CN215687947U - Anti-scatter grid and CT imaging device - Google Patents

Abstract

The application relates to an anti-scatter grid and CT imaging equipment, the anti-scatter grid includes: the grating comprises a grating body and an anti-scattering base body connected with the grating body; the grid body comprises an anti-scattering plate group, wherein the anti-scattering plate group comprises a plurality of uniformly distributed X-ray absorption plates; the anti-scattering matrix comprises a plurality of grid base blocks which are uniformly distributed, and the X-ray absorption plate is arranged on the grid base blocks; a plurality of radiation passages are formed between the plurality of X-ray absorption plates, and the cross-sectional area of the grid base block is larger than that of the X-ray absorption plates. By the method and the device, the influence of projection deviation of partial X-ray beams on the CT detector is inhibited, and the influence of focus displacement of the X-ray bulb tube on imaging quality is reduced.

Description

Anti-scatter grid and CT imaging device

Technical Field

The application relates to the technical field of medical equipment, in particular to an anti-scatter grid and CT imaging equipment.

Background

Computed Tomography (CT) equipment scans X-rays generated by an X-ray tube from multiple directions of a human body to a certain thickness, converts the attenuated X-rays into visible light by a CT detector, converts the visible light into electrical signals, and finally performs image reconstruction by computer equipment to obtain a CT image after performing analog-to-digital conversion on the electrical signals.

During a CT scan, the X-rays emitted by the bulb are attenuated to different degrees in the radiation direction, while being partially scattered with respect to the initial radiation direction, and the scattered X-ray beam, when reaching the CT detector, is distorted due to its superposition with the X-ray beam arriving in the initial radiation direction, resulting in a reconstructed image from the intensity distribution, which reduces the image imaging quality. In general, an Anti-scatter grid (ASG) may be arranged in front in the X-ray radiation direction to reduce the influence of scattered X-rays on the imaging quality.

Conventional CT detectors have been designed with a single pixel as a unit due to the relatively large pixel size. The ASG has symmetry relative to the position of a single pixel, and when the focus of the X-ray tube is displaced, the projection intensity of the ray passing through the ASG is slightly changed, so that the imaging effect of the whole imaging system is slightly influenced. However, when the CT detector pixel size is small, as in a CT system with a photon counting detector, the pixel size is smaller than in a conventional detector. When the ASG is designed, the distance between the plates of the anti-scatter-grid is usually an area formed by a plurality of pixels, and the positions of different pixels in the unit relative to the ASG are different, so that the imaging effect is very sensitive to the movement of the focus of the X-ray tube, and the imaging effect is affected.

Disclosure of Invention

The embodiment of the application provides an anti-scatter grid and CT imaging equipment, and aims to at least solve the problem that when the size of a pixel of a CT detector is small in the related art, the imaging effect is sensitive to the movement of the focus of an X-ray bulb tube and the imaging effect is influenced.

In a first aspect, an embodiment of the present application provides an anti-scatter-grid, including: the grating comprises a grating body and an anti-scattering base body connected with the grating body; wherein the content of the first and second substances,

the grid body comprises an anti-scatter plate group, and the anti-scatter plate group comprises a plurality of uniformly distributed X-ray absorption plates; the anti-scattering matrix comprises a plurality of grid base blocks which are uniformly distributed, and the X-ray absorption plate is arranged on the grid base blocks;

a plurality of radiation passages are formed between the plurality of X-ray absorption plates, and the cross-sectional area of the grid base block is larger than that of the X-ray absorption plates.

In some of these embodiments, the grid base blocks are arranged in a manner that is compatible with the X-ray absorbing plates.

In some of the embodiments, the anti-scatter matrix comprises a plurality of parallel grid blocks extending in a single direction, the X-ray absorbing plate comprises a plurality of parallel absorbing plates extending in a single direction, the parallel absorbing plates are disposed on the parallel grid blocks; the cross-sectional area of the parallel grid base block is larger than that of the parallel absorption plates.

In some of these embodiments, the anti-scatter matrix includes a number of transverse grid blocks and a number of longitudinal grid blocks connected to the transverse grid blocks;

the X-ray absorption plate includes a plurality of transverse absorption plates and a plurality of longitudinal absorption plates connected to the transverse absorption plates; the transverse absorption plates are arranged on the transverse grid base blocks, and the longitudinal absorption plates are arranged on the longitudinal grid base blocks; the cross-sectional area of the transverse grid base block is larger than that of the transverse absorption plate, and the cross-sectional area of the longitudinal grid base block is larger than that of the longitudinal absorption plate.

In some of the embodiments, the height of the anti-scattering matrix along the radiation direction of the X-ray is 2-3 mm.

In some of these embodiments, the distance between the X-ray absorbing plates is the size of one CT detector pixel.

In some of these embodiments, the distance between the X-ray absorbing plates is the size of at least two CT detector pixels.

In some embodiments, the anti-scattering matrix is made of a metal or an alloy having an attenuation effect on X-rays.

In some of these embodiments, the anti-scatter matrix is integrally formed with the grid body; or the anti-scattering base body is detachably connected with the grating body.

In a second aspect, embodiments of the present application provide a CT imaging apparatus, including a CT detector and an anti-scatter-grid as described in the first aspect above, the CT detector including at least one detector unit, each detector unit including a plurality of pixels, forming a pixel array;

the anti-scatter-grid is disposed in front of the CT detector along the X-ray radiation direction and aligned with the pixel array.

Compared with the related art, the anti-scatter-grid provided by the embodiment of the application comprises: the grating comprises a grating body and an anti-scattering base body connected with the grating body; the grid body comprises an anti-scattering plate group, wherein the anti-scattering plate group comprises a plurality of uniformly distributed X-ray absorption plates; the anti-scattering matrix comprises a plurality of grid base blocks which are uniformly distributed, and the X-ray absorption plate is arranged on the grid base blocks; a plurality of radiation passages are formed between the plurality of X-ray absorption plates, and the cross-sectional area of the grid base block is larger than that of the X-ray absorption plates. The anti-scatter grid is arranged along the radiation direction of rays, so that a grid body in the anti-scatter grid is connected with an anti-scatter matrix, and an X-ray absorption plate of an anti-scatter plate group of the grid body is arranged on the grid base block, so that the sectional area of the grid base block is larger than that of the X-ray absorption plate. Under the condition that the focus of the X-ray bulb tube has displacement deviation, part of X-ray projection position changes passing through the anti-scatter grid just fall on the grid base block, so that the influence of projection deviation of part of X-ray beams on the CT detector is inhibited, and the influence of the focus displacement of the X-ray bulb tube on the imaging quality is reduced.

The details of one or more embodiments of the application are set forth in the accompanying drawings and the description below to provide a more thorough understanding of the application.

Drawings

The accompanying drawings, which are included to provide a further understanding of the application and are incorporated in and constitute a part of this application, illustrate embodiment(s) of the application and together with the description serve to explain the application and not to limit the application. In the drawings:

FIG. 1 is a front view of a fitting structure of an anti-scatter grid and a pixel array of a CT detector according to an embodiment of the present application;

FIG. 2 is a side view of a mating structure of an anti-scatter grid and a CT detector pixel array according to an embodiment of the present disclosure;

FIG. 3 is a schematic diagram illustrating the effect of the projection of the X-ray beam onto the CT detector pixel through the anti-scatter-grid in the embodiment of the present application;

FIG. 4 is a schematic structural diagram of a CT detector pixel array according to an embodiment of the present disclosure;

FIG. 5 is a schematic view of the structure of an anti-scattering matrix in one embodiment of the present application;

FIG. 6 is a top view of an alignment structure of an anti-scattering matrix and a pixel array of a CT detector according to an embodiment of the present disclosure;

FIG. 7 is a front view of an alignment structure of an anti-scatter matrix and a CT detector pixel array in an embodiment of the present application.

Description of the drawings: 1. an anti-scatter-grid; 11. a grid body; 111. an X-ray absorbing plate; 111A, parallel absorbing plates; 12. an anti-scatter matrix; 121. a grid base block; 121A, a parallel grating base block; 121B, a transverse grating base block; 121C, longitudinal grating base blocks; 2. an array of pixels.

Detailed Description

In order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be described and illustrated below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the present application and are not intended to limit the present application. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments provided in the present application without any inventive step are within the scope of protection of the present application.

It is obvious that the drawings in the following description are only examples or embodiments of the present application, and that it is also possible for a person skilled in the art to apply the present application to other similar contexts on the basis of these drawings without inventive effort. Moreover, it should be appreciated that in the development of any such actual implementation, as in any engineering or design project, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, which may vary from one implementation to another.

Reference in the specification to "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the specification. The appearances of the phrase in various places in the specification are not necessarily all referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive of other embodiments. Those of ordinary skill in the art will explicitly and implicitly appreciate that the embodiments described herein may be combined with other embodiments without conflict.

Unless defined otherwise, technical or scientific terms referred to herein shall have the ordinary meaning as understood by those of ordinary skill in the art to which this application belongs. Reference to "a," "an," "the," and similar words throughout this application are not to be construed as limiting in number, and may refer to the singular or the plural. The present application is directed to the use of the terms "including," "comprising," "having," and any variations thereof, which are intended to cover non-exclusive inclusions; for example, a process, method, system, article, or apparatus that comprises a list of steps or modules (elements) is not limited to the listed steps or elements, but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus. Reference to "connected," "coupled," and the like in this application is not intended to be limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. The term "plurality" as referred to herein means two or more. "and/or" describes an association relationship of associated objects, meaning that three relationships may exist, for example, "A and/or B" may mean: a exists alone, A and B exist simultaneously, and B exists alone. The character "/" generally indicates that the former and latter associated objects are in an "or" relationship. Reference herein to the terms "first," "second," "third," and the like, are merely to distinguish similar objects and do not denote a particular ordering for the objects.

The imaging principle of CT (Computed Tomography) is to scan a certain thickness of X-rays from a given direction of a human body by using the X-rays, convert the attenuated X-rays into visible light by a detector, convert the visible light into electrical signals, perform analog-to-digital conversion on the electrical signals, and perform image reconstruction by a computer device to obtain a final CT image.

The embodiment of the application provides a CT imaging device, which can comprise a scanner, an electronic module and a memory, wherein the scanner comprises a machine frame, a scanning bed, at least one pair of X-ray radiation sources and a CT detector, the X-ray radiation sources and the CT detector are fixed on the machine frame and are arranged in pairs, and an anti-scatter grid is attached to the CT detector.

The gantry may be configured to support one or more components of the CT imaging apparatus, such as an X-ray radiation source, a CT detector, and the like. The gantry may include a circular opening (e.g., a detection region) to accommodate a scan target.

The scan bed may support a scan target, and the scan target may be moved by the scan bed to a desired position within the gantry within an examination region between the X-ray radiation source and the CT detector during an X-ray radiation scan. In some embodiments, the scan target may be on a scan bed. The scanning bed may be moved and brought to a desired position in the examination area. In other embodiments, the scanner may have a relatively long axial field of view, such as a 2 meter long axial field of view. Accordingly, the scanning bed can be moved along the axial direction to a desired position over a wide range (e.g., greater than 2 meters).

The X-ray radiation source emits X-rays which are attenuated, if necessary, by the scanned target portion. The X-ray radiation source may be configured as an X-ray tube for generating X-rays having an energy in the range of 20-140 keV.

The CT detector may detect radiation events (e.g., X-ray signals) emitted from the detection region and output measurement signals corresponding to the intensity of the incident X-ray radiation. In some embodiments, the detector may receive the radiation and generate an electrical signal. The CT detector has a plurality of pixels for the planar resolved acquisition of the intensity distribution of the incident X-ray radiation. The CT detector may comprise one or more detector units, each detector unit comprising a plurality of pixels, forming a pixel array 2.

The electronic module may collect and/or process the electrical signals generated by the detector. The electronics module may convert an analog signal related to the energy of the radiation received by the detector into a digital signal. The electronics module may compare the plurality of digital signals, analyze the plurality of digital signals, and determine image data from the energy of the radiation received in the detector. In some embodiments, if the detector has a large axial field of view (e.g., 0.75 meters to 2 meters), the electronics module may have a high data input rate from multiple detector channels. For example, the electronic module may process hundreds of billions of events per second.

The anti-scatter-grid has a grid-shaped structure, and is disposed in front of the CT detector along the X-ray radiation direction and aligned with the pixel array. Wherein each grid opening of the grid-shaped structure forms a radiation channel which extends in the direction of the X-ray beam. The X-ray beams emitted by the X-ray tube interact with the scanned object and are emitted in all directions, and the CT detector receives radiation from the X-ray radiation source directly through the anti-scatter-grid 1 and blocks scattered beams from other radiation directions.

Fig. 1-2 are a front view and a side view of a matched structure of an anti-scatter grid and a pixel array of a CT detector according to an embodiment of the present application. Referring to fig. 1-2, an anti-scatter-grid 1 includes: a grid body 11 and an anti-scattering base 12 connecting the grid body 11.

In the present embodiment, the grid body 11 includes an anti-scatter plate group including a plurality of uniformly arranged X-ray absorption plates 111. The length of the X-ray absorption plates 111 in the X-ray beam radiation direction is greater than the dimension perpendicular to the X-ray radiation direction, and X-ray radiation channels are formed between two adjacent X-ray absorption plates 111, and the respective X-ray radiation channels are separated from each other by a plate wall and extend in the X-ray beam radiation direction. X-ray beams of different scattering directions enter the radiation passage and are absorbed by the wall surface of the X-ray absorption plate 111 when the X-ray beams scattered with respect to the initial radiation direction reach the wall surface. The material of the X-ray absorption plate 111 is lead, tungsten or other materials capable of absorbing a large amount of X-ray beams.

Wherein the distance between the X-ray absorption plates 111 can be adaptively configured according to the size of the pixel array 2 of the CT detector. In some embodiments, the pixel array 2 of the CT detector is relatively large in size, and the ASG is designed in units of a single pixel, i.e. the distance between the X-ray absorbing plates 111 is the size of one CT detector pixel. In other embodiments, the pixel array 2 of the CT detector is small in size, e.g. in a system with photon counting CT detectors, the distance between the X-ray absorbing plates 111 is typically in units of a plurality of small pixel areas, i.e. the distance between said X-ray absorbing plates 111 is in units of at least two CT detector pixels, e.g. 1X 3, 2X 2 or 3X 3 small pixel sizes.

Referring to fig. 1-2, in the present embodiment, the anti-scattering matrix 12 includes a plurality of grid base blocks 121 uniformly arranged, the X-ray absorbing plates 111 are disposed on the grid base blocks 121, and a cross-sectional area of the grid base blocks 121 in a direction perpendicular to the X-ray radiation is larger than a cross-sectional area of the X-ray absorbing plates 111. Therefore, when the distance between the X-ray absorption plates 111 takes a plurality of detector pixel areas as a unit, under the condition that the displacement deviation of the focus of the X-ray bulb tube occurs, the influence of the projection deviation of the X-ray beams on different pixels of the CT detector between the adjacent X-ray absorption plates 111 can be reduced. In some embodiments, the material of the anti-scattering substrate 12 is a metal or an alloy having an attenuation effect on X-rays, such as lead, tungsten, etc.

The following describes a specific implementation process of the embodiment of the present application, taking a change in the position of the projection of the X-ray beam L on the detector pixel before and after the displacement deviation of the X-ray tube as an example:

fig. 3 is a schematic diagram illustrating the effect of the projection of the X-ray beam on the CT detector pixel through the anti-scatter-grid 1 in the embodiment of the present application. As shown in fig. 3, in case of a shift deviation of the X-ray tube focal spot, the projection path of a part of the X-ray beam, e.g. the ray beam L, is shifted to L'. It can be seen that when the ray bundle L is projected on the detector pixel, the projection positions before and after the deviation of the ray bundle L passing through the anti-scatter grid 1 are all located on the grid base block 121, thereby reducing the influence of the focus displacement of the X-ray tube on the imaging quality.

In summary, the anti-scatter-grid provided by the embodiment of the present application includes: the grating comprises a grating body and an anti-scattering base body connected with the grating body; the grid body comprises an anti-scattering plate group, wherein the anti-scattering plate group comprises a plurality of uniformly distributed X-ray absorption plates; the anti-scattering matrix comprises a plurality of grid base blocks which are uniformly distributed, and the X-ray absorption plate is arranged on the grid base blocks; a plurality of radiation passages are formed between the plurality of X-ray absorption plates, and the cross-sectional area of the grid base block is larger than that of the X-ray absorption plates. The grid body 11 of the anti-scatter grid is connected to the anti-scatter matrix 12 by arranging the anti-scatter grid along the radiation direction, and the anti-scatter plate group X-ray absorption plate 111 of the grid body 11 is arranged on the grid base block 121 so that the cross-sectional area of the grid base block 121 is larger than the cross-sectional area of the X-ray absorption plate 111. Under the condition that the focus of the X-ray bulb tube has displacement deviation, the position changes of the partial X-ray passing through the anti-scatter grid before and after projection deviation are all located on the grid base block 121, so that the influence of projection deviation of partial X-ray beams on the CT detector is inhibited, and the influence of the focus displacement of the X-ray bulb tube on the imaging quality is reduced.

The embodiments of the present application are described and illustrated below by means of preferred embodiments.

On the basis of the above embodiments, in some of the embodiments, the grid base block 121 is arranged in a manner matched with that of the X-ray absorption plate 111. Specifically, the anti-scatter plate groups in the anti-scatter grid 1 may be all in a 1D (one-dimensional) or 2D (two-dimensional) grid structure.

1-2, in one particular embodiment, the group of anti-scatter plates may have a one-dimensional grid structure. Specifically, the anti-scattering matrix 12 includes a plurality of parallel grid base blocks 121A extending in a single direction. Correspondingly, the X-ray absorption plate 111 includes a plurality of parallel absorption plates 111A extending in a single direction, and the parallel absorption plates 111A are disposed on the parallel grid base block 121A. The parallel absorption plates 111A on the adjacent parallel lattice base blocks 121A form radiation passages therebetween and extend in a direction parallel to the plate surfaces. The cross-sectional area of the parallel grid base block 121A is larger than the cross-sectional area of the parallel absorption plate 111A in the direction perpendicular to the X-ray radiation. So that a part of the scattered beam among the X-rays passing through the anti-scatter-grid 1 is absorbed by the plate surface of the X-ray absorption plate 111 and the parallel grid base block 121A. Particularly, under the condition that the focus of the X-ray bulb tube has displacement deviation, the projection positions before and after the projection deviation of partial X-rays passing through the anti-scatter grid 1 all fall on the grid base block, so that the influence of the projection deviation of partial X-ray beams on the CT detector is inhibited, and the influence of the focus displacement of the X-ray bulb tube on the imaging quality is reduced.

FIG. 4 is a schematic structural diagram of a CT detector pixel array; FIG. 5 is a schematic view of the structure of the anti-scatter matrix 12; FIGS. 6-7 are schematic views of the alignment structure of the anti-scattering matrix and the pixel array of the CT detector according to the embodiment of the present application. In another specific embodiment, as shown in fig. 6-7, the group of anti-scatter plates may have a two-dimensional grid structure, which may provide a higher mechanical stiffness than the 1D structure. Specifically, the anti-scattering plate group includes a two-dimensional structure formed by a plurality of unit cells which intersect with each other and are defined by grid base blocks 121, for example, the anti-scattering plate group may be arranged in a rectangular structure, and the anti-scattering base 12 includes a plurality of transverse grid base blocks 121B and a plurality of longitudinal grid base blocks 121C connected to the transverse grid base blocks 121B to form a grid-like structure; suitably, the X-ray absorbing plate 111 comprises a plurality of transverse absorbing plates and a plurality of longitudinal absorbing plates connected to the transverse absorbing plates. The transverse absorption plates are disposed on the transverse grid base blocks 121B, and the longitudinal absorption plates are disposed on the longitudinal grid base blocks 121C. The cross-sectional area of the transverse grid base block 121B is larger than the cross-sectional area of the transverse absorption plate, and the cross-sectional area of the longitudinal grid base block 121C is larger than the cross-sectional area of the longitudinal absorption plate in the direction perpendicular to the X-ray radiation. The principle of suppressing the projection shift of the X-ray beam on the CT detector by the anti-scatter matrix 12 is the same as that of the above embodiment, and is not described herein again.

It should be noted that, in this embodiment, the anti-scatter plate groups may be arranged in a two-dimensional structure of a circle, a polygon (e.g., a hexagon), or other shapes besides a rectangular structure, and the specific shape of the two-dimensional structure is not limited in this application.

In some embodiments, the height of the anti-scatter matrix 12 in the direction of the radiation of the X-rays is 2-3 mm. With this size, the anti-scattering matrix 12 has a good effect of suppressing the projection deviation of the X-ray absorption plate 111 with respect to the X-ray beam, does not affect the absorption effect of the X-ray absorption plate 111 with respect to the scattered X-ray beam, and realizes the support of the X-ray absorption plate 111.

In some embodiments, the anti-scattering matrix 12 is integrally formed with the grid body 11, and may be implemented by bonding, welding, or the like. The integral forming structure can effectively improve the overall strength of the anti-scattering grid 1, simplify the overall structure of the anti-scattering grid 1 and improve the production efficiency. In other embodiments, the anti-scatter matrix 12 is removably attached to the grid body 11. The detachable connection may be achieved by means of an adhesive, a screw, a clamp, and the like, and the application is not particularly limited.

The technical features of the embodiments described above may be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the embodiments described above are not described, but should be considered as being within the scope of the present specification as long as there is no contradiction between the combinations of the technical features.

The above-mentioned embodiments only express several embodiments of the present application, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the concept of the present application, which falls within the scope of protection of the present application. Therefore, the protection scope of the present patent shall be subject to the appended claims.

Claims (10)

1. An anti-scatter-grid, comprising: the grating comprises a grating body and an anti-scattering base body connected with the grating body; wherein the content of the first and second substances,

the grid body comprises an anti-scatter plate group, and the anti-scatter plate group comprises a plurality of uniformly distributed X-ray absorption plates; the anti-scattering matrix comprises a plurality of grid base blocks which are uniformly distributed, and the X-ray absorption plate is arranged on the grid base blocks;

a plurality of radiation passages are formed between the plurality of X-ray absorption plates, and the cross-sectional area of the grid base block is larger than that of the X-ray absorption plates.

2. The anti-scatter-grid according to claim 1, wherein the grid base blocks are arranged in a manner adapted to the X-ray absorbing plates.

3. The anti-scatter-grid according to claim 2, wherein the anti-scatter-matrix comprises a plurality of parallel grid-bases extending in a single direction, the X-ray absorbing plate comprises a plurality of parallel absorbing plates extending in a single direction, the parallel absorbing plates being disposed on the parallel grid-bases; the cross-sectional area of the parallel grid base block is larger than that of the parallel absorption plates.

4. The anti-scatter-grid according to claim 2, wherein the anti-scatter-matrix comprises a plurality of transverse grid blocks and a plurality of longitudinal grid blocks connected to the transverse grid blocks;

the X-ray absorption plate includes a plurality of transverse absorption plates and a plurality of longitudinal absorption plates connected to the transverse absorption plates; the transverse absorption plates are arranged on the transverse grid base blocks, and the longitudinal absorption plates are arranged on the longitudinal grid base blocks; the cross-sectional area of the transverse grid base block is larger than that of the transverse absorption plate, and the cross-sectional area of the longitudinal grid base block is larger than that of the longitudinal absorption plate.

5. The anti-scatter-grid according to claim 1, wherein the height of the anti-scatter matrix in the radiation direction of the X-rays is 2-3 mm.

6. The anti-scatter-grid according to claim 1, wherein the distance between the X-ray absorbing plates is the size of one CT detector pixel.

7. The anti-scatter-grid according to claim 1, wherein the distance between the X-ray absorbing plates is the size of at least two CT detector pixels.

8. The anti-scatter-grid according to claim 1, wherein the anti-scatter matrix is made of a metal or an alloy having an attenuation effect on X-rays.

9. The anti-scatter-grid according to claim 1, wherein the anti-scatter matrix is integrally molded with the grid body; or the anti-scattering base body is detachably connected with the grating body.

10. A CT imaging device comprising a CT detector and an anti-scatter-grid according to any of claims 1-9, the CT detector comprising at least one detector cell, each detector cell comprising a plurality of pixels, forming a pixel array;

the anti-scatter-grid is disposed in front of the CT detector along the X-ray radiation direction and aligned with the pixel array.

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