CN114947921A - CT device - Google Patents

Abstract

The present disclosure relates to a CT device, comprising: a cylindrical casing capable of rotating around its axis; a first subsystem, disposed in the casing, comprising a first x-ray source and a first detector, wherein the first x-ray The source and the first detector are arranged on the inner wall of the casing diametrically opposite; the second subsystem, arranged in the casing, includes a second x-ray source and a second detector, wherein the second x-ray source and The second detector is slidably disposed on the inner wall side of the housing diametrically opposite, and the connection direction of the first x-ray source and the first detector is in the same direction as the connection direction of the second x-ray source and the second detector. a predetermined angle; and an actuator disposed within the housing and configured to move the second subsystem relative to the first subsystem in an axial direction of the housing.

Description

CT device

technical field

The present disclosure relates to the medical field, and more particularly, to a CT device.

Background technique

In high-end CT devices, there are two device designs, namely, dual-source CT devices with high temporal resolution and single-source wide-body CT devices with large z coverage (eg, 12 cm-16 cm). For both devices, there are various strengths and weaknesses in clinical application.

For example, dual-source CT devices can obtain CT images with high temporal resolution, but may result in staircase artifacts in the CT images due to limited z coverage, such as in cardiac scans.

The single-source wide-body CT device has a wide z coverage, but it also has the following problems: the temporal resolution is not high. The time is still too long for the patient; for single-source wide-body CT devices, cone-beam artifacts in CT images are very severe due to the large z-coverage; helical scanning and detection in full z-coverage mode is unlikely Yes, under normal circumstances, a single-source wide-body CT device can only work within a z-coverage range of 6 cm to 8 cm.

To overcome the limitation of z-coverage in dual-source CT setups, the size of the detectors in dual-source CT setups can be increased, however, cone-beam artifacts become very severe and the cost increases dramatically as the size of the detector increases .

In order to overcome the limitation of temporal resolution in the single-source wide-body CT device, the rotation speed of the single-source wide-body CT device can be increased. However, a small increase in rotation speed will cause a huge increase in centrifugal force, which requires very high strength of the rotating parts, otherwise there will be potential safety risks for the x-ray tube of the single-source wide-body CT device and the patient.

SUMMARY OF THE INVENTION

In view of the status and deficiencies of the prior art, the purpose of the present disclosure is to provide a CT device that can not only provide a dual-source mode but also a dual-source wide-body mode, and in the dual-source mode, high temporal resolution can be achieved, In the dual-source wide-body mode, a large z coverage can be achieved, while cone beam artifacts can be reduced, the quality of CT images can be improved, and the mode switching operation is convenient and simple.

According to an aspect of the embodiments of the present disclosure, there is provided a CT apparatus, comprising: a cylindrical casing capable of rotating around its axis; a first subsystem disposed in the casing and including a first x-ray source and a first detector a device, wherein the first x-ray source and the first detector are arranged on the inner wall of the casing diametrically opposite; the second subsystem, arranged in the casing, includes a second x-ray source and a second detector, wherein, The second x-ray source and the second detector are arranged diametrically opposite to the inner wall side of the housing in a slidable manner, and the connection direction of the first x-ray source and the first detector is the same as that of the second x-ray source and the second detector. The connecting direction of the actuator forms a predetermined angle; and the actuator is disposed in the housing and configured to be able to move the second sub-system relative to the first sub-system in the axial direction of the housing.

The second subsystem can be moved relative to the first subsystem by the actuator, so that the CT apparatus can provide at least two modes: dual-source mode and dual-source wide-body mode. In the dual-source mode, a high Temporal resolution, in the dual-source wide-body mode, can achieve large z coverage, reduce cone beam artifacts, improve CT image quality, and mode switching is convenient and simple.

In the CT apparatus according to the embodiment of the present disclosure, the first subsystem further includes a first beam limiter, and the first beam limiter is disposed on the side of the first x-ray source between the first x-ray source and the first detector, is configured to beam limit the first x-rays emitted from the first x-ray source before being detected by the first detector.

By setting the beam limiter, the quality of CT images can be further improved.

In the CT apparatus according to the embodiment of the present disclosure, the second subsystem further includes a second beam limiter, and the second beam limiter is disposed on the side of the second x-ray source between the second x-ray source and the second detector, is configured to limit the second x-rays from the second x-ray source before being detected by the second detector.

By setting the beam limiter, the quality of CT images can be further improved.

In the CT apparatus according to the embodiment of the present disclosure, the CT apparatus further includes: a support portion disposed between the inner walls of the housing along the connecting direction of the second x-ray source and the second detector, the second x-ray source and A second beam limiter is provided at one end of the support portion, and a second detector is provided at the other end of the support portion; and a connecting portion connects the support portion to the inner wall of the housing, wherein the support portion passes along the housing through the connecting portion The body slides in the axial direction, and the actuator is connected to the support portion and is configured to drive the support portion to slide along the axial direction of the housing.

The second subsystem is supported by the support portion, and the connecting portion slidably connects the support portion to the inner wall of the casing, so that the second subsystem can move relative to the first subsystem in the axial direction of the casing.

In the CT apparatus according to the embodiment of the present disclosure, the support portion is a plate-like structure with a central hole, the connecting portion connects the support portion to the inner wall of the housing at four corners of the plate-like structure, and the actuator is in the second detection The device side is connected to the support part.

One specific mounting configuration of the support, the connection and the actuator is provided.

In the CT apparatus according to an embodiment of the present disclosure, the support portion includes a first support portion and a second support portion that are diametrically opposed to each other, and the second x-ray source and the second beam limiter are disposed on the first support portion. , the second detector is arranged on the second support, the actuator includes a first actuator and a second actuator, the first actuator is arranged on the first support to drive the first support along the The housing slides in the axial direction, the second actuator is disposed on the second support part to drive the second support part to slide along the axial direction of the housing, wherein the first actuator and the second actuator are controlled synchronously .

A specific mounting configuration of the support, the second subsystem, and the actuator is provided.

In the CT apparatus according to an embodiment of the present disclosure, the connecting portion includes: a linear rail fixed to an inner wall of the casing along an axial direction of the casing; and a linear bushing fixed to the casing along an axial direction of the casing The corner edge of the support portion, wherein the linear bush is sleeved on the linear track.

The specific configuration form of the connection part is provided.

In the CT apparatus according to the embodiment of the present disclosure, the first x-ray source and the first detector are fixed on the inner wall of the casing, and the predetermined angle is in the range of 85 degrees to 95 degrees.

The first x-ray source and the first detector are fixed on the inner wall of the housing, and only the second subsystem is moved, so that the movement of the second subsystem relative to the first subsystem is structurally easier to achieve.

In the CT apparatus according to the embodiment of the present disclosure, the widths of the first detector and the second detector in the axial direction of the casing are the same.

The same width of the first detector and the second detector in the axial direction of the housing facilitates the realization of the dual-source mode.

In the CT apparatus according to the embodiment of the present disclosure, the widths of the first detector and the second detector in the axial direction of the casing are 6 cm to 8 cm.

Specific examples of first detector and second detector widths are provided.

Description of drawings

The accompanying drawings described herein are used to provide further understanding of the present disclosure and constitute a part of the present disclosure. The exemplary embodiments of the present disclosure and their descriptions are used to explain the present disclosure and do not constitute an improper limitation of the present disclosure. In the attached image:

FIG. 1 shows a block diagram of a CT apparatus according to an embodiment of the present disclosure.

FIG. 2 shows a specific structure of a CT apparatus according to an embodiment of the present disclosure.

FIG. 3 shows another specific structure of a CT apparatus according to an embodiment of the present disclosure.

FIG. 4 shows a graph showing the variation of the distance between the first detector and the second detector as the actuator is driven.

5 is a diagram illustrating an x-ray beam configuration of a CT apparatus operating in a dual-source mode according to an embodiment of the present disclosure.

FIG. 6 shows an x-ray beam configuration diagram of a CT apparatus operating in a dual-source wide-body mode according to an embodiment of the present disclosure.

Among them, the reference numerals are as follows:

100: CT device;

101: shell;

103: the first subsystem;

105: the second subsystem;

107: actuator;

1031: the first x-ray source;

1032: the first beam limiter;

1033: the first detector;

1051: a second x-ray source;

1052: the second beam limiter;

1053: the second detector;

107: actuator;

109: support part;

111: connecting part;

1111: Linear track;

1113: Linear bushing;

1091: The first support

1092: Second support part

1071: the first actuator;

1072: Second Actuator.

Detailed ways

The technical solutions in the embodiments of the present disclosure will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present disclosure. Obviously, the described embodiments are only a part of the embodiments of the present disclosure, but not all of the embodiments. Based on the embodiments in the present disclosure, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present disclosure.

The present disclosure provides a CT apparatus. FIG. 1 shows a block diagram of a CT apparatus according to an embodiment of the present disclosure, FIG. 2 shows a specific structure of the CT apparatus according to an embodiment of the present disclosure, and FIG. 3 shows another aspect of the CT apparatus according to an embodiment of the present disclosure. a specific structure. For simplicity, only the components related to the inventive point are schematically shown in FIGS. 2 and 3 , and the illustration of the components irrelevant to the inventive point is omitted.

The CT apparatus according to the embodiment of the present disclosure will be described below with reference to FIGS. 1 to 3 .

As shown in FIG. 1 , the CT apparatus 100 according to an embodiment of the present disclosure includes a housing 101 , a first subsystem 103 , a second subsystem 105 , and an actuator 107 .

Specifically, as shown in FIG. 2 and FIG. 3 , the housing 101 is a cylindrical structure that can rotate around its axis. The housing 101 is typically made of an aluminum casting, but the present disclosure is not so limited, and any material with sufficient strength may be used to form the housing 101 .

The first subsystem 103 is arranged in the casing 101 , which includes a first x-ray source 1031 and a first detector 1033 , and the first x-ray source 1031 and the first detector 1033 are arranged diametrically opposite to the inner wall of the casing 101 superior. Specifically, the connecting line between the first x-ray source 1031 and the first detector 1033 intersects the axis of the cylindrical casing 101 , that is, the first x-ray source 1031 and the first detector 1033 are arranged in the cylindrical casing 101 . on one inner diameter of the housing 101 . The first x-ray source 1031 and the first detector 1033 may be fixed on the inner wall of the housing 101 .

The first x-ray source 1031 may be, for example, an x-ray tube, and the first detector 1033 detects the x-rays emitted from the first x-ray source 1031, and sends the detected data to the processor for subsequent processing.

As shown in FIGS. 2 and 3 , optionally, the first subsystem 103 may further include a first beam limiter 1032 disposed between the first x-ray source 1031 and the first detector 1033 and close to the first x-rays Source 1031 side. The first beam limiter 1032 limits the x-rays emitted from the first x-ray source 1031 before the x-rays are detected by the first detector 1033, thereby further improving the CT image quality. The first beam limiter 1032 may be an x-ray tube beam limiter.

The second subsystem 105 is arranged in the housing 101 , and includes a second x-ray source 1051 and a second detector 1053 , and the second x-ray source 1051 and the second detector 1053 are arranged diametrically opposite to the inner wall of the housing 101 superior. Specifically, the connecting line between the second x-ray source 1051 and the second detector 1053 intersects the axis of the cylindrical casing 101, that is, the second x-ray source 1051 and the second detector 1053 are arranged in the cylindrical casing 101. on the other inner diameter of the housing 101 . In the embodiment of the present disclosure, preferably, the inner diameter of the first x-ray source 1031 and the first detector 1033 and the inner diameter of the second x-ray source 1051 and the second detector 1053 are perpendicular to each other, but the present disclosure is not limited to Therefore, the inner diameter of the first x-ray source 1031 and the first detector 1033 and the inner diameter of the second x-ray source 1051 and the second detector 1053 may form other angles, for example, the angle is in the range of 85 degrees to 95 degrees Inside.

The second x-ray source 1051 may be, for example, an x-ray tube, and the second detector 1053 detects the x-rays emitted from the second x-ray source 1051, and sends the detected data to the processor for subsequent processing.

As shown in FIGS. 2 and 3 , optionally, the second subsystem 105 may further include a second beam limiter 1052 disposed between the second x-ray source 1051 and the second detector 1053 close to the second x-ray Source 1051 side. The second beam limiter 1052 limits the x-rays emitted from the second x-ray source 1051 before they are detected by the second detector 1053, thereby further improving the CT image quality. The second beam limiter 1052 may be an x-ray tube beam limiter.

The actuator 107 is provided in the housing 101 and is configured to be capable of systematically moving the second subsystem 105 relative to the first subsystem 103 in the axial direction of the housing 101 . The actuator 107 may be a linear actuator.

As shown in FIGS. 2 and 3 , the CT apparatus 100 may further include a support part 109 and a connection part 111 .

The support portion 109 is disposed between the inner walls of the casing 101 along the connecting line direction of the second x-ray source 1051 and the second detector 1053 (ie, another inner diameter direction of the casing 101 ). The second x-ray source 1051 and the second beam limiter 1052 are disposed at one end of the support portion 109 and close to the inner wall of the housing 101 . The second detector 1053 is disposed at the other end of the support portion 109 and is close to the inner wall of the housing 101 .

The connection part 111 connects the support part 109 to the inner wall of the housing 101 . The support portion 109 slides along the axial direction of the housing 101 through the connection portion 111 . The actuator 107 is connected to the support portion 109 and is configured to drive the support portion 109 to slide along the axial direction of the housing 101 .

FIG. 2 shows a specific installation configuration of the support portion, the connection portion, and the actuator.

Specifically, as shown in FIG. 2 , the support portion 109 is a plate-like structure with a hole in the center, the connecting portion 111 connects the support portion 109 to the inner wall of the housing at the four corners of the plate-like structure, and the actuator 107 is in the first The two detectors 1053 are connected to the support portion 109 .

The connection part 111 may include a linear rail 1111 and a linear bushing 1113 . The linear rail 1111 is fixed to the inner wall of the housing along the axial direction of the housing 101 , the linear bushing 1113 is fixed to the corner edge of the support part 109 along the axial direction of the housing 101 , and the linear bushing 1113 is sleeved on the linear rail 1111 so that the support part 109 can move along the axis direction of the casing 101 under the driving of the actuator 107 , so as to realize the relative movement of the second subsystem 105 and the first subsystem 103 in the axis direction of the casing 101 .

The mounting arrangement of the support portion, the connection portion, and the actuator is not limited to the above-mentioned form. Another form of the mounting configuration of the support portion, the connection portion, and the actuator is shown in FIG. 3 .

Specifically, as shown in FIG. 3 , the support portion 109 includes a first support portion 1091 and a second support portion 1092 that are diametrically opposed and provided separately, that is, there is no part of the support portion 109 in the central portion of the housing 101 . . Both the first support portion 1091 and the second support portion 1092 are disposed close to the inner wall of the housing 101 .

The actuator 107 includes a first actuator 1071 and a second actuator 1072 .

The first support portion 1091 and the second support portion 1092 are both plate-like structures. The first support portion 1091 has two linear bushings 1113 on the two corner edges of its plate-like structure near the inner wall of the housing 101 respectively, and the two linear bushings 1113 are respectively sleeved and fixed along the axial direction of the housing 101 . On the two linear rails 1111 of the inner wall of the casing 101 , the first actuator 1071 is provided on the first supporting part 1091 on the side close to the central part of the casing 101 , and can drive the first supporting part 1091 along the direction of the casing 101 . Sliding in the direction of the axis. The second support portion 1091 has two linear bushings 1113 on two corner edges of its plate-like structure close to the inner wall of the housing 101 respectively, and the two linear bushings 1113 are respectively sleeved and fixed along the axis of the housing 101 . On the two linear rails 1111 of the inner wall of the housing 101 , the second actuator 1072 is provided on the second supporting part 1092 near the center portion side of the housing 101 , and can drive the second supporting part 1092 along the direction of the housing 101 . Sliding in the direction of the axis.

The second x-ray source 1051 and the second beam limiter 1052 are arranged on the first supporting part 1091 , and the second detector 1053 is arranged on the second supporting part 1092 . The first actuator 1071 and the second actuator 1072 are controlled synchronously to keep the second x-ray source 1051 , the second beam limiter 1052 and the second detector 1053 of the moved second subsystem 105 in a straight line superior.

The widths of the first detector 1033 and the second detector 1053 in the axial direction of the casing 101 are preferably the same, for example, both may be 6 cm˜8 cm. However, the disclosure is not limited thereto, and the widths of the first detector 1033 and the second detector 1053 in the axial direction of the housing 101 may be different, and may be selected as required.

In the above embodiment, the example in which the connecting portion is constituted by the linear rail and the linear bush is described, but the present disclosure is not limited thereto, and the connecting portion may be constituted by the linear rail and, for example, a double V-shaped bearing. Through this structure, the second subsystem can perform precise linear movement in the axial direction of the housing, and at the same time, such a structure can bear loads in various directions.

In the above embodiments, the linear actuator is used to move the second sub-system relative to the first sub-system in the axial direction of the housing, however, the present disclosure is not limited to this, and a lead screw, hydraulic drive, etc. The second subsystem moves relative to the first subsystem in the axial direction of the housing.

In the above embodiments, although not specifically described, it should be noted that the circular opening in the central portion of the cylindrical casing in FIGS. 2 and 3 represents the place where the object to be examined is brought into or moved out of the CT apparatus during the CT examination. Through the opening, the circular plate with the circular opening can be used to support other components of the CT apparatus. In addition, the first subsystem may be connected to the inner wall of the housing through support ribs not shown in the figures. Since the invention of the present disclosure does not lie in the circular plate and the supporting rib, the circular plate and the supporting rib are not described in detail.

For a better understanding of the present disclosure, the following will specifically describe the operation mode switching of the CT apparatus according to the embodiment of the present disclosure. FIG. 4 shows a graph showing the variation of the distance between the first detector and the second detector as the actuator is driven. 5 is a diagram illustrating an x-ray beam configuration of the CT apparatus according to an embodiment of the present disclosure operating in a dual-source mode, and FIG. 6 illustrates an x-ray beam configuration of the CT apparatus according to an embodiment of the present disclosure operating in a dual-source wide-body mode Beam configuration diagram.

Hereinafter, for the convenience of description, the axial direction of the housing 101 is described as the z direction, the widths of the first detector and the second detector in the CT apparatus in the z direction are described as the z coverage and assuming they are equal, the The plane of the radial direction of the housing 101 is described as the phi plane, where the z direction is perpendicular to the phi plane.

In the CT apparatus according to the embodiment of the present disclosure, the distance in the z direction between the first subsystem 103 and the second subsystem 105 can be changed by moving the second subsystem 105 by the actuator.

FIG. 4 shows that the distance between the first detector 1033 in the first subsystem 103 and the second detector 1053 in the second subsystem 105 changes in the z-direction as the actuator is driven. (A) of FIG. 4 shows that the distance between the first detector 1033 and the second detector 1053 in the z direction is smaller than the z coverage, and the first detector 1033 and the second detector 1053 cover the z direction Partially overlapping; FIG. 4(B) shows that the distance in the z direction between the first detector 1033 and the second detector 1053 in the z direction is greater than the z coverage, and the first detector 1033 and the second detector 1053 in the z direction spaced above; FIG. 4(C) shows that the distance between the first detector 1033 and the second detector 1053 in the z direction is equal to the z coverage, and the first detector 1033 and the second detector 1053 are in the z direction Just connected, at this time, the CT device is said to be in dual-source wide-body mode; (D) of FIG. 4 shows that the distance between the first detector 1033 and the second detector 1053 in the z direction is 0, at this time, it is called CT The device is in dual source mode.

The CT device can be switched between the dual-source mode and the dual-source wide-body mode by driving the actuator as required.

For example, in a clinical scan, if a patient has a severe arrhythmia, a CT device with high temporal resolution is required to image the patient's heart with high quality. At this time, the CT apparatus can be switched to the dual source mode shown in (D) of FIG. 4 .

As shown in FIG. 5 , in the dual-source mode, the first detector 1033 of the first subsystem of the CT apparatus and the second detector 1053 of the second subsystem are in the same position in the z-direction, and the first x-ray source 1031 The emitted x-ray beam A and the x-ray beam B emitted by the second x-ray source 1051 are on the same φ plane, so as to image the same slice part of the heart.

Since the first sub-system and the second sub-system are vertically arranged on the same φ plane, compared with the single-source CT device that needs to perform 180-degree scanning to complete the scan of one slice, the CT device according to the embodiment of the present disclosure operates in a dual-source CT device. In the source mode, only a 90-degree scan is required to complete the scan of a slice, so that the time resolution is twice that of a single-source CT device. In dual-source mode, high-quality CT images can be obtained with high temporal resolution.

For example, in a clinical scan, if the scan performed is an enhanced scan, the scan should be performed in the presence of a contrast agent. Without moving the scanning bed, in this case, the CT apparatus according to the present disclosure can be switched to the dual-source wide-body mode shown in (C) of FIG. 4 .

As shown in FIG. 6 , in the dual-source wide-body mode, the first detector 1033 of the first subsystem of the CT apparatus and the second detector 1053 of the second subsystem are just connected back and forth in the z direction, and the first x-ray The x-ray beam A emitted by the source 1031 and the x-ray beam B emitted by the second x-ray source 1051 just continuously irradiate the inspection object in the z direction, so that the inspection object can be scanned and imaged with a wide imaging area.

In the dual-source wide-body mode, since the first sub-system and the second sub-system are vertically arranged on different φ planes, different first x-ray sources 1031 and second x-ray sources 1051 are used to separate directions relative to the single source. The first detector 1033 and the second detector 1053 with narrow z coverage (for example, 6 cm to 8 cm) of the wide-body CT device (z coverage range of 12 cm to 16 cm) emit scanning x-rays, therefore, both the z direction is realized. Scanning with a wide z coverage range reduces cone beam artifacts caused by the wide z coverage range, so that high-quality CT images can be obtained with a wide z coverage range.

The CT apparatus according to the embodiment of the present disclosure can provide at least two operating modes, a dual-source mode and a dual-source wide-body mode, which can provide higher temporal resolution than a single-source wide-body CT apparatus, and a higher temporal resolution than any existing dual-source CT. Device wider z coverage.

Additionally, when a CT apparatus according to the present disclosure operates in a dual-source wide-body mode, the two subsystems operate with different scan parameters, since the taper angles of the two subsystems are that of a single-source wide-body CT apparatus with the same z coverage. half, thereby reducing cone beam artifacts, allowing helical scans to be performed in full z-coverage mode.

In the above-mentioned embodiments of the present disclosure, the description of each embodiment has its own emphasis. For parts that are not described in detail in a certain embodiment, reference may be made to the relevant descriptions of other embodiments.

The above are only the preferred embodiments of the present disclosure. It should be pointed out that for those skilled in the art, without departing from the principles of the present disclosure, several improvements and modifications can be made. It should be regarded as the protection scope of the present disclosure.

Claims (10)

1. A CT device (100), characterized in that, comprising: a cylindrical casing (101), rotatable around its axis; A first subsystem (103), disposed in the housing, includes a first x-ray source (1031) and a first detector (1033), wherein the first x-ray source (1031) and the first x-ray source (1031) The detector (1033) is arranged on the inner wall of the casing (101) diametrically opposite; A second subsystem (105), disposed in the housing (101), includes a second x-ray source (1051) and a second detector (1053), wherein the second x-ray source (1051) and The second detector (1053) is slidably disposed on the inner wall side of the housing (101) diametrically opposite, the first x-ray source (1031) and the first detector (1033) The connecting line direction of the second x-ray source (1051) and the connecting line direction of the second detector (1053) form a predetermined angle; and An actuator (107), disposed within the housing (101), configured to cause the second subsystem (105) to be relative to the first in the axial direction of the housing (101) Subsystem (103) moves. 2. The CT apparatus (100) according to claim 1, wherein the first subsystem (103) further comprises a first beam limiter (1032), the first beam limiter (1032) is provided On the side of the first x-ray source between the first x-ray source (1031) and the first detector (1033), configured to The emitted first x-rays are beam-limited before being detected by the first detector (1033). 3. The CT apparatus (100) according to claim 1 or 2, wherein the second subsystem (105) further comprises a second beam limiter (1052), the second beam limiter (1052) ) is disposed on the side of the second x-ray source between the second x-ray source (1051) and the second detector (1053), and is configured to The emitted second x-rays are beam-limited before being detected by the second detector (1053). 4. The CT device (100) according to claim 3, characterized in that, further comprising: A support part (109) is provided between the inner walls of the casing (101) along the connecting line direction of the second x-ray source (1051) and the second detector (1053), and the second x-ray source (1051) The x-ray source (1051) and the second beam limiter (1052) are arranged at one end of the support part (109), and the second detector (1053) is arranged at the other end of the support part (109) ;as well as a connecting part (111), connecting the supporting part (109) to the inner wall of the casing (101), wherein the supporting part (109) passes the connecting part (111) along the casing (109). 101), the actuator (107) is connected to the support portion (109) and is configured to drive the support portion (109) to slide along the axis direction of the housing (101). 5. The CT device (100) according to claim 4, characterized in that, The supporting part (111) is a plate-like structure with a central hole, and the connecting parts (111) connect the supporting part (109) to the casing (101) at four corners of the plate-like structure ), the actuator (107) is connected to the support portion (109) on the side of the second detector (1053). 6. The CT device (100) according to claim 4, characterized in that, The support part (109) comprises a first support part (1091) and a second support part (1092) which are arranged diametrically opposite to each other, the second x-ray source (1051) and the second beam limiter ( 1052) is arranged on the first support part (1091), the second detector (1053) is arranged on the second support part (1092), The actuator (107) includes a first actuator (1071) and a second actuator (1072), and the first actuator (1071) is provided on the first support portion (1091) to The first support part (1091) is driven to slide along the axial direction of the casing (101), and the second actuator (1072) is provided on the second support part (1092) to drive the The second support part (1092) slides along the axial direction of the housing (101), wherein the first actuator (1071) and the second actuator (1072) are controlled synchronously. 7. The CT device (100) according to claim 4, characterized in that, The connecting part (111) includes: a linear rail (1111) fixed to the inner wall of the housing (101) along the axial direction of the housing (101); and Linear bushings (1113) fixed to the corner edges of the support (109) along the axial direction of the housing (101), Wherein, the linear bush (1113) is sleeved on the linear track (1111). 8. The CT device (100) according to claim 1, characterized in that, The first x-ray source (1031) and the first detector (1033) are fixed on the inner wall of the housing (101), and the predetermined angle is in the range of 85 degrees to 95 degrees. 9. The CT device (100) according to claim 1, characterized in that, The widths of the first detector (1033) and the second detector (1053) in the axial direction of the casing (101) are the same. 10. The CT device (100) according to claim 9, characterized in that, The widths of the first detector (1033) and the second detector (1053) in the axial direction of the casing (101) are 6 cm to 8 cm.

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