CT imaging system

Abstract

The CT imaging system 1000 includes a scanning channel 200 arranged along a first direction, a radiation source unit 10 disposed on one side of the scanning channel 200 for emitting a radiation beam, and a detector unit 20 disposed on the other side of the scanning channel 200, facing the radiation source unit 10, for receiving the radiation beam, the radiation beam forms an imaging area between the radiation source unit 10 and the detector unit 20, the detector unit 20 includes at least two detection areas 21 and one blank area 22, the imaging area has a main beam plane 31 extending through the radiation source unit 10, and the positions of the detection areas 21 and the blank area 22 are complementary to the main beam plane 31. The CT imaging system 1000 can obtain missing data through algorithm correction using data symmetry caused by rotational scanning, and complete projection data is obtained and used to restore image information of the detected object 100.

Description

[Technical field]

[0001] The present application relates to the field of security check technology, and in particular to CT imaging systems. [Background technology]

[0002] The size and acquisition speed of the detector are mutually limited. A high-resolution detector has a relatively slow acquisition speed, and in a CT imaging system, thousands of frames of data must be acquired, so the time to acquire complete data is quite long. Also, a high-acquisition-speed detector has a relatively small imaging area, so it cannot meet the requirements for wide-field imaging. Summary of the Invention

[0003] The main purpose of the present application is to solve at least one of the technical problems existing in the prior art.

[0004] For example, the embodiments of the present disclosure propose a CT imaging system that can be used for high-resolution X-ray imaging, meets the demands for a wide field of view and collection speed, does not impose special restrictions on detector specifications, and broadens the application range of conventional detectors.

[0005] In order to achieve the above-mentioned object, the present application provides a CT imaging system including a scanning channel arranged along a first direction, through which a detected object passes to and from the CT imaging system; a radiation source unit provided on one side of the scanning channel for emitting a radiation beam; and a detector unit provided on the other side of the scanning channel, facing the radiation source unit, for receiving the radiation beam, wherein the radiation beam forms an imaging area between the radiation source unit and the detector unit, the detector unit including at least two detection areas and one blank area, and the imaging area has a main beam plane extending through the radiation source unit, and the positions of the detection areas and the blank area are complementary to the main beam plane.

[0006] According to the CT imaging system of the present application, the detection areas are distributed asymmetrically with respect to the main beam plane, and the positions of the detection areas and the blank areas are complementary with respect to the main beam plane. Therefore, by utilizing the data symmetry caused by rotational scanning, missing data can be obtained through algorithm correction, and complete projection data can be obtained and used to restore the image information of the detected object.

[0007] Furthermore, one of the at least two detection areas Main beam surface and the other of the at least two detection areas is provided on one side of the one of the detection areas.

[0008] Furthermore, one of the at least two detection areas is provided on the main beam plane and is equally divided by the main beam plane.

[0009] Furthermore, the other of the at least two detection areas is adjacent to one of the at least two detection areas.

[0010] Furthermore, the other of the at least two detection areas is separated from one of the at least two detection areas by the blank area.

[0011] Furthermore, at least one detector is included within the detection area, and the size of the blank area is equal to or larger than the size of one detector pixel.

[0012] Furthermore, the CT imaging system has a first position where the radiation beam covers a first blank area and a second position where the radiation beam covers a first detection area, and the image data output from the first position and the second position are the same.

[0013] Furthermore, the detector units are provided in a plurality of rows, and the detector units in the plurality of rows are aligned in a first direction.

[0014] Furthermore, the radiation beam includes a first exit angle and a second exit angle, and the range covered by the first exit angle and the second exit angle is an exit range of the radiation beam.

[0015] Furthermore, at least two detection areas are covered within the emission range.

[0016] The system further includes a mounting stage slidably mounted on the scan channel so that a detected object passes through the scan channel into and out of the CT imaging system.

[0017] Furthermore, an adjustment platform for adjusting the attitude of the object to be detected is provided between the mounting stage and the object to be detected.

[0018] Additional aspects and advantages of the present application will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the present application.

[0019] Other objects and advantages of the present application will become apparent and the present disclosure can be more fully understood by describing the embodiments of the present disclosure with reference to the following drawings. [Brief description of the drawings]

[0020] [Figure 1] FIG. 1 is a diagram showing an application scene of a CT imaging system according to an embodiment of the present invention. [Diagram 2] FIG. 2 is a schematic diagram of the configuration of a CT imaging system according to an embodiment of the present invention. [Diagram 3] FIG. 3 is a schematic diagram illustrating a configuration of a CT imaging system according to an embodiment of the present invention in a first position. [Figure 4] FIG. 4 is a schematic diagram illustrating a configuration of a CT imaging system according to an embodiment of the present invention in a second position.

[0021] For clarity, in the drawings illustrating the embodiments of the present disclosure, the sizes of components and areas may be enlarged or reduced, that is, it should be noted that these drawings do not necessarily need to be drawn at actual scales.

Description of Reference Numerals

[0022] CT imaging system 1000, Object to be detected 100, scanning channel 200, adjustment platform 300, mounting stage 400, Radiation source unit 10, Detector unit 20, Detection area 21, first detection area 211, second detection area 212, Blank area 22, first blank area 221, Main beam plane 31, first emission angle 32, second emission angle 33.

Embodiments for Carrying Out the Invention

[0023] To make the objectives, technical solutions and advantages of the embodiments of the present disclosure clearer, the technical solutions of the embodiments of the present disclosure will be clearly and completely described below with reference to the drawings of the embodiments of the present disclosure. Of course, the described embodiments are only part of the embodiments of the present disclosure, not all of them. Based on the described embodiments of the present disclosure, all other embodiments that can be conceived by those skilled in the art without creative efforts fall within the protection scope of the present disclosure.

[0024] Unless otherwise defined, technical terms or scientific terms used in the present disclosure shall have the ordinary meanings understood by those skilled in the art. The terms "first", "second" and similar words used in the present disclosure do not indicate order, quantity or importance, but are only used to distinguish different components. Similar terms such as "including" or "comprising" mean that the elements or things before the term include the elements or things listed after the term and their equivalents, and do not exclude other elements or things.

[0025] Unless otherwise specified, terms related to directions such as "up", "down", "left", "right", "inside", and "outside" are used to indicate the directions and positional relationships shown in the drawings, and are merely for the convenience of explaining the present disclosure, and do not explicitly or implicitly indicate that the related devices, elements, or components have a specific orientation, or are constructed or operate in a specific orientation. When the absolute positions of the described objects change, the relative positional relationships they represent may also change accordingly. Therefore, these terms related to directions should not be construed as limitations of the present disclosure.

[0026] In a CT imaging system, a radiation beam emitted from a radiation source, collimated, and having a certain energy passes through a subject, and due to the differences in the attenuation coefficients of each volume element in each transmission direction, the energy received by the detector also varies, and a scanned image is obtained through a series of signal conversions. transparent The energy is also different, and a scanned image is obtained through a series of signal conversions.

[0027] The size and collection speed of the detector are mutually restricted. A detector with high resolution has a relatively slow collection speed. For wide-field imaging, a stepped scanning strategy is adopted multiple times, and the detection object needs to be scanned multiple times. In a CT imaging system, it is also necessary to collect thousands of frames of data, and the time required to obtain complete data becomes quite long. On the other hand, a detector with a high collection speed has a relatively small imaging area and cannot meet the imaging requirements of a wide field of view.

[0028] To meet the wide - field - of - view requirement, as a current solution, there is a technical solution of joining multiple rows of detectors. However, during the joining arrangement, it is necessary to reduce the joining gap between the detectors as much as possible. Otherwise, ring artifacts may occur due to data loss, which may affect the image quality. However, currently, high - resolution detectors have an edge thickness that is much larger than the size of the pixels of the detector. Therefore, if direct joining is used, a lot of data will be lost. On the other hand, if an integrated detector is used as it is, high requirements are imposed on the detector system, and the requirements for the field of view, transmission speed, resolution, etc. of the detector itself become higher, so it has generally become difficult to achieve.

[0029] This application proposes a CT imaging system 1000 with a wide field of view that can obtain complete CT data with just one CT scan by using a detector with high resolution and a small size, and can solve the above - mentioned problems.

[0030] It should be noted that the embodiments of the present disclosure are applicable to application scenarios such as CT scans and DR scans, but here, there is no limitation on the type of scan at all.

[0031] For example, in a CT scan, a radiation beam emitted from a radiation source, collimated, and having a certain energy passes through a subject. Due to the difference in the attenuation coefficients of each volume element in each transmission direction, the energy received by the detector is also different, and a scanned image is obtained through a series of signal conversions. transparent The energy is also different, and a scanned image is obtained through a series of signal conversions.

[0032] For example, in a DR scan, by using CCD imaging and performing imaging processing after irradiating with X - rays as they are, a weighted image of an object through which X - rays have passed in the irradiation direction is obtained.

[0033] In the embodiment of the present disclosure, the workpiece to be detected may be a device to be detected in various fields, such as a rocket body in the aerospace field or a pipe in the pipeline equipment field. Specifically, the workpiece has a cylindrical or approximately cylindrical structure. It is understood that the present technology method can also be used for workpieces with other contour structures, such as a cubic structure, a vertebral structure, etc.

[0034] A CT imaging system 1000 according to an embodiment of the present invention will be described below with reference to FIGS.

[0035] As shown in Figures 1 and 2, the CT imaging system 1000 of the present application is used to detect the internal structure of an object 100 to be detected, and includes a scanning channel 200, a radiation source unit 10 provided on one side of the scanning channel 200, and a detector unit 20 provided on the other side of the scanning channel 200.

[0036] Specifically, the scanning channel 200 is arranged along a first direction so that the object to be detected 100 passes through the scanning channel 200 and enters and exits the CT imaging system 1000, the radiation source unit 10 is used to emit a radiation beam, and the detector unit 20 and the radiation source unit 10 are arranged relative to each other and receive the radiation beam.

[0037] The first direction is understood as the transport direction of the scanning channel 200, and the detection object 100 is placed in the scanning channel 200 and moves in and out of the CT imaging system 1000 along the first direction. A radiation source unit 10 and a detector unit 20 are provided on both sides of the scanning channel 200, respectively, and the radiation source unit 10 and the detector unit 20 are provided opposite each other at an angle of 180°.

[0038] Inside the radiation source unit 10, a radiation generator, which is a core component of the radiation source unit 10, is provided. X-rays are generated by exciting the radiation generator to detect the object to be detected 100. A detector is provided inside the detector unit 20, which receives the radiation emitted from the radiation source and converts it into a digital signal. However, it includes a detector panel, a power supply, a cable, a detector shielding device, and the like.

[0039] An imaging area is formed between the radiation source unit 10 and the detector unit 20 for the radiation beam. A collimator is provided at the exit position of the radiation generator. After the X-rays are emitted from the radiation generator, they are irradiated onto the object to be detected 100 through the collimator. The collimator restricts the emission range of the X-rays to form the imaging area, mainly shields the X-rays emitted from other directions, and restricts the X-rays within the same plane.

[0040] The detector unit 20 includes at least two detection areas 21 and one blank area 22, and at least one detector is provided for each detection area 21.

[0041] In order to reduce the number of detectors in this application, a detection area 21 and a blank area 22 are provided in the detector unit 20. However, a detector is provided in the detection area 21 to receive the radiation beam. Also, two adjacent detection areas 21 are separated, and there is no detector in the separated area, so it does not have the function of receiving the radiation beam. The area provided between two adjacent detection areas 21 is the blank area 22. Therefore, the detector unit 20 includes at least two detection areas 21 separated so that one blank area 22 is formed.

[0042] On the field of view surface, the detector unit 20 has separated detection areas 21, and at least two detection areas 21 receive the radiation beam simultaneously, so it has a wide field of view function during the imaging process. In terms of cost, since there is a blank area 22 in the detector unit 20, the number of detectors used can be further reduced to lower the cost of the CT imaging system 1000.

[0043] Of course, there may be multiple detectors for receiving the radiation beam per detection area 21, and the total number of physical cells of the detector, i.e., detector pixels, number Detector resolution is closely related to pixel size; the smaller and more numerous the pixels, the higher the resolution of the CT imaging system 1000 and the clearer the image.

[0044] The imaging area has a main beam plane 31 extending through the radiation source unit 10, and at least two detection areas 21 are asymmetrically distributed in the second direction with reference to the main beam plane 31, and the positions of the detection areas 21 and the blank areas 22 are complementary to the main beam plane 31.

[0045] As shown in Figure 2, the dotted line in the middle of the imaging area is the main beam plane 31, and with the main beam plane 31 as a reference, the detection areas 21 are distributed asymmetrically in the second direction, that is, the detection areas 21 on both sides of the main beam plane 31 are asymmetric, and the distance between the position of the detection areas 21 and the main beam plane 31, and the distance between the position of the blank area 22 and the main beam plane 31 are the same, and there is a spatially complementary relationship.

[0046] The range of one detection area 21 may be equal to or greater than the range of the blank area 22 that spatially corresponds to this detection area 21 with respect to the main beam plane 31, that is, the length of the detection area 21 in the second direction may be equal to or greater than the length in the second direction of the blank area 22 that spatially corresponds to this detection area 21 with respect to the main beam plane 31. Preferably, when the range of the detection area 21 is equal to the range of the blank area 22 that spatially corresponds to this detection area 21 with respect to the main beam plane 31, the number of detectors required is minimized, resulting in a significant reduction in costs.

[0047] In one preferred embodiment, the CT imaging system 1000 includes a slip ring surrounded by a scanning channel 200. Both the radiation source unit 10 and the detector unit 20 are provided on the slip ring and are relatively arranged. After the slip ring is driven by a drive motor, it can rotate around the axis of the scanning channel 200. That is, after the slip ring rotates, the radiation source unit 10 and the detector unit 20 rotate around the axis of the scanning channel 200 to detect different cross-sections of the detection object 100.

[0048] According to the CT imaging system 1000 of the present application, a plurality of detectors having high resolution, small size, and high collection speed are used. The detection area 21 is distributed asymmetrically with respect to the main beam plane 31, and the positions of the detection area 21 and the blank area 22 complement each other with respect to the main beam plane 31. Therefore, by using the data symmetry of rotational scanning, missing data can be obtained through algorithm correction, and complete data can be obtained. The principle of obtaining missing data by rotational scanning will be described with reference to the following specific embodiments.

[0049] In a schematic embodiment of the present application, one of at least two detection areas 21 is provided on the main beam plane 31, and the other of at least two detection areas 21 is provided on one side of the one.

[0050] Taking the detector unit 20 including two detectors Knowledge Rear 21 and one blank area 22 as an example. The main beam plane 31 passes through one of the detection areas 21, and the other of the detection areas 21 is arranged on the right side of the one of the detection areas 21 and forms a blank area 22 with a gap. With respect to the main beam plane 31, two detectors in the imaging area are arranged asymmetrically.

[0051] Regarding the arrangement form of the detector unit 20, when divided in more detail, it may be divided into the following 3 types of embodiments.

[0052] In Embodiment 1, one of at least two detection areas 21 is provided on the main beam plane 31 and is equally divided by the main beam plane 31. However, the other of at least two detection areas 21 is adjacent to one of at least two detection areas 21.

[0053] In the plurality of detection areas 21 and the plurality of blank areas 22, the main beam plane 31 equally divides one detection area 21 through this detection area 21, the other detection area 21 is adjacent to the right side of this one detection area 21, and the two detection areas 21 are closely joined, which corresponds to the two detectors in the imaging area being asymmetrically arranged with respect to the main beam plane 31.

[0054] In Embodiment 2, one of at least two detection areas 21 is provided on the main beam plane 31 and is not equally divided by the main beam plane 31. However, the other of at least two detection areas 21 is separated from one of at least two detection areas 21 by a blank area 22.

[0055] In the plurality of detection areas 21 and the plurality of blank areas 22, the main beam plane 31 passes through one detection area 21, but the sizes of the detection areas on the left and right sides of the detection area 21 passed through by the main beam plane 31 are different. The other detection area 21 is arranged on the right side of this one detection area 21, and with respect to the main beam plane 31 that forms a blank area 22 with a gap, the two detectors in the imaging area are asymmetrically arranged.

[0056] In Embodiment 3, one of at least two detection areas 21 is provided on the main beam plane 31 and is not equally divided by the main beam plane 31. However, the other of at least two detection areas 21 is separated from one of at least two detection areas 21 by a blank area 22.

[0057] In the plurality of detection areas 21 and the plurality of blank areas 22, the main beam plane 31 passes through one of the detection areas 21, but the sizes of the detection areas on the left and right sides of the detection area 21 through which the main beam plane 31 passes are different. The other detection area 21 is adjacent to the right side of this one detection area 21, corresponding to the two detection areas 21 being closely joined, and for the main beam plane 31, the two detectors in the imaging area are asymmetrically arranged.

[0058] Note that "the sizes of the detection areas on the left and right sides of the detection area 21 through which the main beam plane 31 passes are different" described in the above embodiment refers to a physical difference, that is, a difference in the covered area.

[0059] According to an embodiment of the present application, at least one detector is included in the detection area 21, and the size of the blank area 22 is equal to or larger than the size of one detector pixel.

[0060] The blank area 22 is formed by two adjacent detection areas 21 being spaced apart, and the size of the blank area 22 represents the distance between the two adjacent detection areas. This distance is equal to or larger than the size of one detector pixel in the detection area 21. For example, when the size of the detector pixel in the detection area 21 is 0.1 mm × 0.1 mm, the size of the blank area is 0.1 mm or more.

[0061] According to an embodiment of the present application, the CT imaging system 1000 has a first position where the radiation beam covers the first blank area 221 and a second position where the radiation beam covers the first detection area 211, and the image data output from the first position and the image data output from the second position are the same.

[0062] To further explain the principle of complementing lost data by spatial complementation in the present application, in the CT imaging system 1000, two representative positions are The radiation beam the first position covering the first blank area 221 and the second position where the radiation beam covers the first detection area 211.

[0063] For easier understanding, in FIGS. 3 and 4, a blank area 22 is shown, the filled area is the detection area 21, and the blank area is the blank area 22. Actually, the blank area 22 is a position where no detector is provided between the two detection areas 21.

[0064] As shown in FIG. 3, at the first position of the CT imaging system 1000, the radiation source unit 10 emits a radiation beam above the scanning channel 200, the detector unit 20 receives the radiation beam below the scanning channel 200, the detector unit 20 includes, in order from left to right, a first detection area 211, a second detection area 212, and a first blank area 221, and the radiation beam can cover the first detection area 211, the second detection area 212, and the first blank area 221.

[0065] At the first position, since detectors are mounted in both the first detection area 211 and the second detection area 212, imaging can be performed in both areas. Since there is no detector in the first blank area 221, there is no data here.

[0066] As shown in FIG. 4, the second position of the CT imaging system 1000 is obtained by rotating the CT imaging system 1000 counterclockwise from the first position to the second position. The radiation source unit 10 emits a radiation beam at the lower left of the scanning channel 200, and the detector unit 2 receives the radiation beam at the upper right of the scanning channel 200. The detector unit 2 includes, in order from bottom to top, a first detection area 211, a second detection area 212, and a first blank area 221, and the radiation beam can cover the first detection area 211, the second detection area 212, and the first blank area 221.

[0067] At the second position, since detectors are mounted in both the first detection area 211 and the second detection area 212, imaging can be performed in both areas. Since there is no detector in the first blank area 221, there is no data here.

[0068] As can be seen by comparing the first position and the second position, the imaging data obtained by the radiation source unit 10 and the first detection area 211 at the first position is the same as the imaging data obtained by the radiation source unit 10 and the first blank area 221 at the second position. The data not present in the first blank area 221 at the second position can be complemented by the first detection area 211 at the first position. Data complementation can be achieved, and complete data required for the detection object 100 can be created.

[0069] In the present application, the intervals between the detection areas 21 are not limited. The intervals between two adjacent detection areas 21 may not all be equal, or some of the intervals between two adjacent detection areas 21 may not be equal, or all of the intervals between two adjacent detection areas 21 may be equal.

[0070] Here, the interval is the length in the second direction between two adjacent detection areas 21.

[0071] In one embodiment, the intervals between two adjacent detection areas 21 are all equal.

[0072] In order to be advantageous for calculating the number of detectors in the detector unit 20 and the arrangement position of each detector, the intervals between two adjacent detection areas 21 are all equal, that is, the length distances in the second direction of two adjacent detection areas 21 are all equal.

[0073] In the present application, the over-areas of the detection areas 21 are not limited. The over-areas of the detection areas 21 may be completely different, or some of the over-areas of the detection areas 21 may be different, or the over-areas of the detection areas 21 may all be equal.

[0074] Here, the over area is the product of the length in the second direction and the length in the third direction of each detection area 21. Note that even if the over area of two detection areas 21 is the same, the length in the second direction and the length in the third direction of these two detection areas 21 may be different.

[0075] The third direction is understood to be a radial direction with the radiation source unit 10 as its center, and the third direction is perpendicular to both the second direction and the first direction.

[0076] In one embodiment, the overall area of the sensing area 21 in the second direction is equal to one another.

[0077] In order to facilitate calculation of the number of detectors in the detector unit 20 and the arrangement positions of the detectors, the detection areas 21 are all equal in area and length in the second direction.

[0078] According to one embodiment of the present application, the detector units 20 are arranged in a plurality of rows, and the plurality of rows of detector units 20 are aligned in a first direction.

[0079] Of course, the present application is not limited to the number of rows of the detector units 20, and the detector units 20 in the above-described embodiment may be implemented in multiple rows in the first direction, which can be applied to spiral CT scanning, save inspection time, and improve work efficiency.

[0080] According to one embodiment of the present application, the radiation beam includes a first exit angle 32 and a second exit angle 33, and the range covered by the first exit angle 32 and the second exit angle 33 is the exit range of the radiation beam.

[0081] As shown in FIG. 2, in the imaging area formed by the radiation beam, the dotted line in the middle is the main beam plane 31, the angle formed by the dotted line on the left side and the main beam plane 31 is the first emission angle 32, and the angle formed by the dotted line on the right side and the main beam plane 31 is the second emission angle 33. The emission ranges covered by the first emission angle 32 and the second emission angle 33 together form the field of view range of the CT imaging system 1000 of the present application, which is the emission range of the radiation beam. When the CT imaging system 1000 rotates once, it can complete the acquisition of all images of the detection object 100.

[0082] According to an embodiment of the present application, at least two detection areas 21 are covered within the emission range.

[0083] In order to meet the conditions of high resolution and high speed while satisfying the wide imaging field of view of the present application, the emission range must cover at least two detection areas 21. That is, even the minimum emission range must cover a range including two detection areas 21 and one blank area 22 between these two detection areas 21. Since there is a blank area 22 in the covered range of the emission range, the number of detectors used can be reduced, the cost of the CT imaging system 1000 can be reduced, and through spatial complementation, during rotational scanning, the data of the blank area 22 can be acquired by the two detection areas 21, and complete image data can be obtained. The specific principle has been described above, so it will not be repeated here.

[0084] According to an embodiment of the present application, the CT imaging system 1000 further includes a mounting stage 400 slidably provided in the scanning channel 200 so that the detection object 100 enters and exits the CT imaging system 1000 through the scanning channel 200.

[0085] The mounting stage 400 is connected to a feed screw, and the object to be detected 100 is placed on the mounting stage 400. The driving device drives the mounting stage 400 via the feed screw, and the mounting stage 400 pushes the object to be detected 100 to move within the scanning channel 200. The feed screw allows the object to be detected 100 to be accurately positioned by the radiation beam of the CT imaging system 1000, effectively solving the problem of insufficient positioning precision of the transmission system of the detection equipment and meeting the requirements for image detection quality of certain products.

[0086] According to one embodiment of the present application, an adjustment platform 300 for adjusting the attitude of the object 100 to be detected is provided between the mounting stage 400 and the object 100 to be detected.

[0087] The adjustment platform 300 of the present application is used to adjust the movement posture of the detection object 100 being transmitted to the production line, and is also used in the field of radiation detection to adjust the detection object 100 to a predetermined detection position.

[0088] In the description herein, terms such as "one embodiment," "some embodiments," "examples," "embodiment," or "some examples" mean that the specific features, structures, materials, or particularities described in connection with that embodiment or example are included in at least one embodiment or example of the present application. References to such terms in this specification do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or particularities described may be combined in any suitable manner in any one or more embodiments or examples.

[0089] Although several embodiments according to the general technical concept of the present disclosure have been shown and described, those skilled in the art will understand that modifications can be made to these embodiments without departing from the principle and spirit of the general technical concept of the present disclosure. The scope of the present disclosure is limited by the claims and their equivalents.

Claims

1. A CT imaging system, comprising: A scanning channel arranged along a first direction, through which an object to be detected enters and exits the CT imaging system; A radiation source unit provided on one side of the scanning channel for emitting a radiation beam; A detector unit provided on the other side of the scanning channel, provided opposite to the radiation source unit for receiving the radiation beam; The radiation beam forms an imaging area between the radiation source unit and the detector unit; The detector unit includes at least two detection areas and one blank area; The imaging area has a main beam plane that extends through the radiation source unit; The positions of the detection areas and the blank area are complementary with respect to the main beam plane, and the distances between the positions of the detection areas and the main beam plane, and the distances between the positions of the blank areas paired with the detection areas and the main beam plane are the same; A CT imaging system characterized by the above.

2. One of the at least two detection areas is provided on the main beam plane; The other of the at least two detection areas is provided on one side of the one; The CT imaging system according to Claim 1, characterized by the above.

3. One of the at least two detection areas is provided on the main beam plane and is equally divided by the main beam plane; The CT imaging system according to Claim 2, characterized by the above.

4. The other of the at least two detection areas is adjacent to one of the at least two detection areas; The CT imaging system according to Claim 2, characterized by the above.

5. The other of the at least two detection areas is separated from one of the at least two detection areas by the blank area; The CT imaging system according to Claim 2, characterized by the above.

6. At least one detector is included in the detection area; The size of the blank area is equal to or larger than the size of one detector pixel; The CT imaging system according to any one of Claims 1 to 5, characterized by the above.

7. The CT imaging system has a first position where the radiation beam covers a first blank area and a second position where the radiation beam covers a first detection area, and the image data output from the first position is the same as the image data output from the second position. The CT imaging system according to claim 1, characterized in that.

8. A plurality of rows of the detector units are provided, and the plurality of rows of the detector units are arranged in a first direction. The CT imaging system according to claim 1, characterized in that.

9. The radiation beam includes a first emission angle and a second emission angle, and the range covered by the first emission angle and the second emission angle is the emission range of the radiation beam. The CT imaging system according to claim 1, characterized in that.

10. At least two detection areas are covered within the emission range. The CT imaging system according to claim 9, characterized in that.

11. The CT imaging system further includes a mounting stage slidably provided on the scanning channel so that the object to be detected enters and exits the CT imaging system through the scanning channel. The CT imaging system according to claim 1, characterized in that.

12. An adjustment platform for adjusting the posture of the object to be detected is provided between the mounting stage and the object to be detected. The CT imaging system according to claim 11, characterized in that.

Images