Detector module, detector, and medical imaging apparatus

Abstract

The utility model discloses a detector module, a detector and medical imaging equipment. The detector module is used for detecting rays emitted by a radiation source and attenuated by a scanned object. The detector module comprises a module support and a plurality of sub-modules, wherein the module support extends in the Z direction; the plurality of sub-modules are sequentially mounted on the module bracket along the Z direction, and are provided with a plurality of pixels which are arranged in an array along the X direction and the Z direction; the plurality of sub-modules comprise a first sub-module and a second sub-module, and in the Z direction, the pixel size of the first sub-module is smaller than the pixel size of the second sub-module. The detector module is provided with a plurality of sub-modules which can be mounted and arranged according to actual requirements, so that the detector module adapts to different detection environments and requirements, images with higher resolution and thinner thickness are realized, and meanwhile, the cost of the detector module is controlled.

Description

Technical Field

[0001] The present application relates to the technical field of medical equipment, and in particular to a detector module, a detector and a medical equipment. Background Art

[0002] With the continuous development of medical technology, more and more medical equipment is used to assist medical diagnosis or treatment. For example, CT (Computed Tomography) equipment is used to detect human diseases. CT equipment detects X-rays passing through the human body through a CT detector and converts the received optical signals into electrical signals. The multiple detector submodules installed on the shell of the CT detector are important components in the CT detector for realizing photoelectric conversion. In order to ensure the diagnostic effect of the CT detector, more detector submodules need to be installed on the shell. Utility Model Content

[0003] The utility model aims to solve at least one of the technical problems existing in the prior art. To this end, the first aspect of the utility model aims to provide a detector module, which can provide images with higher resolution and thinner layer thickness.

[0004] The second aspect of the present invention aims to provide a detector.

[0005] The third aspect of the present invention aims to provide a medical imaging device.

[0006] According to the detector module of the first aspect of the present utility model, the detector module is used to detect the rays emitted by the radiation source after being attenuated by the scanned object. The detector module includes a module bracket and a plurality of submodules, wherein the module bracket is extended along the Z direction; the plurality of submodules are sequentially mounted on the module bracket along the Z direction, and the submodule is provided with a plurality of pixels arranged in an array along the X direction and the Z direction; the plurality of submodules include a first submodule and a second submodule, and in the Z direction, the size of the pixels of the first submodule is smaller than the size of the pixels of the second submodule.

[0007] According to the detector module of the embodiment of the utility model, by setting a plurality of submodules, the flexibility of setting the detector module is improved. A plurality of submodules can be installed and arranged according to actual needs, so as to adapt to different detection environments and needs. Among the plurality of submodules, a first submodule and a second submodule are included. The Z-direction size of the pixels of the first submodule is smaller than the Z-direction size of the pixels of the second submodule. The pixels on the first submodule can be arranged more densely in the Z direction, which can provide more refined detection results and is suitable for detection scenes requiring high resolution. The second submodule is set on the detector module, that is, only a part of the submodules on the detector module adopts a dense pixel solution, and the other part of the modules adopts a non-dense pixel solution, which can appropriately control the cost. The setting of the second submodule can provide a wider detection range, which is suitable for detection scenes requiring large area coverage. Not only the performance of the detector module is improved, but also its practicality is increased to achieve the best detection effect.

[0008] According to the detector module of some embodiments of the present invention, the number of the pixels of the first submodule is an integer multiple of the number of the pixels of the second submodule.

[0009] According to the detector module of some embodiments of the present invention, the submodule further includes: a wiring harness connecting the plurality of pixels; a circuit board mounted on the module bracket and connected to the wiring harness; the number of the wiring harnesses on the first submodule is greater than the number of the wiring harnesses on the second submodule.

[0010] Optionally, at least two of the cables are arranged in sequence along the X direction on the first submodule; the circuit boards correspond to the cables one by one, and the circuit boards are located on one side of the cables in the X direction.

[0011] In some specific embodiments, in the X direction, the size of the pixel of the first submodule is smaller than the size of the pixel of the second submodule.

[0012] In some specific embodiments, in the Z direction, the module bracket includes a first area located in the middle and a second area located outside the first area, the first submodule is installed on the first area, and the second submodule is installed on the second area.

[0013] Optionally, the second submodule is further installed on the first area, and the second submodule on the first area is located on at least one side of the first submodule.

[0014] Optionally, a radius of a target circle tangent to the top surface of the submodule in the first region is smaller than a radius of a target circle tangent to the top surface of the submodule in the second region; and a center of the target circle is located at a focus of the radiation source.

[0015] In some embodiments, the X-dimension of the submodule at the middle position is greater than the X-dimension of the submodule at the two side positions.

[0016] A detector according to an embodiment of the second aspect of the utility model comprises a housing and a plurality of detector modules, wherein the plurality of detector modules are arranged side by side along the X direction. The detector module is the detector module of the embodiment of the first aspect of the present application.

[0017] According to the detector of the embodiment of the utility model, by adopting the above-mentioned detector module, the detector is made more flexible and practical, and provides strong technical support for the detection of rays emitted by the radiation source after being attenuated by the scanned object.

[0018] According to a third aspect of the present invention, a medical imaging device includes a scanning frame, a radiation source and a detector; the radiation source and the detector are respectively arranged on the scanning frame, the radiation source is used to emit radiation to the scanning object, and the detector is used to receive the radiation attenuated by the scanning object. The detector is the detector of the second aspect of the present application.

[0019] Additional aspects and advantages of the present invention will be given in part in the following description, and in part will become apparent from the following description, or will be learned through the practice of the present invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] The above and / or additional aspects and advantages of the present invention will become apparent and easily understood from the description of the embodiments in conjunction with the following drawings, in which:

[0021] Figure 1 is a schematic diagram of the positions of the detector and the radiation source in this application;

[0022] Figure 2 is a schematic diagram of the arrangement principle of submodules in the detector module of some embodiments of the present application;

[0023] Figure 3 is a schematic diagram of the detector module structure of some embodiments of the present application;

[0024] Figure 4 is a schematic diagram of pixel arrangement in some embodiments of the present application;

[0025] Figure 5 is a schematic diagram of pixel arrangement in the second submodule in some embodiments of the present application;

[0026] Figure 6 is a schematic diagram of the arrangement of the first submodule and the second submodule in the detector module of some embodiments of the present application;

[0027] Figure 7is a schematic diagram of the arrangement of the first submodule and the second submodule in the detector module of some other embodiments of the present application;

[0028] Figure 8 A schematic diagram of the arrangement of the first submodule and the second submodule in the detector module in some embodiments of the present application;

[0029] Fig. 9 is a schematic diagram of pixel arrangement of a first submodule and a second submodule in a detector module in some embodiments of the present application;

[0030] Fig.10 is a schematic diagram of pixel arrangement of the first submodule and the second submodule in the detector module of some other embodiments of the present application;

[0031] Fig.11 is a schematic diagram of pixel arrangement of the first submodule and the second submodule in the detector module of some other embodiments of the present application;

[0032] Fig.12 It is a schematic diagram of the structure of submodules in some embodiments of the present application;

[0033] Fig.13 is a schematic diagram of pixel arrangement of a first submodule and a second submodule spliced ​​together in a detector module of some embodiments of the present application;

[0034] Fig.14 is another schematic diagram of the detector module structure of some embodiments of the present application;

[0035] Fig.15 is a top view of the detector module structure of some embodiments of the present application;

[0036] Fig.16 is a three-dimensional diagram of the detector module structure of some embodiments of the present application;

[0037] Fig.17 It is a schematic diagram of the structure of medical imaging equipment in some embodiments of the present application.

[0038] Reference numerals:

[0039] Medical imaging equipment 100,

[0040] Detector 10, scanning frame 20, scanning cavity 201, radiation source 30, scanning object 40, scanning bed 50,

[0041] Detector module 101, module support 102, first area S1, second area S2, submodule 103, first submodule 1031, second submodule 1032,

[0042] Pixel 1, scintillator 11, conversion module 12,

[0043] Cable 3, substrate 4, shielding plate 5, circuit board 6, PCB substrate 7. DETAILED DESCRIPTION

[0044] The embodiments of the present invention are described in detail below, and examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present invention, and cannot be understood as limiting the present invention.

[0045] In the description of the present utility model, it is necessary to understand that the terms "length", "width", "thickness", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside" and the like indicate positions or positional relationships based on the positions or positional relationships shown in the accompanying drawings, and are only for the convenience of describing the present utility model and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as a limitation on the present utility model. In addition, features defined as "first" and "second" may explicitly or implicitly include one or more of the features. In the description of the present utility model, unless otherwise specified, "multiple" means two or more.

[0046] In the description of the present invention, it should be noted that, unless otherwise clearly specified and limited, the terms "installation", "connection" and "connection" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection, or it can be indirectly connected through an intermediate medium, or it can be the internal communication of two components. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0047] The detector module 101 is a component unit of the detector 10. Figure 1 As shown, the detector 10 is used to detect the rays emitted by the radiation source 30 after being attenuated by the scanned object 40, so each detector module 101 is also used to detect the rays emitted by the radiation source 30 after being attenuated by the scanned object 40. The detector 10 is not limited to any application device, and can be applied to the medical imaging device 100 or other devices that require scanning imaging.

[0048] For example, the medical imaging device 100 is a CT scanner (CT is the abbreviation of Computed Tomography). With the development of CT scanners, the number of layers of the detector 10 of the CT scanner is increasing. In order to facilitate production and improve the yield rate, the detector 10 is usually divided into dozens of detector modules 101 along the X direction, that is, the channel direction. These detector modules 101 are arranged on a circular arc concentric with the focus. Figure 2 As shown, each detector module 101 is divided into one to dozens of submodules 103 along the Z direction, i.e., the layer arrangement direction, or the rotation axis of the CT scanner, according to the number of required layers. Usually, each submodule 103 has a pixel matrix of 32×6 or 32×32.

[0049] The pixels of the detector submodule 103 determine the minimum image layer thickness that the detector 10 can detect. The thinner the layer thickness, the higher the spatial resolution of the image. Existing medical imaging devices 100 usually use detector submodules 103 with the same or similar pixels. For parts that need to be observed in detail, such as the brain, chest, etc., a smaller layer thickness, such as 1-2 mm, is usually set to obtain a more detailed image. When all submodules 103 in the pixel matrix use low-pixel submodules 103, the image detected by the detector module 101 has low resolution, insufficient clarity, and insufficient image details; for large parts, such as the abdomen, the layer thickness can be set to 5-10 mm to increase the scanning speed and reduce the radiation dose. When all submodules 103 in the pixel matrix are high-pixel, the structure of the detector submodule 103 is complex, the chip size increases exponentially, and the cost is high. If a detector module 101 contains 8 high-pixel detector submodules 103, the cost of the detector module 101 will be very expensive. If the detector 10 has 42 modules, and one module is added with two high-pixel detector submodules 103, the entire detector 10 is added with 84 high-pixel detector submodules 103. This results in high costs and is not conducive to the economic efficiency of the device.

[0050] In order to solve the above problems, refer to Figure 3-Figure 16 A detector module 101 according to an embodiment of the present invention is described.

[0051] like Figure 3 As shown, according to the detector module 101 of the first embodiment of the utility model, the detector module 101 includes a module bracket 102 and a plurality of sub-modules 103. The module bracket 102 is extended along the Z direction. The module bracket 102 plays a supporting and fixing role in the detector module 101, and the plurality of sub-modules 103 are sequentially mounted on the module bracket 102 along the Z direction, and the sub-modules 103 are provided with a plurality of pixels 1 arranged in an array along the X direction and the Z direction.

[0052] Here, the X direction is the arrangement direction of the module bracket 102 , or is called the rotation axis direction of the CT scanner; and the Z direction is the direction extending along the length of the module bracket 102 .

[0053] In some solutions, the pixel 1 on the submodule 103 is a scintillator pixel, such as Fig.12 As shown, the pixel 1 includes a scintillator 11 and a conversion module 12. The scintillator 11 can directly convert X-rays into optical signals, and the optical signals are converted into electrical signals through the conversion module 12. In some solutions, the pixel 1 on the submodule 103 may not contain the scintillator 11. For example, the pixel 1 includes the conversion module 12, and the conversion module 12 directly converts X-rays into electrical signals.

[0054] The plurality of submodules 103 include a first submodule 1031 and a second submodule 1032 . In the Z direction, the size of the pixel 1 of the first submodule 1031 is smaller than the size of the pixel 1 of the second submodule 1032 .

[0055] That is to say, Figure 4 and Figure 5 For example, the Z-direction size m1 of the pixel 1 on the first submodule 1031 is smaller than the Z-direction size m2 of the pixel 1 on the second submodule 1032 . The first submodule 1031 can arrange the pixels 1 more densely in the Z direction relative to the second submodule 1032 .

[0056] Even in some embodiments, in the X direction, the size of the pixel 1 of the first submodule 1031 is smaller than the size of the pixel 1 of the second submodule 1032. The X-direction size n1 of the pixel 1 on the first submodule 1031 is smaller than the X-direction size n2 of the pixel 1 on the second submodule 1032, and the first submodule 1031 can arrange the pixels 1 more densely in the X direction relative to the second submodule 1032.

[0057] This application takes the example of cutting the first submodule 1031 into 32×64=2048 high-density physical pixels and the second submodule 1032 into 16×32=512 ordinary physical pixels for illustration. Of course, in some other embodiments, the first submodule 1031 can also be cut into 2, 4 or other numbers of high-density physical pixels, which will not be repeated here.

[0058] For example, Figure 4 As shown, originally one submodule 103 has 16×32=512 ordinary physical pixels, and this submodule 103 can be used as the second submodule 1032. After cutting an ordinary physical image into 4 high-density physical pixels, as shown in FIG. Figure 5 As shown, the submodule 103 becomes a first submodule 1031 of 32×64=2048 high-density physical pixels.

[0059] This means that the first submodule 1031 has a higher pixel density, while the second submodule 1032 has a lower pixel density, so that the first submodule 1031 can provide a high-definition detection result.

[0060] When the first submodule 1031 is used, it has more high-density physical pixels, which can provide more detailed detection results and is suitable for detection scenarios requiring high resolution, such as detail display in medical imaging. The lower pixel density of the second submodule 1032 can expand the detection range and is suitable for detection scenarios requiring large area coverage, such as full-body scanning.

[0061] By combining the first submodule 1031 and the second submodule 1032, the detector module 101 can provide flexible detection capabilities at different levels. According to actual needs, appropriate submodules 103 can be selected for combination to meet various detection needs. This design not only improves the performance and practicality of the detector 10, but also helps to reduce production costs and improve production efficiency.

[0062] In addition, the design of the first submodule 1031 and the second submodule 1032 can also be adjusted according to actual needs. Figure 6-Figure 8 As shown, the quantity ratio of the first submodule 1031 and the second submodule 1032 can be adjusted according to different application scenarios and user needs to obtain the best detection effect. This flexibility enables the detector module 101 to adapt to different application environments and needs, further improving its practicality and adaptability.

[0063] In general, if Figure 9-11 As shown, the detector module 101 according to the embodiment of the utility model achieves high-definition and large-area coverage detection capabilities by combining sub-modules 103 with different pixel densities, improves the performance of the detector 10, and provides strong technical support for medical imaging and other equipment requiring scanning imaging.

[0064] According to the detector module 101 of some embodiments of the present invention, the number of pixels 1 of the first submodule 1031 is an integer multiple of the number of pixels 1 of the second submodule 1032. This can provide an image with higher resolution and thinner layer thickness.

[0065] Specifically, the integer multiple relationship means that the pixel density of the first submodule 1031 is several times that of the second submodule 1032, thereby providing a higher resolution. In medical imaging, this enables the acquisition of thinner slice images. Thin slice images can better capture the fine structure of tissues and improve the accuracy of diagnosis. This is particularly important for detection scenarios that require high resolution, such as the diagnosis of fine structures such as the heart, brain, or tumors.

[0066] By configuring in this way, the detector module 101 can provide high-definition detection results while maintaining cost-effectiveness. This high-resolution detection capability is not limited to the medical imaging device 100, but can also be applied to other devices that require scanning imaging, such as security inspection equipment, material detection, etc.

[0067] In addition, the design of the first submodule 1031 and the second submodule 1032 can also be adjusted according to actual needs. For example, different numbers of first submodules 1031 and second submodules 1032 are used for splicing on the detector module 101, and the respective numbers are selected according to cost and demand to form the detector module 101. Multiple detector modules 101 constitute the entire detector 10, so that the detector 10 can have different layer thickness combinations and richer parameters. The quantity ratio of the first submodule 1031 and the second submodule 1032 can be adjusted according to different application scenarios and user needs to obtain the best detection effect. In this way, the detector module 101 can adapt to different application environments and needs, further improving its practicality and adaptability.

[0068] In some specific embodiments, Figure 6-Figure 8 As shown, in the Z direction, the module bracket 102 includes a first area S1 located in the middle and a second area S2 located outside the first area S1, the first submodule 1031 is installed on the first area S1, and the second submodule 1032 is installed on the second area S2. In this way, in the entire detector module 101, the first submodule 1031 is arranged in the middle position in the Z direction, and the second submodule 1032 is arranged on both sides in the Z direction. The middle position usually has a larger amount of radiation, so concentrating the first submodule 1031 with a stronger resolution in the middle position in the Z direction is more conducive to improving its utilization.

[0069] In some optional embodiments, such as Figure 6 As shown, a second submodule 1032 may also be installed on the first area S1, and the second submodule 1032 on the first area S1 is located on at least one side of the first submodule 1031. This can further control the cost.

[0070] In some optional embodiments, Figure 7 As shown, only the first submodule 1031 is installed on the first area S1, and only the second submodule 1032 is installed on the second area S2. This strict separation does not allow for assembly errors.

[0071] like Figure 6 , Fig. 9As shown, in some embodiments of the present application, exemplarily, there are 8 sub-module 103 positions in the Z direction of a module bracket 102, the middle four positions are the first area S1, and the two positions on both sides are the second area S2. Two first sub-modules 1031 are in the first area S1, and among the six second sub-modules 1032, two are in the first area S1, and the remaining four are installed in the second area S2. After splicing, the pixels formed along the Z direction are: 3*32 (0.625mm) + 2*64 (0.3125mm) + 3*32 (0.625mm).

[0072] For example, Figure 7 , Fig.10 As shown, among the 8 sub-module 103 positions in the Z direction of a module bracket 102, the middle four positions are the first area S1, and the two positions on both sides are the second area S2. The four first sub-modules 1031 are in the first area S1, and the four second sub-modules 1032 are respectively in the second area S2 on both sides. After splicing, the Z-direction pixels formed are: 2*32 (0.625mm) + 4*64 (0.3125mm) + 2*32 (0.625mm).

[0073] For example, Figure 8 , Fig.11 As shown, among the 8 sub-module 103 positions in the Z direction of a module bracket 102, the middle four positions are the first area S1, and the two positions on both sides are the second area S2. Among the 6 first sub-modules 1031, 4 first sub-modules 1031 are in the first area S1, 2 first sub-modules 1031 are in the second area S2 on both sides, and 2 second sub-modules 1032 are respectively in the second area S2 on both sides. After splicing, the Z-direction pixels are: 1*32 (0.625mm) + 6*64 (0.3125mm) + 1*32 (0.625mm).

[0074] According to the combination of the first submodule 1031 and the second submodule 1032 , a detector module 101 with different pixel combinations can be formed.

[0075] Furthermore, the radius of the target circle tangent to the top surface of the submodule 103 in the first area S1 is smaller than the radius of the target circle tangent to the top surface of the submodule 103 in the second area S2; the center of the target circle is located at the focus of the radiation source 30. In this way, the radiation radiated by the radiation source 30 can be vertically incident on the top surface of the submodule 103 and the tangent point of the target circle. When the signal generated by the submodule 103 is processed later, the correction of the data is easier, which can simplify the data processing process and improve the accuracy of the data results.

[0076] like Figure 6-Figure 8As shown, from the X direction, the height of the submodule 103 in the middle position is not on the same plane as the height of the submodules 103 at the two end positions. This is because, in terms of the distribution of the detector submodules 103 in space, if they are to occupy the entire area of ​​the sphere, the X-direction size of the submodule 103 in the middle position in the Z direction should be larger than the X-direction size of the submodules 103 at the two end positions. On the contrary, if submodules 103 with the same X-direction size are used, the submodule 103 in the middle position in the Z direction has a larger gap in the X direction, and the X-direction size of the middle submodule 103 is increased, which can reduce the size of the X-direction gap.

[0077] Reducing the X-axis gap size can reduce interference and loss during data transmission. By adjusting the height of the submodule 103, the structure of the module bracket 102 is made more compact, and the overall stability and reliability of the detector 10 are improved. By optimizing the arrangement and height of the submodule 103, the detector module 101 can better cope with various scanning imaging tasks and provide more accurate and reliable detection results.

[0078] Optionally, the X-direction dimension of the submodule 103 at the middle position is larger than the X-direction dimension of the submodules 103 at the two side positions, so that the gap between two adjacent submodules 103 in the X-direction can be reduced accordingly.

[0079] Optionally, eight submodules 103 are arranged on each module bracket 102 along the Z direction, but the present invention is not limited thereto.

[0080] The eight submodules 103 are arranged on the same radius with the focus of the tube as the center. The first submodule 1031 is used in the middle part of the module, and the X-direction dimensions of the first and second individual submodules 103 are different. The X-dimension of the middle first submodule 1031 is larger than the X-dimension of the second modules on both sides, which can reduce the gap between two adjacent submodules 103 in the X-direction.

[0081] According to the detector module 101 in some embodiments, the first submodule 1031 is located in the middle of all the submodules 103 , and the size of the first submodule 1031 is an odd number or an even number.

[0082] According to the detector module 101 of some embodiments of the present invention, the submodule 103 further includes a flat cable 3 and a circuit board 6, the flat cable 3 connects a plurality of pixels 1, and the circuit board 6 is mounted on the module bracket 102 and connected to the flat cable 3. Fig.13 As shown, the pixel 1 is the core part of the submodule 103, which is used to receive and convert the ray signal. The wiring 3 is used to transmit the signal collected by the pixel 1 to the circuit board 6 for processing.

[0083] The material and structure of the flat cable 3 can be selected according to actual needs to ensure the stability and reliability of data transmission. This configuration not only simplifies the structure of the detector module 101 and improves production efficiency, but also ensures the accuracy and stability of the detection results. The circuit board 6 is the control system of the detector module 101, which is used to process and transmit data.

[0084] The number of the wiring 3 on the first submodule 1031 is greater than the number of the wiring 3 on the second submodule 1032, so that the first submodule 1031 has a higher data transmission capacity and can process more signals and data. This configuration enables the first submodule 1031 to better process high-resolution and high-definition detection data and provide more accurate detection results.

[0085] By combining the circuit board 6, the flat cable 3 and the submodule 103, the data processing capability, transmission capability and detection capability of the detector module 101 are improved, and the performance and practicality of the detector 10 are further improved, providing more reliable and efficient technical support for medical imaging and other equipment requiring scanning imaging.

[0086] In some embodiments, Fig.12 As shown, the submodule 103 further includes a substrate 4 , a shielding plate 5 and a PCB substrate 7 .

[0087] The pixel 1 is located on one side of the substrate 4, the shielding plate 5 is located on the other side of the substrate 4, and the circuit board 6 is located on the side of the shielding plate 5 away from the pixel 1. The projection of the corresponding circuit board 6 along the Y direction is located within the projection range of the shielding plate 5 along the Y direction, so that when the human eye is on the side of the shielding plate 5 away from the circuit board 6 and observes along the Y direction, the corresponding circuit board 6 cannot be seen due to the shielding of the circuit board 6 by the shielding plate 5. Therefore, when the submodule 103 is used in the medical imaging device 100, the shielding plate 5 can protect the circuit board 6 from the influence of the radiation source 30 of the medical imaging device 100.

[0088] Alternatively, if Fig.13 As shown, the number of pixels 1 of the first submodule 1031 is N times the number of pixels 1 of the second submodule 1032 , and the number of wiring lines 3 of the first submodule 1031 is also N times the number of wiring lines 3 of the second submodule 1032 .

[0089] When the value of N is large, the data processing and transmission capabilities of the first submodule 1031 are stronger, and a large amount of detection data can be better processed. This enables the first submodule 1031 to provide clearer and more accurate images in medical imaging and other equipment that requires scanning imaging, thereby improving the accuracy and reliability of diagnosis.

[0090] This also makes the data transmission between the first submodule 1031 and the second submodule 1032 more balanced, reduces the risk of data congestion and transmission delay, and helps to improve the overall performance and stability of the detector 10.

[0091] In general, the detector module 101 achieves detection capabilities of high resolution, high definition, and efficient data processing through the proportional relationship between the pixel 1 size and the number of wiring lines 3 between the first submodule 1031 and the second submodule 1032. This not only improves the performance, practicality, and production efficiency of the detector 10, but also provides more reliable and efficient technical support for medical imaging and other equipment that requires scanning imaging.

[0092] In some embodiments, at least two flat cables 3 are sequentially arranged along the X direction on the first submodule 1031. The circuit board corresponds to the flat cables 3 one by one, and the circuit board is located on the side of the flat cables 3 in the X direction. This ensures that the process of data transmission from the flat cables 3 to the circuit board is smoother, reducing the risk of transmission delay and data loss.

[0093] like Fig.14 As shown, the detector 10 according to the embodiment of the second aspect of the utility model includes a housing and a plurality of detector modules 101, and the plurality of detector modules 101 are arranged side by side along the X direction. In the present application, the housing can adopt a known solution in the prior art, and the housing itself is not the core point of the present application, so it is not described here. The detector module 101 is the detector module 101 in the embodiment of the first aspect of the present application.

[0094] like Fig.17 As shown, according to the medical imaging device 100 of the embodiment of the third aspect of the utility model, the medical imaging device 100 includes a scanning frame 20, a radiation source 30 and the detector 10 of the above embodiment.

[0095] The radiation source 30 and the detector 10 are respectively arranged on the scanning frame 20, the radiation source 30 is used to emit radiation to the scanning object 40, and the detector 10 is used to receive the radiation attenuated by the scanning object 40. When the scanning frame 20 rotates around the Z axis, the radiation source 30 and the detector 10 both rotate synchronously with the scanning frame 20, and always maintain radially opposite positions, so that the detector 10 can receive the radiation, such as X-rays, emitted by the radiation source 30 and passing through the scanning object 40. Therefore, since the resolution of the detector 10 is improved, it is beneficial to improve the imaging effect of the medical imaging device 100.

[0096] The structure of the scanning frame 20 is not limited. For example, the scanning frame 20 forms a scanning cavity 201 for receiving the scanning object 40, and the radiation source 30 and the detector 10 are respectively arranged on both sides of the scanning cavity 201 in the radial direction.

[0097] Exemplarily, in addition to the above-mentioned structure, the medical imaging device 100 may also include a scanning bed 50 for carrying the scanning object 40. Of course, the present invention is not limited to this. For example, when the Z direction is vertical, the scanning bed 50 may not be needed. The patient can stand vertically, and the scanning frame 20 moves up and down while rotating around the Z axis to scan the patient. It will not be elaborated here.

[0098] Below, refer to the attached Figure 12-16 , describing a detector module 101 according to a specific embodiment of the present application.

[0099] Reference Fig.14 The detector module 101 includes a module bracket 102 and a plurality of submodules 103 .

[0100] The module bracket 102 is extended along the Z direction.

[0101] Multiple submodules 103 are sequentially mounted on the module bracket 102 along the Z direction, referring to Fig.13 , the submodule 103 is provided with a plurality of pixels 1 arranged in an array along the X direction and the Z direction. The plurality of submodules 103 include a first submodule 1031 and a second submodule 1032, the Z-direction size m1 of the pixel 1 of the first submodule 1031 is smaller than the Z-direction size m2 of the pixel 1 of the second submodule 1032, and the X-direction size n1 of the pixel 1 of the first submodule 1031 is smaller than the X-direction size n2 of the pixel 1 of the second submodule 1032. Fig.13 , wherein the number of pixels 1 of the first submodule 1031 is an integer multiple of the number of pixels 1 of the second submodule 1032 .

[0102] Reference Fig.12 The submodule 103 includes a pixel 1, a wiring 3, a substrate 4, a shielding plate 5, a circuit board 6 and a PCB substrate 7.

[0103] The circuit board 6 is disposed on one side of the base plate 4 and mounted on the module bracket 102 .

[0104] The pixel 1 is arranged on one side of the substrate 4, and the shielding plate 5 is arranged on the other side of the substrate 4. The shielding plate 5 is located between the circuit board 6 and the substrate 4, and the projection of the corresponding circuit board 6 along the Y direction is located within the projection range of the shielding plate 5 along the Y direction.

[0105] One end of the wiring 3 of each submodule 103 is connected to a plurality of pixels 1, and the other end is connected to the circuit board 6. The number of wirings 3 on the first submodule 1031 is greater than the number of wirings 3 on the second submodule 1032.

[0106] At least two cables 3 are arranged in sequence along the X direction on the first submodule 1031 .

[0107] The circuit board 6 corresponds to the flat cable 3 one by one, and the circuit board 6 is located on one side of the flat cable 3 in the X direction.

[0108] Among all submodules 103 , the radius of the target circle tangent to the top surface of the submodule 103 at the middle position is smaller than the radius of the target circle tangent to the top surface of the submodule 103 at the two end positions on the module bracket 102 ; the center of the target circle is located at the focus of the radiation source 30 .

[0109] The X-dimension of the submodule 103 at the middle position is greater than the X-dimension of the submodules 103 at the two side positions.

[0110] Reference Figure 15-16 , the first submodule 1031 is located in the middle of all submodules 103, and there are four of them.

[0111] Other components of the detector module 101 according to the embodiment of the present invention, such as the detector 10 and the medical imaging device 100, and operations thereof are known to those skilled in the art and will not be described in detail herein.

[0112] In the description of this specification, the description with reference to the terms "embodiment", "example", etc. means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the utility model. In this specification, the schematic representation of the above terms does not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in any one or more embodiments or examples in a suitable manner.

[0113] Although the embodiments of the present invention have been shown and described, those skilled in the art will appreciate that various changes, modifications, substitutions and variations may be made to the embodiments without departing from the principles and spirit of the present invention, and that the scope of the present invention is defined by the claims and their equivalents.

Claims

1. A detector module for detecting radiation emitted by a radiation source after being attenuated by a scanned object, characterized in that: include: A module bracket, wherein the module bracket is extended along the Z direction; A plurality of submodules, wherein the plurality of submodules are sequentially mounted on the module bracket along the Z direction, and the submodules are provided with a plurality of pixels arranged in an array along the X direction and the Z direction; The plurality of submodules include a first submodule and a second submodule. In the Z direction, the size of the pixel of the first submodule is smaller than the size of the pixel of the second submodule.

2. The detector module according to claim 1, characterized in that The number of the pixels of the first submodule is an integer multiple of the number of the pixels of the second submodule.

3. The detector module according to claim 1, characterized in that The submodule also includes: A wiring line, wherein the wiring line connects a plurality of the pixels; A circuit board, which is mounted on the module bracket and connected to the flat cable; The number of the wiring harnesses on the first submodule is greater than the number of the wiring harnesses on the second submodule.

4. The detector module according to claim 3, characterized in that At least two of the cables are arranged in sequence along the X direction on the first submodule; The circuit boards correspond to the flat cables one by one, and the circuit boards are located on one side of the flat cables in the X direction.

5. The detector module according to claim 1, characterized in that In the X direction, the size of the pixel of the first submodule is smaller than the size of the pixel of the second submodule.

6. The detector module according to any one of claims 1 to 5, characterized in that: In the Z direction, the module bracket includes a first area located in the middle and a second area located outside the first area, the first submodule is installed on the first area, and the second submodule is installed on the second area.

7. The detector module according to claim 6, characterized in that The second submodule is also installed on the first area, and the second submodule on the first area is located on at least one side of the first submodule.

8. The detector module according to claim 6, characterized in that The radius of the target circle tangent to the top surface of the submodule in the first area is smaller than the radius of the target circle tangent to the top surface of the submodule in the second area; the center of the target circle is located at the focus of the radiation source.

9. The detector module according to any one of claims 1 to 5, characterized in that: The X-dimension of the submodule at the middle position is greater than the X-dimension of the submodule at the two side positions.

10. A detector, characterized in that: The invention comprises a housing and a plurality of detector modules according to any one of claims 1 to 9, wherein the plurality of detector modules are arranged side by side along the X direction.

11. A medical imaging device, characterized in that: comprising a scanning frame, a radiation source and a detector according to any one of claims 10; The radiation source and the detector are respectively arranged on the scanning frame, the radiation source is used to emit radiation to the scanning object, and the detector is used to receive the radiation attenuated by the scanning object.

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