Medical imaging system and CT detection components thereof

Abstract

The utility model provides a medical imaging system and a CT detection component thereof, wherein the CT detection component comprises a detector ring and an anti-scattering component; the anti-scattering component is in the form of a sheet, and is arranged on the inner side of the detector ring, and is perpendicular to the axial direction of the detector ring; a plurality of anti-scattering components are arranged in sequence along the axial direction of the detector ring, and at least some of the two adjacent anti-scattering components have a gap between them. In this way, the utility model can not only reduce the interference of scattered rays on the imaging quality of the medical imaging system through the anti-scattering component, but also the arrangement of the anti-scattering component can ensure that the rays received by the detector units at different positions on the detector ring will not be largely blocked by the anti-scattering component, thereby ensuring that the detector units at the same position on the detector ring can have a sufficient dose of rays to reconstruct the image.

Description

Technical Field

[0001] The utility model relates to the technical field of medical equipment, in particular to a medical imaging system and a CT detection component. Background Art

[0002] In traditional CT systems (i.e., third-generation CT systems), the tube and the detector work together to detect radiation on the patient. Specifically, the radiation emitted by the tube passes through the patient's scanned area and is detected and received by the detector, which generates radiation attenuation information of the scanned area. During the entire CT examination process, the tube and the detector rotate synchronously around the center of the scanning hole, and the tube and the detector remain relatively stationary during the rotation process, so as to obtain radiation attenuation information of the scanned area at different angles.

[0003] After the radiation emitted by the tube hits the patient's scanned area, part of the radiation is absorbed by the scanned area, another part of the radiation will pass through the scanned area and be received by the detector, and another part of the radiation will interact with the scanned area to produce scattered radiation. The intensity, frequency and direction of the scattered radiation are different from those originally radiated by the tube. Since the direction of the scattered radiation is random, it is easy to be received by the detector, which seriously affects the imaging quality. In order to reduce the interference of the scattered radiation on the imaging, an anti-scatter grid (Anit-Scatter Grid, ASG) is designed in the third-generation CT system to reduce the proportion of scattered radiation reaching the detector. The ASG is set on the detector, and multiple ASGs are arranged in sequence along the circumference of the scanning hole. The ASG is usually parallel to the axial direction of the scanning hole and extends along the radial direction of the scanning hole.

[0004] However, in the fourth-generation CT system (also known as static CT), the focus of the detector and the tube are distributed in a ring throughout the scanning bore of the scanning frame. During the scanning process, the detector will receive rays emitted from the focus of the tube at different positions, which is different from the scanning method of the third-generation CT. At present, there is no better solution for suppressing scattered rays in static CT systems. Some manufacturers have adopted the solution for suppressing scattered rays in the third-generation CT, that is, arranging multiple ASGs in sequence along the circumference of the scanning bore, and the ASGs are parallel to the axial direction of the scanning bore and extend radially along the scanning bore. However, in actual application scenarios, since the annularly arranged detectors and the annularly arranged tube focus will not rotate and remain stationary, when the tube focus at different angles emits rays, the corresponding ASG set at the same detector will block most of the rays, resulting in insufficient radiation dose received by the detector, and thus the inability to reconstruct the image.

[0005] In summary, designing a scattered ray suppression scheme in the 4th generation CT system by referring to the scattered ray suppression scheme in the 3rd generation CT system will result in insufficient radiation dose received by the same detector and thus failure to image. Therefore, it is necessary to propose a scattered ray suppression scheme for the 4th generation CT system (static CT system) so as to achieve the purpose of reducing the interference of scattered rays while allowing the detector to receive a sufficient dose of radiation to ensure imaging. Utility Model Content

[0006] The utility model provides a medical imaging system and a CT detection component thereof, aiming to reduce the interference of scattered rays on the static CT system so that sufficient doses of rays of the static CT system can be detected to ensure that images can be reconstructed.

[0007] In order to solve the above technical problems, based on one aspect of the utility model, the utility model provides a CT detection assembly, which includes a detector ring and an anti-scattering member;

[0008] The anti-scattering component is in sheet shape and is arranged on the inner side of the detector ring. The anti-scattering component is perpendicular to the axial direction of the detector ring. A plurality of anti-scattering components are arranged in sequence along the axial direction of the detector ring, and there is a gap between at least two adjacent anti-scattering components.

[0009] Optionally, the anti-scattering member is in the shape of an annular sheet, the inner side of the anti-scattering member is circular or regular polygonal, and the anti-scattering member and the detector ring are coaxially arranged.

[0010] Optionally, a plurality of anti-scattering elements are evenly spaced along the axial direction of the detector ring.

[0011] Optionally, inner sides of at least two anti-scattering elements overlap along the axial direction of the detector ring.

[0012] Optionally, the anti-scattering element includes a plurality of anti-scattering substrates arranged in a ring shape.

[0013] Optionally, the anti-scatter substrate is perpendicular to the axial direction of the detector ring.

[0014] Optionally, the anti-scattering substrate is fan-shaped.

[0015] Optionally, the anti-scattering substrate is rectangular, trapezoidal or parallelogram.

[0016] Optionally, the multiple anti-scattering substrates of the anti-scattering element are integrally formed.

[0017] Optionally, the CT detection assembly also includes an inner fixing structure and an outer fixing structure, the outer fixing structure is installed on the inner side of the detector ring, the outer sides of all the anti-scattering parts are fixed on the outer fixing structure, and the inner sides of all the anti-scattering parts are fixedly connected to the inner fixing structure; the inner fixing structure and the outer fixing structure are both used for allowing rays to pass through.

[0018] Optionally, the anti-scatter substrates of all the anti-scatter components correspond one-to-one in the axial direction of the detector ring, and multiple anti-scatter substrates corresponding in the axial direction of the detector ring form a group of anti-scatter units, the inner fixed structure includes multiple inner mounting plates corresponding one-to-one to the anti-scatter units, and the outer fixed structure includes multiple outer mounting plates corresponding one-to-one to the anti-scatter units, and all the anti-scatter substrates in the same group of anti-scatter units are fixedly connected to the corresponding inner mounting plates and the outer mounting plates.

[0019] Optionally, the detector ring includes a plurality of detector units arranged in a ring shape, the detector units correspond to the anti-scatter units one by one, and the corresponding detector units are fixedly connected to the outer mounting plates corresponding to the anti-scatter units.

[0020] Optionally, the detector unit includes a plurality of detector crystals, wherein the detector crystals extend along the axial direction of the detector ring, and the detector crystals are used to receive high-energy photon signals and convert the photon signals into low-energy visible light signals.

[0021] Optionally, the detector crystal is a scintillator.

[0022] In order to solve the above technical problems, based on another aspect of the present invention, the present invention also provides a medical imaging system, which includes:

[0023] Tube focus ring;

[0024] As described above, the detector ring of the CT detection assembly and the focus ring of the tube are coaxially arranged.

[0025] Optionally, the medical imaging system further comprises a scanning frame having a scanning hole, the detector ring and the tube focus ring are both mounted on the scanning frame, and the detector ring is coaxial with the scanning hole.

[0026] Optionally, the number of the CT detection components is at least two, and they are arranged in sequence along the axial direction of the scanning hole; the number of the tube focus ring is at least one.

[0027] Optionally, the center point of at least one of the tube focus rings coincides with the center point of at least one of the detector rings.

[0028] In order to solve the above technical problems, based on another aspect of the present invention, the present invention further provides a medical imaging system, which includes:

[0029] Tube focus ring;

[0030] A detector ring is coaxially arranged with the tube focal ring, the detector ring comprising a plurality of detector units distributed along the circumferential direction, each of the detector units extending along the axial direction of the detector ring;

[0031] A plurality of anti-scattering parts are arranged on the inner side of the detector ring, and the plurality of anti-scattering parts are arranged in sequence along the extension direction of the detector unit, and an X-ray channel is formed between adjacent anti-scattering parts to allow X-rays to pass through the X-ray channel to reach the detector ring.

[0032] Optionally, the anti-scattering element is in a sheet shape and is perpendicular to the axial direction of the detector ring.

[0033] In summary, in the medical imaging system and CT detection assembly thereof provided by the utility model, the CT detection assembly includes a detector ring and an anti-scattering member; the anti-scattering member is in the form of a sheet, the anti-scattering member is arranged on the inner side of the detector ring, the anti-scattering member is perpendicular to the axial direction of the detector ring, a plurality of anti-scattering members are arranged in sequence along the axial direction of the detector ring, and at least part of two adjacent anti-scattering members have a gap. Such a configuration can ensure that the CT detection assembly is assembled in the medical imaging system, the anti-scattering member is perpendicular to the scanning hole of the medical imaging system, and a plurality of anti-scattering members are arranged along the axial direction of the scanning hole, the rays emitted from the focus at any position on the focus ring of the tube will not be largely blocked by the anti-scattering member, and the dose of rays received by the detector ring can ensure the reconstruction of the image. In this way, the utility model can not only reduce the interference of scattered rays on the imaging quality of the medical imaging system through the anti-scattering member, but also the arrangement of the anti-scattering member can ensure that the rays received by the detector units at different positions on the detector ring will not be largely blocked by the anti-scattering member, thereby ensuring that the detector units at the same angle position on the detector ring can have sufficient doses of rays to reconstruct the image.

[0034] It should be noted that, since the medical imaging system includes the CT detection component, it also has the beneficial technical effects brought by the CT detection component, which will not be repeated here. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] Those skilled in the art should understand that the drawings provided are for a better understanding of the present invention and do not constitute any limitation on the scope of the present invention.

[0036] Figure 1 is a schematic diagram of a third generation CT system in the prior art;

[0037] Figure 2 It is a working principle diagram of the third generation CT system in the prior art;

[0038] Figure 3 is a schematic diagram of a scattered ray suppression solution in a third generation CT system in the prior art;

[0039] Figure 4 is a schematic diagram of a solution for suppressing scattered rays of a detector unit in a third generation CT system in the prior art;

[0040] Figure 5 It is a front view of a 4th generation CT system in the prior art;

[0041] Figure 6 is a schematic diagram of a scattered ray suppression solution in a 4th generation CT system in the prior art;

[0042] Figure 7 It is a front view of a CT detection assembly according to an embodiment of the utility model;

[0043] Figure 8 It is a schematic diagram of an anti-scattering substrate in one embodiment of the utility model being arranged on the inner circumference of a detector ring;

[0044] Fig. 9 It is a schematic diagram of an anti-scattering substrate of different anti-scattering members of an embodiment of the utility model being arranged on a detector unit;

[0045] Fig.10 It is a schematic diagram of an anti-scattering unit, an inner mounting plate and an outer mounting plate according to an embodiment of the utility model.

[0046] In the attached figure:

[0047] 10-scanning rack; 11-scanning hole; 20-tube; 30-detector; 31-detector unit; 310-detector crystal; 40-scanning bed; 50-subject;

[0048] 60 - detector ring; 70 - anti-scattering element; 71 - anti-scattering substrate; 710 - anti-scattering unit; 80 - tube focus ring; 81 - tube focus; 91 - inner mounting plate; 92 - outer mounting plate. DETAILED DESCRIPTION

[0049] In order to make the purpose, advantages and features of the utility model clearer, the utility model is further described in detail below in conjunction with the accompanying drawings and specific embodiments. It should be noted that the drawings are all in a very simplified form and are not drawn to scale, and are only used to conveniently and clearly assist in explaining the purpose of the embodiments of the utility model. In addition, the structure shown in the drawings is often a part of the actual structure. In particular, the emphasis of each drawing is different, and sometimes different scales are used.

[0050] As used in the present invention, the singular forms "one", "an" and "the" include plural objects, the term "or" is usually used to include the meaning of "and / or", the term "several" is usually used to include the meaning of "at least one", and the term "at least two" is usually used to include the meaning of "two or more". In addition, the terms "first", "second" and "third" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Therefore, the features defined as "first", "second" and "third" may explicitly or implicitly include one or at least two of the features, "one end" and "the other end" and "the proximal end" and "the distal end" generally refer to two corresponding parts, which not only include the endpoints, and the terms "installed", "connected" and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral one; it can be a mechanical connection or an electrical connection; it can be directly connected or indirectly connected through an intermediate medium, it can be the internal connection of two elements or the interaction relationship between two elements. In addition, as used in the present invention, an element disposed on another element generally only indicates that there is a connection, coupling, cooperation or transmission relationship between the two elements, and the connection, coupling, cooperation or transmission between the two elements may be direct or indirect through an intermediate element, and cannot be understood as indicating or implying the spatial position relationship between the two elements, that is, an element may be in any orientation such as inside, outside, above, below or on one side of another element, unless otherwise clearly indicated in the content. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0051] Figure 1 It is a schematic diagram of the third generation CT (Computed Tomography) system in the prior art. Figure 2 This is a working principle diagram of the third generation CT system in the prior art. Figure 1 and Figure 2As shown, the third generation CT system at least includes a scanning gantry 10, a tube 20, a detector 30 and a scanning bed 40. The tube 20 and the detector 30 are the core components of scanning and imaging in the CT system. The focus of the tube 20 emits electron rays (usually X-rays), which pass through the subject 50 and are received by the detector 30. With the cooperation of the tube 20 and the detector 30, the subject 50 is subjected to a radiographic scanning inspection; the scanning gantry 10 is a mechanical bearing structure for installing the tube 20 and the detector 30. The scanning gantry 10 has a scanning hole 11, and the tube 20 and the detector 30 are symmetrically mounted on both radial sides of the scanning hole 11; the scanning bed 40 is a carrier for carrying the subject 50 (the subject 50 is, for example, a patient) in and out of the scanning hole 11. In actual application scenarios, the subject 50 lies flat on the scanning bed 40. As the scanning bed 40 enters the scanning hole 11, the scanning gantry 10 synchronously drives the tube 20 and the detector 30 to rotate (specifically, circular motion around the central axis of the scanning hole 11), thereby performing a spiral scan on the subject 50 to collect the attenuation information of the rays of the scanning part of the subject 50 at different angles. This is the imaging scanning process of the third-generation CT system.

[0052] Figure 3 is a schematic diagram of a solution for suppressing scattered rays in a third-generation CT system in the prior art. Figure 4 Schematic diagram of a solution for suppressing scattered rays of a detector unit in a third generation CT system in the prior art. Figure 3 After the electron beam emitted by the tube 20 passes through the subject 50, a portion of the electron beam will be absorbed by the subject 50, another portion of the electron beam will pass through the subject 50 and be received by the detector 30, and another portion of the electron beam will interact with the subject 50 to form scattered beams with different intensity, frequency and direction from the electron beam radiated by the emission source. The scattered beams may be absorbed by the detector 30, thereby affecting the imaging quality. For further information, see Figure 3 The detector 30 includes a plurality of detector units 31 arranged along the circumference of the scanning hole 11, and the plurality of detector units 31 are arranged in an arc shape. For the suppression scheme of scattered rays in the third generation CT, one suppression scheme is generally: a plurality of anti-scatter grids (ASGs) are arranged in an arc shape along the circumference of the scanning hole 11, and the anti-scatter grids are in the form of sheets, the ASGs are parallel to the axial direction of the scanning hole 11, and the extension line of the ASGs passes through the focus of the tube 20. Specifically, see Figure 4Each detector unit 31 includes a plurality of detector crystals 310 arranged along the circumference of the scanning hole 11. The detector crystals 310 here may be scintillation crystals. The detector crystals 310 extend along the axial direction of the scanning hole 11. The detector crystals 310 may receive high-energy photon signals (ray signals emitted by the tube 20) and convert the photon signals into low-energy visible light signals. Detector crystals 310 are arranged on both sides of each detector crystal 310. In this way, as much scattered rays as possible can be absorbed under the action of the ASG, and the dose of scattered rays received by the detector crystals 310 is reduced, thereby ensuring the imaging quality.

[0053] Figure 5 1 is a front view of a 4th generation CT system in the prior art (a schematic diagram along the axial direction of the scanning hole 11). Figure 5 As shown, and in conjunction with Figure 1The fourth generation CT system includes a detector ring 60 and a tube focus ring 80 both mounted on the scanning gantry 10. The detector ring 60 can be understood as a plurality of detector units 31 arranged in a ring shape (arranged in a circle along the circumference of the scanning hole 11). As mentioned above, each detector unit 31 includes a plurality of detector crystals 310 arranged in sequence. The tube focus ring 80 can be understood as a plurality of tube foci 81 arranged in a ring shape (arranged in a circle along the circumference of the scanning hole 11). Each tube focus 81 can emit electron rays. Furthermore, the detector ring 60, the tube focus ring 80 and the scanning hole 11 are coaxially arranged. There is no restriction on the axial position of the detector ring 60 and the tube focus ring 80 along the scanning hole 11. Preferably, the center point of the detector ring 60 may coincide with the center point of the tube focus ring 80, so that the axial position of the detector ring 60 along the scanning hole 11 is substantially the same as the axial position of the tube focus ring 80 along the scanning hole 11. In other words, the center of the detector ring 60 is concentric with the center of the tube focus ring 80. In some other embodiments, the center of the tube focus ring 80 and the center of the detector ring 60 may be staggered along the axial direction of the scanning hole 11. In addition, there is no restriction on the number of detector rings 60 and the number of tube focus rings 80. For example, both are multiple and arranged along the axial direction of the scanning hole 11. In addition, a predetermined number (such as one, two, three, etc.) of tube focus rings 80 may be arranged between two adjacent detector rings 60, or a predetermined number (such as one, two, three, etc.) of detector rings 60 may be arranged between two adjacent tube focus rings 80, or the detector rings 60 and the tube focus rings 80 may be arranged staggered in sequence along the axial direction of the scanning hole 11, that is, one tube focus ring 80 is arranged between two adjacent detector rings 60, and one detector ring 60 is arranged between two adjacent tube focus rings 80. In addition, for a plurality of tube focus points 81 on a single tube focus ring 80, or a total tube focus point 81 of a plurality of tube focus rings 80, a single tube 20 (ray source) may be configured with all the tube focus points 81, or a plurality of tubes 20 may be configured with the total tube focus point 81, or one tube 20 may be configured with all the tube focus points 81 of a tube focus ring 80.

[0054] It should be noted that the present embodiment does not limit the shapes of the detector ring 60, the tube focus ring 80, and the scanning hole 11. Taking the detector ring 60 as an example, the detector ring 60 may be in a circular ring shape or a polygonal ring shape (e.g., a regular octagon). The tube focus ring 80 may be located inside the detector ring 60, or outside the detector ring 60, or the tube focus ring 80 and the detector ring 60 may be arranged on the same cylindrical body along the axial direction of the scanning hole 11.

[0055] Different from the third generation CT system, based on the structure of the fourth generation CT system, each detector unit 31 in the detector ring 60 in the fourth generation CT system can receive electron rays (specifically X-rays) emitted from different tube focal points 81. Different from the spiral scanning method in the third generation CT system, during the scanning process of the fourth generation CT system, the relative positions of the detector ring 60 and the tube focal ring 80 are fixed, and the scanning gantry 10 is also fixed, that is, the scanning gantry 10 will not drive the tube focal ring 80 and the detector ring 60 to rotate. The fourth generation CT is also called static CT.

[0056] During the scanning process of the 4th generation CT system, scattered rays are generated, which affect the imaging scanning results, for example, the contrast-to-noise ratio of the generated medical image. Figure 6 is a schematic diagram of a scattered ray suppression scheme in a 4th generation CT system in the prior art. Currently, some manufacturers have applied the scattered ray suppression scheme of the 3rd generation CT system to the 4th generation CT system. Specifically, see Figure 6 , multiple ASGs are sequentially arranged on the inner side of the detector ring 60 along the circumference of the detector ring 60, and the ASGs are parallel to the axial direction of the detector ring 60, and the ASGs extend along the radial direction of the detector ring 60. Specifically, ASGs are arranged on both sides of each detector crystal 310 of each detector unit 31. However, in actual application scenarios, since the scanning gantry 10 remains stationary, it will not drive the rotating detector ring 60 and the tube focus ring 80 to rotate. When the tube focus 81 at different angular positions emits rays, the ASGs corresponding to the detector unit 31 at the same angular position will block most of the rays, resulting in the radiation dose obtained by the detector unit 31 being insufficient for image reconstruction.

[0057] In view of this, an embodiment of the present invention proposes a CT detection component applied to a medical imaging system (the medical imaging system here is a static CT system) to reduce the interference of scattered rays on the static CT system so that a sufficient dose of rays can be detected in the static CT system to ensure that the image can be reconstructed.

[0058] Figure 7 1 is a front view of a CT detection assembly according to an embodiment of the present invention (a schematic diagram along the axial direction of the detector ring). Figure 7The CT detection assembly of this embodiment includes an anti-scattering member 70 and a detector ring 60. The detector ring here is the detector ring 60 that matches the tube focus ring 80 in the static CT system mentioned above. The detector ring 60 is installed on the scanning gantry 10 and is coaxial with the scanning hole 11 of the scanning gantry 10. The anti-scattering member 70 can absorb the electron rays (i.e., X-rays) emitted by the tube focus ring 80, and thus can also absorb the scattered rays formed by the electron rays. For example, the material of the anti-scattering member 70 is lead, tungsten or other materials that can absorb a large amount of X-ray beams. The anti-scattering member 70 is in the form of a sheet and is arranged on the inner side of the detector ring 60. The anti-scattering member 70 is perpendicular to the axial direction of the detector ring 60. In this way, the anti-scattering member 70 is also perpendicular to the axial direction of the scanning hole 11, and the anti-scattering member 70 is perpendicular to the detector crystal 310. In one embodiment, the anti-scattering member 70 is in the shape of an annular sheet, and the outer side of the anti-scattering member 70 is located on the inner side of the detector ring 60, that is, the anti-scattering member 70 is arranged on the detection surface on the inner side of the detector ring 60. Multiple anti-scattering members 70 are sequentially arranged on the inner side of the detector ring 60 along the axial direction of the detector ring 60, and there is a gap between at least two adjacent anti-scattering members 70. Specifically, multiple anti-scattering members 70 can be evenly arranged on the inner side of the detector ring 60 along the axial direction of the detector ring 60, or some adjacent anti-scattering members 70 can be stacked together, such as three adjacent anti-scattering members 70 are stacked together, and there is a gap between the anti-scattering members 70 on both sides of the axial direction. It can be understood by those skilled in the art that this gap serves as an X-ray channel, so that after the X-ray passes through the patient and passes through the X-ray channel, it reaches the inner detection surface of the detector ring 60, and the anti-scattering members 70 on both sides can absorb the scattered rays. Preferably, the inner sides of at least two anti-scattering members 70 overlap along the axial direction of the detector ring 60, that is, the inner sides of at least two anti-scattering members 70 have the same shape and size and are coaxially arranged. Preferably, the inner sides of all anti-scattering members 70 overlap along the axial direction of the detector ring 60. This embodiment does not limit the shape of the inner side of the annular anti-scattering member 70, which is preferably circular or regular polygonal and coaxially arranged with the detector ring 60. Preferably, the inner side of the anti-scattering member 70, the detector ring 60 and the scanning hole 11 have the same shape, such as circular. The number of CT detection components is at least two, and they are arranged in sequence along the axial direction of the scanning hole 11, and the number of detector rings 60 is at least two, and they are arranged in sequence along the axial direction of the scanning hole 11.

[0059] Thus, compared with the solution of applying the suppression method of scattered rays of the third generation CT system to the static CT system, after the CT detection assembly of this embodiment is assembled in the medical imaging system, the anti-scattering member 70 is perpendicular to the scanning hole 11 of the medical imaging system, and the multiple anti-scattering members 70 are arranged along the axial direction of the scanning hole 11, and the rays emitted from the focus 81 of the tube at any position on the focus ring 80 of the tube will not be largely blocked by the anti-scattering member 70, and the dose of rays received by the detector ring 60 can ensure the reconstruction of the image. The utility model not only reduces the interference of scattered rays on the imaging quality of the medical imaging system through the anti-scattering member 70, but also the arrangement of the anti-scattering member 70 can ensure that the rays received at different angular positions on the detector ring 60 (i.e., the detector units 31 at different positions) will not be largely blocked by the anti-scattering member 70, thereby ensuring that the detection units 31 at the same angular position on the detector ring 60 can receive sufficient doses of rays to reconstruct the image.

[0060] Figure 8 This is a schematic diagram of an anti-scattering substrate in an embodiment of the utility model being arranged on the inner circumference of a detector ring. Fig. 9 FIG. 1 is a schematic diagram of an anti-scattering substrate of a different anti-scattering member of an embodiment of the present invention being arranged on a detector unit. Figure 8 Houhe Fig. 9 The anti-scattering component 70 includes a plurality of anti-scattering substrates 71 arranged in a ring shape. The anti-scattering substrate 71 here may be specifically the ASG mentioned above, that is, a sheet-shaped anti-scattering grid. The anti-scattering substrate 71 is perpendicular to the axial direction of the detector ring 60, and the anti-scattering substrate 71 is perpendicular to the detector crystal 310. In some other embodiments, the anti-scattering substrate 71 may not be perpendicular to the axial direction of the detector ring 30, and the angle between the two may be, for example, 75°, 80°, or 85°. Usually, each anti-scattering substrate 71 is separated from each other and can be independently disassembled and assembled on the detection surface on the inner side of the detector ring 60, which is convenient for maintenance and replacement. In some other embodiments, the anti-scattering component 70 may be formed by integrally manufacturing a plurality of anti-scattering substrates 71.

[0061] Preferably, the anti-scatter substrate 71 is fan-shaped to ensure that two adjacent anti-scatter substrates 71 can be closely attached to each other, and there is no gap between two adjacent anti-scatter substrates 71 as much as possible, thereby further increasing the absorption range of scattered rays by the anti-scatter element 70. In some other embodiments, the anti-scatter substrate 71 can also be other shapes, such as the anti-scatter substrate 71 can also be rectangular, trapezoidal or parallelogram.

[0062] Regarding the installation method of the anti-scattering component 70, the CT detection assembly of this embodiment also includes an inner fixing structure and an outer fixing structure. The outer fixing structure is installed on the inner side of the detector ring 60. The outer sides of all anti-scattering components 70 are fixed to the outer fixing structure. The inner sides of all anti-scattering components 70 are fixedly connected to the inner fixing structure, that is, the anti-scattering substrates 71 of all anti-scattering components 70 are connected to the inner fixing structure and the outer fixing structure. Both the inner fixing structure and the outer fixing structure can allow rays to pass through. The materials of the inner fixing structure and the materials of the outer fixing structure are, for example, carbon fiber. In this way, all anti-scattering substrates 71 can be installed on the inner side of the detector ring 60 through the outer fixing structure, and the inner fixing structure can further fix each anti-scattering substrate 71 to improve the overall stability.

[0063] Fig.10 Schematic diagram of an anti-scattering unit, an inner mounting plate and an outer mounting plate according to an embodiment of the present invention. Fig.10 , the anti-scattering substrates 71 of all anti-scattering elements 70 correspond one-to-one in the axial direction of the detector ring 60, that is, the number of anti-scattering substrates 71 of each anti-scattering element 70 is equal and corresponds in the axial direction of the detector ring 60. Further, the multiple anti-scattering substrates 71 corresponding to each other in the axial direction of the detector ring 60 are a group of anti-scattering units 710. It can be understood that the number of anti-scattering units 710 is equal to the number of anti-scattering substrates 71 in a single anti-scattering element 70. The inner fixing structure includes multiple inner mounting plates 91 corresponding one-to-one to the anti-scattering units 710, that is, the multiple inner mounting plates 91 are arranged in sequence along the circumferential direction of the detector ring 60, and the multiple inner mounting plates 91 correspond one-to-one to the multiple groups of anti-scattering units 710 in the radial direction of the detector ring 60. The outer fixing structure includes a plurality of outer mounting plates 92 corresponding to the anti-scatter units 710 one by one, that is, the plurality of outer mounting plates 92 are arranged in sequence along the circumferential direction of the detector ring 60, and the plurality of outer mounting plates 92 correspond to the plurality of groups of anti-scatter units 710 one by one in the radial direction of the detector ring 60. All anti-scatter substrates 71 in the same group of anti-scatter units 710 are fixedly connected to the corresponding inner mounting plates 91 and outer mounting plates 92. In this way, the corresponding inner mounting plates 91, anti-scatter substrates 71 and outer mounting plates 92 are assembled into a module and then disassembled and assembled as a whole on the inner side of the detector ring 60. The installation of all anti-scatter components 70 is realized through the modular concept, which simplifies the installation difficulty and facilitates the subsequent disassembly and maintenance of the local CT detection components.

[0064] Further, see Fig.10 , and refer to Fig. 9, the number of detector units 31 in the detector ring 60 is the same as the number of anti-scatter units 710, and the multiple detector units 31 and the multiple groups of anti-scatter units 710 correspond to each other in the radial direction of the detector ring 60, and the corresponding detector units 31 are fixedly connected to the outer mounting plates 92 corresponding to the anti-scatter units 710. In this way, the corresponding inner mounting plates 91, the anti-scatter substrate 71, the outer mounting plates 92 and the detector units 31 can be assembled into a module and then disassembled and assembled on the scanning frame 10 as a whole. The CT detection assembly of this embodiment is disassembled and assembled on the scanning frame 10 through the modular concept. This modular disassembly concept also facilitates the subsequent maintenance and replacement of the CT detection assembly.

[0065] Based on the above-mentioned CT detection assembly, this embodiment also provides a medical imaging system, including a tube focus ring 80 and the above-mentioned CT detection assembly, wherein the detector ring 60 of the CT detection assembly is coaxially arranged with the tube focus ring 80. Specifically, the medical imaging system may be a CT system, including a tube focus ring 80, a detector ring 60 and a plurality of anti-scattering components 70, wherein the detector ring 60 is coaxially arranged with the tube focus ring 80, the detector ring 60 includes a plurality of detector units 31 distributed along its own circumference, and each detector unit 31 extends along the axial direction of the detector ring 60; the anti-scattering components 70 are arranged on the inner side of the detector ring 60, and the plurality of anti-scattering components 70 are arranged in sequence along the extension direction of the detector unit 31, and an X-ray channel is formed between adjacent anti-scattering components 70 to allow X-rays to pass through the X-ray channel and reach the detector ring 60, that is, there is a gap between adjacent anti-scattering components 70, and the gap serves as an X-ray channel. The anti-scattering components 70 are perpendicular to the axial direction of the scanning hole 11.

[0066] Furthermore, the medical imaging system further includes a scanning gantry 10 and a scanning bed 40. The scanning gantry 10 is used as a mechanical bearing structure for installing the tube focus ring 80 and the detector ring 60, and the scanning bed 40 is used as a carrier for carrying the subject 50 (the subject 50 is, for example, a patient) to enter and exit the scanning hole 11 of the scanning gantry 10. In an actual application scenario, the subject 50 lies flat on the scanning bed 40, and as the scanning bed 40 enters the scanning hole 11, the patient is subjected to a radiographic examination in cooperation with the tube focus ring 80 and the detector ring 60. During the radiographic examination of the patient, the tube focus ring 80, the detector ring 60 and the scanning gantry 10 are required to remain relatively still. The rays emitted by the tube focus ring 80 pass through the patient through the X-ray channel to the inner side of the detector ring 60, and are received by the detector unit 31. The scattered rays generated during the examination are absorbed by the anti-scattering components 70 on both sides of the X-ray channel. In this way, the anti-scatter components 70 on both sides of the X-ray channel ensure that the scattered rays generated during the inspection process can be effectively absorbed to reduce the imaging interference of the scattered rays, and ensure that the rays received by the detector units 31 at different positions on the detector ring 60 will not be largely blocked by the anti-scatter components 70, thereby ensuring that the detector units 31 at the same angular position on the detector ring 60 can have a sufficient dose of rays to reconstruct the image.

[0067] In summary, in the medical imaging system and CT detection assembly thereof provided by the utility model, the CT detection assembly includes a detector ring and an anti-scattering member; the anti-scattering member is in the form of a sheet, the anti-scattering member is arranged on the inner side of the detector ring, the anti-scattering member is perpendicular to the axial direction of the detector ring, a plurality of anti-scattering members are arranged in sequence along the axial direction of the detector ring, and at least part of two adjacent anti-scattering members have a gap. Such a configuration can ensure that the CT detection assembly is assembled in the medical imaging system, the anti-scattering member is perpendicular to the scanning hole of the medical imaging system, and a plurality of anti-scattering members are arranged along the axial direction of the scanning hole, the rays emitted from the focus at any position on the focus ring of the tube will not be largely blocked by the anti-scattering member, and the dose of rays received by the detector ring can ensure the reconstruction of the image. In this way, the utility model can not only reduce the interference of scattered rays on the imaging quality of the medical imaging system through the anti-scattering member, but also the arrangement of the anti-scattering member can ensure that the rays received by the detector units at different positions on the detector ring will not be largely blocked by the anti-scattering member, thereby ensuring that the detector units at the same angle position on the detector ring can have sufficient doses of rays to reconstruct the image.

[0068] Although the utility model is disclosed as above with preferred embodiments, the above embodiments are not intended to limit the utility model. For any technician familiar with the art, without departing from the scope of the technical solution of the utility model, the above disclosed technical content can be used to make many possible changes and modifications to the technical solution of the utility model, or modified into equivalent embodiments with equivalent changes. Therefore, any simple modification, equivalent change and modification made to the above embodiments based on the technical essence of the utility model without departing from the content of the technical solution of the utility model still falls within the scope of protection of the technical solution of the utility model.

Claims

1. A CT detection assembly, characterized in that: It comprises a detector ring (60) and an anti-scattering element (70); The anti-scattering member (70) is in sheet form and is arranged on the inner side of the detector ring (60). The anti-scattering member (70) is perpendicular to the axial direction of the detector ring (60). A plurality of anti-scattering members (70) are arranged in sequence along the axial direction of the detector ring (60), and at least two adjacent anti-scattering members (70) are spaced apart from each other.

2. The CT detection assembly according to claim 1, characterized in that: A plurality of anti-scattering elements (70) are evenly spaced and arranged along the axial direction of the detector ring (60).

3. The CT detection assembly according to claim 1, characterized in that: The anti-scattering element (70) comprises a plurality of anti-scattering substrates (71) arranged in a ring shape.

4. The CT detection assembly according to claim 3, characterized in that: The anti-scattering substrate (71) is fan-shaped; or, the plurality of anti-scattering substrates (71) of the anti-scattering element (70) are integrally formed.

5. The CT detection assembly according to claim 3, characterized in that: The CT detection assembly further comprises an inner fixing structure and an outer fixing structure, wherein the outer fixing structure is mounted on the inner side of the detector ring (60), the outer sides of all the anti-scattering components (70) are fixed to the outer fixing structure, and the inner sides of all the anti-scattering components (70) are fixedly connected to the inner fixing structure; the inner fixing structure and the outer fixing structure are both used for allowing rays to pass through.

6. The CT detection assembly according to claim 5, characterized in that: The anti-scatter substrates (71) of all the anti-scatter elements (70) correspond one-to-one in the axial direction of the detector ring (60), and a plurality of the anti-scatter substrates (71) corresponding in the axial direction of the detector ring (60) form a group of anti-scatter units (710); the inner fixing structure comprises a plurality of inner mounting plates (91) corresponding one-to-one to the anti-scatter units (710); the outer fixing structure comprises a plurality of outer mounting plates (92) corresponding one-to-one to the anti-scatter units (710); and all the anti-scatter substrates (71) in the same group of anti-scatter units (710) are fixedly connected to the corresponding inner mounting plates (91) and the outer mounting plates (92).

7. The CT detection assembly according to claim 6, characterized in that: The detector ring (60) comprises a plurality of detector units (31) arranged in a ring shape, the detector units (31) corresponding to the anti-scatter units (710) one by one, and the corresponding detector units (31) are fixedly connected to the outer mounting plates (92) corresponding to the anti-scatter units (710).

8. A medical imaging system, characterized in that: include: Tube focus ring (80); A detector ring (60) is coaxially arranged with the tube focus ring (80), the detector ring (60) comprising a plurality of detector units (31) distributed along the circumferential direction, each of the detector units (31) extending along the axial direction of the detector ring (60); A plurality of anti-scattering members (70), wherein the anti-scattering members (70) are arranged on the inner side of the detector ring (60), and the plurality of anti-scattering members (70) are arranged in sequence along the extension direction of the detector unit (31), and an X-ray channel is formed between adjacent anti-scattering members (70) to allow X-rays to pass through the X-ray channel and reach the detector ring (60).

9. The medical imaging system according to claim 8, characterized in that: The medical imaging system further comprises a scanning gantry (10), wherein the scanning gantry (10) has a scanning hole (11), the detector ring (60) and the tube focus ring (80) are both mounted on the scanning gantry (10), and the detector ring (60) is coaxial with the scanning hole (11).

10. The medical imaging system according to claim 9, characterized in that: The number of the detector rings (60) is at least two and they are arranged in sequence along the axial direction of the scanning hole; the number of the tube focus ring is at least one.

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