaging effect of the CT equipment.

[0013] In some embodiments, the support portion is disposed on both sides of the collimating body portion along a width direction.

[0014] In some embodiments, the extension comprises:

[0015] a first light-shielding wall extending outwardly along a radiation-emitting surface of the collimating body; and

[0016] A second light-shielding wall extends along a surface perpendicular to the radiation emitting surface of the collimating body, the second light-shielding wall is located at both ends of the collimating body along the length direction, and the receiving portion is formed between the first light-shielding wall and the second light-shielding wall.

[0017] In some embodiments, a dimension of the first light-shielding wall extending along the width direction is greater than a dimension of the second light-shielding wall extending along the width direction.

[0018] In some embodiments, the extension portion further includes a mounting portion for mounting a fixing element, and the first light-shielding wall is connected to the mounting portion.

[0019] In some embodiments, the collimator assembly further includes a light shielding plate, which covers at least the radiation incident surface of the collimating body portion, and the light shielding plate transmits the radiation without loss.

[0020] In some embodiments, at least one of the extension portion and the support portion is a light absorbing component.

[0021] In some embodiments, a surface of at least one of the extension portion and the support portion has a black coating.

[0022] In some embodiments, the collimator assembly further comprises:

[0023] A first light-shielding tape covers a gap between the extending portion and the supporting portion.

[0024] According to another aspect of the embodiments of the present application, a detector module is further provided, the detector module comprising:

[0025] The sensor includes a plurality of scintillators that receive radiation and generate light, and a plurality of photoelectric conversion elements that convert the light generated by the scintillators after being irradiated by radiation into electrical signals;

[0026] The collimator assembly according to any one of the above embodiments, wherein the collimator body of the collimator assembly has a radiation incident surface for receiving the incident radiation and a radiation exit surface located behind the radiation incident surface, the radiation exit surface being bonded to the sensor; and

[0027] A frame supports the sensor and the collimator assembly.

[0028] In some embodiments, the detector module further includes a second light-shielding tape, wherein the second light-shielding tape covers a joint gap between the exit surface and the sensor.

[0029] In some embodiments, the second light-shielding tape has a thickness of 5 micrometers to 40 micrometers.

[0030] According to another aspect of the embodiments of the present application, a detector module is further provided, the detector module comprising:

[0031] The sensor includes a plurality of scintillators that receive radiation and generate light, and a plurality of photoelectric conversion elements that convert the light generated by the scintillators after being irradiated by radiation into electrical signals;

[0032] a collimator, which is an integrated structure and is used to collimate the radiation emitted by the radiation source to the radiation sensor; and

[0033] a supporting portion connected to the collimator;

[0034] Wherein, one of the collimator and the support portion has at least one light shielding portion, and the light shielding portion extends to a position that shields a gap formed between the collimator and the support portion.

[0035] In the detector module, one of the collimator and the support portion has at least one light shielding portion, thereby reducing the possibility of light leakage at the connection between the collimator and the support portion, thereby preventing the leaked light from irradiating the photoelectric conversion element and affecting the medical imaging effect of the CT equipment.

[0036] In some embodiments, the collimator includes a collimating body portion having a channel allowing rays to pass through in a predetermined direction; the light shielding portion includes an extension portion located outside the collimating body portion and connected to the collimating body portion.

[0037] In some embodiments, the extension portion includes a first light-shielding wall extending from both sides of the collimator body portion and toward the support portion, and the first light-shielding wall shields at least a portion of a gap formed between the collimator and the support portion.

[0038] In some embodiments, the extension portion includes second light-shielding walls extending from both sides of the collimating body portion and toward the supporting portion, and the second light-shielding walls are perpendicular to the first light-shielding walls.

[0039] In some embodiments, the first light-shielding wall is parallel to the radiation incident surface of the collimating main body, the second light-shielding wall is perpendicularly arranged at both ends of the first light-shielding wall, and the first light-shielding wall and the second light-shielding wall cover at least two surfaces of the gap formed between the collimator and the support part.

[0040] In some embodiments, the supporting portion includes a receiving portion for receiving the first light-shielding wall and the second light-shielding wall.

[0041] In some embodiments, the light-shielding portion further includes a first light-shielding tape covering a gap between the extending portion and the supporting portion.

[0042] According to another aspect of an embodiment of the present application, a medical imaging device is provided, which has the detector module and imaging device described in the above embodiment, and the imaging device performs tomographic imaging of the object based on the electrical signal generated by the photoelectric conversion element in the sensor of the detector module.

[0043] 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

[0044] 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:

[0045] Figure 1 is a schematic diagram of a CT device according to an embodiment of the present application;

[0046] Figure 2 is a schematic diagram of a CT imaging system according to an embodiment of the present application;

[0047] Figure 3 is a schematic diagram of a collimator assembly according to an embodiment of the present application;

[0048] Figure 4 is a schematic three-dimensional assembly diagram of a collimator assembly according to an embodiment of the present application;

[0049] Figure 5 is a schematic diagram of a collimator according to an embodiment of the present application;

[0050] Figure 6 It is along Figure 3 Schematic diagram of the cross section observed from the AA direction;

[0051] Figure 7 is a three-dimensional schematic diagram of the collimator assembly viewed from the incident surface of the collimator body;

[0052] Figure 8 is a schematic diagram of a detector module according to an embodiment of the present application;

[0053] Figure 9 It is a schematic diagram of the composition of an imaging device. DETAILED DESCRIPTION

[0054] 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.

[0055] 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.

[0056] 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.

[0057] 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.

[0058] The medical imaging device described in this application can be applicable to various medical imaging modalities, including but not limited to CT (computed tomography) imaging equipment, PET (positron emission tomography)-CT, magnetic resonance imaging (MRI) or any other suitable medical imaging equipment.

[0059] 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.

[0060] 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.

[0061] 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.

[0062] 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 2 As 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 .

[0063] 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.

[0064] 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.

[0065] 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.

[0066] 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.

[0067] 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.

[0068] 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.

[0069] The above schematically illustrates medical image scanning, and the following embodiments of the present application are specifically described with reference to the accompanying drawings. In the following embodiments, the medical imaging device is a CT device as an example for description, and the description is also applicable to other medical imaging devices.

[0070] An embodiment of the present application provides a collimator assembly.

[0071] Figure 3 FIG. 1 is a schematic diagram of a collimator assembly according to an embodiment of the present application. Figure 3 As shown, the collimator assembly 300 includes: a collimator 3 and a support portion 4.

[0072] The collimator assembly 300 is used to collimate the radiation emitted by the radiation source to the sensor (the sensor of the present application is also referred to as a radiation sensor). In some examples, the radiation source can be Figure 2 The X-ray source 103 is shown; the sensor can be Figure 2 The detector unit 104a may include a scintillator and a photoelectric conversion element, wherein the rays (e.g., X-rays) emitted by the X-ray source 103 are collimated by the collimator assembly 300 and then irradiated onto the scintillator, and the light generated by the scintillator after being irradiated by the rays is converted into an electrical signal by the photoelectric conversion element, and the electrical signal generated by the photoelectric conversion element is used for tomographic imaging of the object.

[0073] Figure 4 3D is a schematic diagram of the three-dimensional assembly of the collimator assembly according to an embodiment of the present application, showing the structure of the collimator 3 and the two support parts 4 in a separated state. Figure 5 Schematic diagram of a collimator according to an embodiment of the present application. Figure 6 It is along Figure 3 Schematic diagram of the cross section observed from the AA direction.

[0074] like Figure 3 、 Figure 4 and Figure 5As shown, the collimator 3 can be a one-piece structure, thereby reducing light leakage caused by assembly gaps when different components are assembled together. In contrast, if it is a split structure, the gaps between the different components when the split structure is assembled together are more likely to cause light leakage. In some examples, the collimator 3 can be a one-piece structure formed by a 3D printing method.

[0075] The collimator 3 includes a collimating body portion 31 located in the middle and an extending portion 32 outside the collimating body portion 31 and connected to the collimating body portion 31 .

[0076] The collimating body 31 has an emission surface 31B ( Figure 3 and Figure 4 shown) and incident surface 31A ( Figure 5 As shown in FIG. 1 , the collimating body 31 may be in the shape of a rectangular parallelepiped, having a width direction W and a length direction L. The width direction W and the length direction L are perpendicular to each other and parallel to the incident surface 31A or the exit surface 31B. In this application, the incident surface may also be referred to as the radiation incident surface, and the exit surface may also be referred to as the radiation exit surface.

[0077] The collimating body 31 has channels 311 that allow radiation to pass through in a predetermined direction. There can be multiple channels 311, distributed in an array on the incident surface 31A of the collimating body 31. These channels 311 extend along the predetermined direction and penetrate both the incident surface 31A and the exit surface 31B of the collimating body 31. Thus, when radiation emitted by the radiation source strikes the incident surface 31A, radiation traveling in the predetermined direction can pass through the channels 311 and exit from the exit surface 31B of the collimating body 31. Radiation traveling in unpredictable directions is absorbed by the collimating body 31.

[0078] In the present application, the support portion 4 is connected to the extension portion 32 , thereby supporting the collimator 3 . For example, the support portion 4 is provided on both sides of the collimator body portion 31 in the width direction W.

[0079] like Figure 4 As shown, in some examples, the extension portion 32 has at least one (for example, four) receiving portion 321, and the support portion 4 has at least one (for example, four) light shielding portion 41, and each receiving portion 321 accommodates a corresponding light shielding portion 41. In addition, the present application is not limited thereto, and in other examples, the receiving portion can be provided on the support portion 4, and the light shielding portion can be provided on the extension portion 32; or, a portion of the receiving portions and a portion of the light shielding portions can be provided on the support portion 4, and another portion of the receiving portions and another portion of the light shielding portions can be provided on the extension portion 32.

[0080] Thus, one of the extension part 32 and the support part 4 has at least one light-shielding part, and the other of the extension part 32 and the support part 4 has a receiving part for accommodating the at least one light-shielding part. Through such a structure, the light-shielding part and the receiving part can cooperate with each other to reduce the possibility of light leakage at the connection between the extension part 32 and the support part 4, thereby avoiding the leaked light from irradiating the photoelectric conversion element and affecting the medical imaging effect of the medical imaging equipment (for example, CT equipment).

[0081] In the following description of this application, the example in which the receiving portions 321 are all arranged on the extension portion 32 and the shading portions 41 are all arranged on the support portion 4 will be used for explanation. The description is also applicable to the case in which at least one receiving portion is arranged on the support portion or at least one shading portion is arranged on the extension portion 32.

[0082] like Figure 4 and Figure 5 As shown, the extension portion 32 includes a first light shielding wall 322 and a second light shielding wall 323 .

[0083] The first light-shielding wall 322 extends outward along the exit surface 31B of the collimating body 31. For example, the first light-shielding wall 322 is parallel to the exit surface 31B of the collimating body 31 and extends along the width direction W to the outside of the exit surface 31B along the width direction W. Thus, the first light-shielding wall 322 can block light from entering the collimating body 31 on both sides of the collimating body 31 along the width direction W.

[0084] The second light-shielding walls 323 extend along a surface perpendicular to the emission surface 31B of the collimator body 31. The second light-shielding walls 323 are located at both ends of the collimator body 31 along the longitudinal direction L. Furthermore, the second light-shielding walls 323 extend outward of the collimator body 31 in the width direction W relative to the collimator body 31. Thus, the second light-shielding walls 323 can block light from entering the collimator body 31 at both ends of the collimator body 31 along the longitudinal direction L.

[0085] In this application, the receiving portion 321 is formed between the first light shielding wall 322 and the second light shielding wall 323, so that Figure 6 As shown, the corner space enclosed by the first light-shielding wall 322 and the second light-shielding wall 323 can be fully utilized to accommodate the light-shielding portion 41. In this way, the light-shielding effect can be improved by the first light-shielding wall 322, the second light-shielding wall 323 and the light-shielding portion 41, and space can be saved to simplify the structure and avoid setting up a special space for accommodating the light-shielding portion 41.

[0086] like Figure 5As shown, the dimension of the first light shielding wall 322 extending in the width direction W is greater than the dimension of the second light shielding wall 323 extending in the width direction W. Thus, when the collimator 3 and the support portion 4 are assembled into one, the first light shielding wall 322 can cover the gap G ( Figure 6 shown).

[0087] In at least some embodiments, Figure 3 、 Figure 4 and Figure 5 As shown, the extension portion 32 further includes a mounting portion 324. The mounting portion 324 is used to mount a fixing element (not shown), such as a screw. Figure 4 As shown, the support portion 4 may include mounting holes 42. The mounting holes 42 may correspond to the positions of the mounting portions 324. The number of mounting holes 42 and the number of mounting portions 324 may be the same (for example, there may be six mounting holes 42 and six mounting portions 324). The mounting holes 42 may be screw holes, so that a fixing element such as a screw may be fixedly mounted in the mounting holes 42. Thus, the mounting portion 324, the mounting holes 42, and the fixing element may connect the support portion 4 and the collimator 3 together.

[0088] In the present application, the first light shielding wall 322 is connected to the mounting portion 324 , thereby preventing light leakage between the first light shielding wall 322 and the mounting portion 234 and improving the strength of the first light shielding wall 322 and the mounting portion 324 .

[0089] like Figure 4 As shown, a positioning hole 325 may be provided near the mounting portion 324, for example, the positioning hole 325 is provided on one side of the mounting portion 324 along the length direction L. The support portion 4 may have a positioning post 43, the position of the positioning post 43 corresponding to the positioning hole 325. When the collimator 3 and the support portion 4 are installed, the positioning post 43 may be inserted into the positioning hole 325, thereby achieving alignment between the collimator 3 and the support portion 4.

[0090] In the present application, the number of the positioning holes 325 may be at least one, for example, two. Figure 4 As shown, the two positioning holes 325 are respectively close to the mounting portion 324 at both ends of the length direction L. The positions of the positioning posts 43 correspond to the positions of the positioning holes 325 , and the number of the positioning posts 43 is the same as the number of the positioning holes 325 .

[0091] In addition, the present application is not limited to this. In other examples, at least one positioning hole may be provided on the support portion 4, and at least one positioning column may be provided on the extension portion 32. In other embodiments, the positioning column may be a component independent of the support portion 4 and the extension portion 32, and aligned mounting holes are provided on the support portion 4 and the extension portion 32, respectively. The positioning column is installed in the mounting hole to fix or connect the collimator 3 and the support portion 4. For example, the mounting hole is a threaded hole, and the positioning column is a stud with a height corresponding to the threaded hole.

[0092] In the present application, at least one of the extension portion 32 and the support portion 4 is a light-absorbing component. For example, at least one of the extension portion 32 and the support portion 4 may have a black coating or another dark coating on its surface. This allows at least one of the extension portion 32 and the support portion 4 to absorb light, preventing it from being reflected, scattered, or entering the interior of the collimator 3.

[0093] like Figure 3 As shown, the collimator assembly 300 further includes a first light-shielding tape 5. The first light-shielding tape 5 covers the gap between the extension portion 32 and the support portion 4. Thus, the first light-shielding tape 5 further prevents external light from entering the interior of the collimator assembly 300. The first light-shielding tape 5 can be black or another dark color to enhance the light-shielding effect. In some examples, the thickness of the first light-shielding tape 5 can range from 5 microns to 40 microns. For example, the first light-shielding tape 5 can be an adhesive tape having at least one surface that is sticky. Figure 3 The first shading band 5 shown is arranged at both ends of the extension portion 32 and the support portion 4 to cover the gap at the junction of the two end surfaces; in other embodiments, the first shading band 5 can be arranged on the surface of the extension portion 32 and the support portion 4, which is parallel to the bottom surface of the collimator main body 31 or the output surface 31B described below, and the first shading band 5 shields the gap at the junction of the extension portion 32 and the support portion 4 at the surface.

[0094] Figure 7 FIG. 3 is a perspective view of the collimator assembly 300 viewed from the incident surface 31A of the collimator body 31. Figure 4 and Figure 7 As shown, the collimator assembly 300 further includes a light shield 6. The light shield 6 covers at least the incident surface 31A of the collimator body 31. The light shield 6 can transmit radiation (e.g., X-rays) emitted by the radiation source without loss. Thus, the light shield 6 can both block external light from entering the collimator 3 while allowing radiation emitted by the radiation source to penetrate the light shield 6 and enter the incident surface 31A of the collimator body 31. In some examples, the light shield 6 can be, for example, a rectangular sheet, and the material of the light shield 6 can be carbon fiber, plastic, or the like.

[0095] The embodiment of the present application also provides a detector module.

[0096] Figure 8 FIG. 1 is a schematic diagram of a detector module according to an embodiment of the present application. Figure 8 As shown, the detector module 800 includes a sensor 81 , a collimator assembly 300 and a frame 82 .

[0097] The sensor 81 includes multiple scintillators 811 for receiving radiation, and multiple photoelectric conversion elements 812, such as photodiodes, for converting light generated by the scintillators 811 into electrical signals. The multiple scintillators 811 can be arranged in an array, and the multiple photoelectric conversion elements 812 can also be arranged in an array corresponding to the scintillators 811.

[0098] The collimator body 31 of the collimator assembly 300 includes an incident surface 31A for receiving incident radiation and an exit surface 31B located behind the incident surface 31A. The exit surface 31B is connected to the sensor 81 .

[0099] The frame 82 supports the sensor 81 and the collimator assembly 300 .

[0100] like Figure 8 As shown, the detector module 800 further includes a second light-shielding tape 83. The second light-shielding tape 83 covers the joint gap between the exit surface 31B and the sensor 8. For example, the second light-shielding tape 83 can cover the sidewalls of the collimator assembly 300 and the sensor 81. Thus, the second light-shielding tape 83 prevents external light from entering the interior of the collimator assembly 300.

[0101] The second light shielding tape 83 can be black or other dark colors to improve the light shielding effect. In some examples, the thickness of the second light shielding tape 83 can be 5 microns to 40 microns. The second light shielding tape 83 can be, for example, an adhesive tape with at least one side having adhesiveness.

[0102] In some embodiments, Figure 8 The second light shielding band 83 is shown with Figure 3 The first light shielding strip 5 shown is the same component

[0103] In other embodiments, the present application also provides a detector module. Figures 3 to 8 , the detector module 800 includes:

[0104] The sensor 81 includes a plurality of scintillators 811 that receive radiation and generate light, and a plurality of photoelectric conversion elements 812 that convert the light generated by the scintillators 811 after being irradiated by radiation into electrical signals;

[0105] a collimator 3 , which is an integrated structure and is used to collimate the radiation emitted from the radiation source to the radiation sensor; and

[0106] The supporting portion 4 is connected to the collimator 3 .

[0107] One of the collimator 3 and the support portion 4 has at least one light shielding portion, and the light shielding portion extends to a position that blocks a gap formed between the collimator 3 and the support portion 4 .

[0108] In the detector module, one of the collimator and the support portion has at least one light shielding portion, thereby reducing the possibility of light leakage at the connection between the collimator and the support portion, thereby preventing the leaked light from irradiating the photoelectric conversion element and affecting the medical imaging effect of the CT equipment.

[0109] In some examples, the collimator 3 includes a collimating body 31 having a channel 311 allowing rays to pass through in a predetermined direction; the light shielding portion includes an extension portion 32 located outside the collimating body 31 and connected to the collimating body 31 .

[0110] In some examples, the extension portion 32 includes first light shielding walls 322 extending from both sides of the collimating body 31 and toward the support portion 4 . The first light shielding walls 322 shield at least a portion of the gap formed between the collimator 3 and the support portion 4 .

[0111] In some examples, the extension portion 32 includes second light-shielding walls 323 extending from both sides of the collimating body portion 31 and toward the support portion 4 . The second light-shielding walls 323 are perpendicular to the first light-shielding walls 322 .

[0112] In some examples, the first light-shielding wall 322 is parallel to the radiation incident surface of the collimating body 31 , and the second light-shielding wall 323 is perpendicularly arranged at both ends of the first light-shielding wall 322 , and the first light-shielding wall 322 and the second light-shielding wall 323 cover at least two surfaces of the gap formed between the collimator 3 and the support portion 4 .

[0113] In some examples, the support portion 4 includes a receiving portion for receiving the first light-shielding wall 322 and the second light-shielding wall 323 .

[0114] The shading portion further includes a first shading tape 5 , which covers the gap between the extending portion and the supporting portion.

[0115] An embodiment of the present application further provides an imaging device, which is, for example, a medical imaging device.

[0116] Figure 9 This is a schematic diagram of the composition of an imaging device. Figure 9 As shown, the imaging device 900 includes Figure 8 The detector module 800 and the imaging device 91 are shown. The imaging device 91 performs tomographic imaging of the object based on the electrical signal generated by the photoelectric conversion element 812 of the sensor 81 in the detector module 800.

[0117] In some examples, the imaging device 91 may correspond to, for example, Figure 2The imaging device 91 includes a data acquisition system (DAS) 104b and an image reconstruction device 204. For detailed description of the imaging device 91, reference may be made to related art.

[0118] The imaging device 900 of the present application is, for example, a CT (computed tomography) imaging device, a PET-CT or any other suitable medical imaging device.

[0119] 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 collimator assembly for collimating radiation emitted from a radiation source to a radiation sensor, characterized in that: The collimator assembly comprises: A collimator having an integrated structure and comprising a collimating body portion located in the middle and an extension portion outside the collimating body portion and connected to the collimating body portion, wherein the collimating body portion has a channel allowing rays to pass through in a predetermined direction; and a supporting portion connected to the extending portion and supporting the collimator, One of the extending portion and the supporting portion has at least one light shielding portion, and the other of the extending portion and the supporting portion has a receiving portion for receiving the at least one light shielding portion.

2. The collimator assembly according to claim 1, wherein The support portions are provided on both sides of the collimating body portion along a width direction.

3. The collimator assembly according to claim 2, wherein: The extension portion comprises: a first light-shielding wall extending outwardly along a radiation-emitting surface of the collimating body; and a second light-shielding wall extending along a surface perpendicular to the radiation emitting surface of the collimating main body, the second light-shielding wall being located at both ends of the collimating main body in the length direction; The receiving portion is formed between the first light shielding wall and the second light shielding wall.

4. The collimator assembly according to claim 3, wherein: A dimension of the first light shielding wall extending along the width direction is greater than a dimension of the second light shielding wall extending along the width direction.

5. The collimator assembly according to claim 3, wherein: The extension portion further includes a mounting portion for mounting a fixing element, and the first light-shielding wall is connected to the mounting portion.

6. The collimator assembly according to claim 1, wherein: The collimator assembly further includes a light shielding plate, which at least covers the radiation incident surface of the collimating body portion and transmits the radiation without loss.

7. The collimator assembly according to claim 1, wherein: At least one of the extending portion and the supporting portion is a light absorbing member.

8. The collimator assembly according to claim 7, wherein: A surface of at least one of the extension portion and the support portion has a black coating.

9. The collimator assembly according to claim 1, wherein: The collimator assembly further comprises: A first light-shielding tape covers a gap between the extending portion and the supporting portion.

10. A detector module, characterized in that: The detector module comprises: The sensor includes a plurality of scintillators that receive radiation and generate light, and a plurality of photoelectric conversion elements that convert the light generated by the scintillators after being irradiated by radiation into electrical signals; The collimator assembly according to any one of claims 1 to 9, wherein the collimator body of the collimator assembly has a radiation incident surface for receiving the incident radiation and a radiation exit surface located behind the radiation incident surface, the radiation exit surface being bonded to the sensor; and A frame supports the sensor and the collimator assembly.

11. The detector module according to claim 10, wherein The detector module further includes a second light-shielding tape, which covers a joint gap between the radiation exit surface and the sensor.

12. The detector module according to claim 11, wherein The thickness of the second light-shielding tape is 5 micrometers to 40 micrometers.

13. A detector module, characterized in that: The detector module comprises: The sensor includes a plurality of scintillators that receive radiation and generate light, and a plurality of photoelectric conversion elements that convert the light generated by the scintillators after being irradiated by radiation into electrical signals; a collimator, which is an integrated structure and is used to collimate the radiation emitted by the radiation source to the radiation sensor; and a supporting portion connected to the collimator; Wherein, one of the collimator and the support portion has at least one light shielding portion, and the light shielding portion extends to a position that shields a gap formed between the collimator and the support portion.

14. The detector module according to claim 13, wherein The collimator includes a collimating body portion having a channel allowing rays to pass through in a predetermined direction; the light shielding portion includes an extension portion located outside the collimating body portion and connected to the collimating body portion.

15. The detector module according to claim 14, wherein The extending portion includes first light-shielding walls extending from both sides of the collimating body portion toward the supporting portion, and the first light-shielding walls shield at least a portion of a gap formed between the collimator and the supporting portion.

16. The detector module according to claim 15, wherein The extending portion includes second light-shielding walls extending from both sides of the collimating main portion toward the supporting portion, and the second light-shielding walls are perpendicular to the first light-shielding walls.

17. The detector module according to claim 16, wherein The first light-shielding wall is parallel to the radiation incident surface of the collimating main body, the second light-shielding wall is perpendicularly arranged at both ends of the first light-shielding wall, and the first light-shielding wall and the second light-shielding wall cover at least two surfaces of the gap formed between the collimator and the supporting part.

18. The detector module according to claim 17, wherein The supporting portion includes a receiving portion for receiving the first light-shielding wall and the second light-shielding wall.

19. The detector module according to claim 18, wherein The light shielding portion further includes a first light shielding tape covering a gap between the extending portion and the supporting portion.

20. An imaging device, characterized in that The imaging apparatus comprises the detector module according to any one of claims 10 to 19 and an imaging device for performing tomographic imaging of an object based on electrical signals generated by photoelectric conversion elements in sensors of the detector module.

Images