阅读说明：本技术 一种平行x射线ct成像装置 (Parallel X-ray CT imaging device ) 是由 贡志锋 马艳玲 高建波 张书彦 詹霞 王晨 张鹏 于 2020-06-05 设计创作，主要内容包括：本发明公开了一种平行X射线CT成像装置,包括：X射线管；X射线导管,包括一段抛物线聚焦导管和一段直线导管,直线导管内部布置有金属格栅；导管支架,固定设置在所述X射线导管的底部；用于接收X射线的高精度探测器。X射线管设置在所述抛物线聚焦导管的一侧,X射线管的光源位于抛物线聚焦导管的所在抛物线的焦点上。通过将点散射光反射为平行光,成像分辨率由探测器分辨率决定,而不由射线管的靶焦点尺寸决定,本发明采用高精度探测器即可达到高成像分辨率,因此可以采用大功率X射线管作为射线源穿透较厚的样品,缩短成像时间,大幅提高检测效率。(The invention discloses a parallel X-ray CT imaging device, comprising: an X-ray tube; the X-ray guide pipe comprises a section of parabolic focusing guide pipe and a section of linear guide pipe, and a metal grid is arranged in the linear guide pipe; the catheter bracket is fixedly arranged at the bottom of the X-ray catheter; a high-precision detector for receiving X-rays. An X-ray tube is arranged on one side of the parabolic focusing catheter, and a light source of the X-ray tube is positioned on a focus of a parabola of the parabolic focusing catheter. By reflecting point scattered light into parallel light, the imaging resolution is determined by the resolution of a detector but not by the size of a target focus of a ray tube, and the high-precision detector is adopted to achieve high imaging resolution, so that a high-power X-ray tube can be used as a ray source to penetrate through a thicker sample, the imaging time is shortened, and the detection efficiency is greatly improved.)

1. A parallel X-ray CT imaging apparatus, comprising:

an X-ray tube as an emission source;

the X-ray guide pipe comprises a section of parabolic focusing guide pipe and a section of linear guide pipe, wherein the parabolic focusing guide pipe is a hollow parabolic revolving body, the linear guide pipe is cylindrical, and a metal grid is arranged in the linear guide pipe; the parabolic focusing conduit and the linear conduit are integrally formed and are communicated with each other;

the catheter bracket is fixedly arranged at the bottom of the X-ray catheter;

a high-precision detector for receiving X-rays;

the X-ray tube is arranged on one side of the parabolic focusing guide tube, a light source of the X-ray tube is positioned at the focus of the parabola of the parabolic focusing guide tube, a sample to be detected is arranged on one side of the linear guide tube, and the high-precision detector is arranged on the other side of the sample opposite to the linear guide tube so as to receive X-rays emitted by the X-ray tube and sequentially passing through the X-ray guide tube and the sample.

2. The parallel X-ray CT imaging apparatus according to claim 1, wherein said parallel X-ray CT imaging apparatus further comprises a sample turret; the sample can be rotatably connected to the sample rotary seat.

3. The parallel X-ray CT imaging apparatus according to claim 2, further comprising an X-Y moving stage, the X-Y moving stage comprising a first slide rail assembly and a second slide rail assembly disposed perpendicularly to each other; the first slide rail assembly comprises a first slide rail, a first sliding table and a first lead screw motor for driving the first sliding table, and the second slide rail assembly comprises a second slide rail, a second sliding table and a second lead screw motor for driving the second sliding table; the second sliding rail is fixedly connected to the first sliding table, and the sample revolving base is fixedly connected to the second sliding table.

4. The parallel X-ray CT imaging apparatus according to claim 3, wherein said parallel X-ray CT imaging apparatus further comprises a base, said first slide rail being fixedly connected to said base.

5. The parallel X-ray CT imaging apparatus according to claim 4, further comprising a first side plate vertically disposed on said base, said X-ray tube being disposed on said first side plate.

6. The parallel X-ray CT imaging apparatus according to claim 5, further comprising a third slide rail assembly provided on said first side plate; the third slide rail assembly comprises a third slide rail and a third sliding table, the third slide rail is fixedly connected to the first side plate, and the X-ray tube is fixedly connected to the third sliding table.

7. The parallel X-ray CT imaging apparatus according to claim 4, wherein the parallel X-ray CT imaging apparatus further comprises a detector slide; the detector sliding table is connected to the first sliding rail and is positioned on the side part of the first sliding table; the high-precision detector is fixedly arranged on the first sliding table.

8. The parallel X-ray CT imaging apparatus according to claim 7, wherein said parallel X-ray CT imaging apparatus further comprises a second side plate and a fourth slide rail assembly; the second side plate is vertically arranged on the detector sliding table, the fourth sliding rail assembly comprises a fourth sliding rail and a fourth sliding table, the fourth sliding rail is fixedly connected to the second side plate, and the high-precision detector is fixedly connected to the fourth sliding table.

9. The parallel X-ray CT imaging apparatus according to claim 1, wherein said X-ray guide tube is a super mirror guide tube, and an inside of said super mirror guide tube is in a vacuum state.

10. The parallel X-ray CT imaging apparatus according to claim 9, wherein both end openings of said super mirror catheter are provided with aluminum alloy windows for sealing.

Technical Field

The invention relates to the field of CT imaging, in particular to an X-ray CT imaging device.

Background

In order to solve the detection of small samples such as circuit boards and 3D printing complex components, high-precision CT imaging of critical parts by using X-rays is generally required to know the conditions of internal structures and welding quality.

In the traditional industrial CT, an X-ray bulb tube is used as a ray source, and X rays emitted by the X-ray bulb tube penetrate through a sample to be detected and then reach a ray detector, so that CT imaging is realized. The quality of the CT image is affected by performance criteria and parameters such as resolution, noise, contrast, and image trajectory, while the spatial resolution is affected by the CT imaging geometry, one of the large geometric factors being the target focus size of the tube.

The conventional industrial CT principle determines: for X-ray tubes that emit point scattered radiation, the imaging resolution is directly affected by the size of the target focal spot of the tube. Because the bulb tube with a small focus generates narrower X rays, higher spatial resolution can be obtained, and the smaller the target focus size of the bulb tube is, the higher the imaging resolution is. The current industrial CT adopts point scattering type X-ray to image, the resolution is determined by the target focus size of a ray tube, but not by the precision of a detector, if the target focus size of a bulb tube is not changed, the imaging resolution cannot be improved, and even if the high-precision detector is adopted to image, the image quality is difficult to improve.

Therefore, to achieve higher accuracy of CT imaging, an X-ray tube with a smaller target focal spot size needs to be selected, which means a low power tube. The energy of the X-ray of the low-power ray tube is correspondingly lower, the thick sample is difficult to penetrate, and the detector needs to receive enough X-ray energy to realize clear imaging, so the imaging time of the low-power ray tube is very long, and the detection efficiency is low.

This problem can be solved by emitting X-rays in the form of parallel light. For the parallel light, the resolution of the detector is the most important factor (similar to the imaging principle of a common camera) influencing the imaging resolution, so if the point scattering type X-ray can be converted into the parallel light type X-ray, the imaging quality can be improved by selecting the high-precision detector, and the limitation of the focus size of the X-ray tube target is avoided. However, the X-ray tube is limited in its structure and emission principle, and cannot directly emit parallel rays. Currently, there is no relevant CT imaging detection device.

Disclosure of Invention

In order to overcome the defects of the prior art, the invention aims to provide a parallel X-ray CT imaging device, which converts point scattered light emitted by an X-ray tube into parallel light and receives X-rays by adopting a high-precision detector to complete high-precision CT imaging.

The invention is realized by adopting the following technical scheme:

a parallel X-ray CT imaging apparatus comprising: an X-ray tube as an emission source; the X-ray guide pipe comprises a section of parabolic focusing guide pipe and a section of linear guide pipe, wherein the parabolic focusing guide pipe is a hollow parabolic revolving body, the linear guide pipe is cylindrical, and a metal grid is arranged in the linear guide pipe; the parabolic focusing conduit and the linear conduit are integrally formed and are communicated with each other; the catheter bracket is fixedly arranged at the bottom of the X-ray catheter; a high-precision detector for receiving X-rays; the X-ray tube is arranged on one side of the parabolic focusing guide tube, a light source of the X-ray tube is positioned at the focus of the parabola of the parabolic focusing guide tube, a sample to be detected is arranged on one side of the linear guide tube, and the high-precision detector is arranged on the other side of the sample opposite to the linear guide tube so as to receive X-rays emitted by the X-ray tube and sequentially passing through the X-ray guide tube and the sample.

Further, the parallel X-ray CT imaging device also comprises a sample revolving seat; the sample can be rotatably connected to the sample rotary seat.

Furthermore, the parallel X-ray CT imaging device also comprises an X-Y moving platform, wherein the X-Y moving platform comprises a first slide rail component and a second slide rail component which are arranged vertically to each other; the first slide rail assembly comprises a first slide rail, a first sliding table and a first lead screw motor for driving the first sliding table, and the second slide rail assembly comprises a second slide rail, a second sliding table and a second lead screw motor for driving the second sliding table; the second sliding rail is fixedly connected to the first sliding table, and the sample revolving base is fixedly connected to the second sliding table.

Further, the parallel X-ray CT imaging device further comprises a base, and the first sliding rail is fixedly connected to the base.

Further, the parallel X-ray CT imaging apparatus further includes a first side plate vertically disposed on the base, and the X-ray tube is disposed on the first side plate.

Further, the parallel X-ray CT imaging device also comprises a third slide rail assembly arranged on the first side plate; the third slide rail assembly comprises a third slide rail and a third sliding table, the third slide rail is fixedly connected to the first side plate, and the X-ray tube is fixedly connected to the third sliding table.

Further, the parallel X-ray CT imaging device also comprises a detector sliding table; the detector sliding table is connected to the first sliding rail and is positioned on the side part of the first sliding table; the high-precision detector is fixedly arranged on the first sliding table.

Further, the parallel X-ray CT imaging device also comprises a second side plate and a fourth sliding rail component; the second side plate is vertically arranged on the detector sliding table, the fourth sliding rail assembly comprises a fourth sliding rail and a fourth sliding table, the fourth sliding rail is fixedly connected to the second side plate, and the high-precision detector is fixedly connected to the fourth sliding table.

Furthermore, the X-ray catheter is a super-scope catheter, and the inside of the super-scope catheter is in a vacuum state.

Further, two end openings of the super mirror catheter are provided with aluminum alloy windows for sealing.

Compared with the prior art, the invention can achieve the following beneficial effects:

after the X-rays enter the X-ray catheter: based on the optical principle of a parabola, the parabola focusing conduit section converts point scattering light into parallel light; the metal grating arranged in the linear guide pipe section can absorb X rays with overlarge scattering angles, reduce the scattering angles of the X rays of an incident sample and further homogenize parallel light; the two pipe sections cooperate to convert point scattering light into parallel light, and the parallel light is received by the high-precision detector after penetrating through the sample, so that high-definition imaging is formed.

Because the ray penetrating through the sample is parallel light, the imaging resolution is determined by the detector resolution and is not determined by the size of the target focus of the ray tube, and the imaging resolution can be improved by improving the detector resolution. Compared with the traditional industrial CT which needs to adopt an X-ray tube with small target focus size (low power), the X-ray tube can improve the imaging resolution, and the high-resolution X-ray tube can achieve high imaging resolution by adopting a high-precision detector, so that the high-power X-ray tube can be used as a ray source without influencing the imaging quality. The high-power X-ray tube has high ray energy and can penetrate through a thicker sample, so that the detection of the thick sample is effectively finished; meanwhile, the imaging time is shortened, and the detection efficiency is greatly improved.

Drawings

FIG. 1 is a perspective view of the present invention;

FIG. 2 is another perspective view of the present invention;

FIG. 3 shows a front view of an X-ray catheter;

FIG. 4 is a cross-sectional view taken along plane A-A of FIG. 3;

FIG. 5 is a cross-sectional view taken along line B-B of FIG. 3;

FIG. 6 is a schematic diagram of the imaging principle of the present invention using a parallel X-ray imaging mode;

FIG. 7 is a schematic view of another imaging principle of the present invention using a parallel X-ray imaging mode;

FIG. 8 is a schematic view of the imaging principle of the present invention in a general industrial CT mode;

fig. 9 is a schematic diagram of another imaging principle of the present invention using a general industrial CT mode.

In the figure: 10. an X-ray tube; 20. an X-ray catheter; 21. a parabolic focusing catheter; 22. a linear conduit; 221. a metal grid; 30. a catheter stent; 40. a high-precision detector; 50. a sample rotary base; 60. an X-Y moving platform; 61. a first slide rail; 62. a first sliding table; 63. a first lead screw motor; 64. a second slide rail; 65. a second sliding table; 66. a second lead screw motor; 70. a base; 80. a first side plate; 90. a third slide rail assembly; 100. a detector sliding table; 110. a second side plate; 120. a fourth slide rail assembly; 130. and (3) sampling.

Detailed Description

The present invention will be further described with reference to the accompanying drawings and the detailed description, and it should be noted that any combination of the embodiments or technical features described below can be used to form a new embodiment without conflict.

Referring to fig. 1-2, the present invention discloses a parallel X-ray CT imaging apparatus, comprising: an X-ray tube 10, an X-ray catheter 20, a catheter holder 30 and a high precision detector 40. The X-ray tube 10 serves as a radiation source for emitting point-scattered X-rays. The X-ray tube 20 is used for converting point scattering light into parallel light and comprises a parabolic focusing tube 21 and a straight tube 22; the parabolic focusing conduit 21 is a hollow parabolic rotator, the cross section of which is parabolic, the linear conduit 22 is cylindrical, and a metal grid 221 (see fig. 3-5) is arranged inside the parabolic focusing conduit, specifically, the metal grid 221 comprises a plurality of vertically arranged metal sheets and a plurality of horizontally arranged metal sheets, and the metal sheets are perpendicular to each other; the parabolic focusing guide 21 and the linear guide 22 are integrally formed and communicate with each other. The catheter mount 30 is fixedly disposed at the bottom of the X-ray catheter 20 for stably supporting the X-ray catheter 20. The high-precision detector 40 is used for receiving X-rays and performing CT imaging.

The position relation of the above parts is as follows: the X-ray tube 10 is disposed at one side of the parabolic focusing guide 21, the light source of the X-ray tube 10 is located at the focal point of the parabola of the parabolic focusing guide 21, the sample 130 to be detected is disposed at one side of the linear guide 22, and the high-precision detector 40 is disposed at the other side of the sample 130 with respect to the linear guide 22.

The working principle of the invention is as follows: the X-ray tube 10 emits point scattered light, the ray first enters the parabolic focusing guide 21, and the light passing through the focal point is parallel to the symmetry axis of the parabola after being reflected by the parabola based on the optical property of the parabola, so that the point scattered light can be reflected into parallel light by the parabolic focusing guide 21. At the same time, it is difficult to produce an absolutely smooth parabolic surface due to machining accuracy, and therefore the reflected light rays are not necessarily perfectly parallel. Therefore, a metal grid 221 is installed in the linear guide 22 to block the excessive scattering angle of the X-rays, so as to reduce the scattering angle of the X-rays, and to further homogenize the parallel light, so that the light incident on the sample 130 is closer to being completely parallel to a greater extent. The parallel light from the X-ray tube 20 penetrates the sample 130, and then is received by the high-precision detector 40, and then is processed by the high-performance computer configured externally and reconstructed to complete the CT imaging.

Specifically, the high-precision detector 40 is a micron-sized resolution X-ray detector, and the detection precision thereof is superior to that of the current common industrial CT detector. The X-ray tube 10 adopts a high-power ray tube, so that the imaging time is shortened, and the detection efficiency is improved.

Preferably, referring to fig. 1, the present invention further comprises a sample turret 50. The sample 130 to be tested is rotatably connected to the sample turret 50, and the sample 130 can be rotated to adjust the position of the sample 130, thereby facilitating the testing of different positions on the sample 130.

Preferably, the present invention also includes an X-Y motion stage 60. Referring to fig. 2, the X-Y moving platform 60 includes a first slide rail assembly and a second slide rail assembly, which are perpendicular to each other, where the first slide rail assembly includes a first slide rail 61, a first sliding table 62, and a first lead screw motor 63 for driving the first sliding table 62; the second slide rail assembly comprises a second slide rail 64, a second sliding table 65 and a second lead screw motor 66 for driving the second sliding table 65; the second slide rail 64 is fixedly connected to the first slide table 62, and the sample rotary base 50 is fixedly connected to the second slide table 65. The X-Y moving stage 60 can translate the sample 130 in both the X and Y directions, so as to adjust the position, and the X-ray can be projected to each position of the sample 130 by cooperating with the rotation function of the sample turret 50.

Preferably, referring to fig. 1, the present invention further includes a base 70 for general support, and the first slide rail 61 is fixedly connected to the base 70.

Preferably, referring to fig. 1, the present invention further comprises a first side plate 80 vertically disposed on the base 70, the X-ray tube 10 being disposed on the first side plate 80, the first side plate 80 serving to provide a mounting location for the X-ray tube 10. Further preferably, the present invention further includes a third slide rail assembly 90 disposed on the first side plate 80, the third slide rail assembly 90 includes a third slide rail and a third sliding table, the third slide rail is fixedly connected to the first side plate 80, and the X-ray tube 10 is fixedly connected to the third sliding table; further, a linear motor can be arranged to be connected with the third sliding table to drive the third sliding table to move up and down. The third slide rail assembly 90 functions to provide the X-ray tube 10 with a height adjustment function.

Preferably, referring to fig. 1, the present invention further includes a detector slide table 100, the detector slide table 100 is connected to the first slide rail 61 and located at a side portion of the first slide table 62, and the high-precision detector 40 is fixedly disposed on the first slide table 62, so that the high-precision detector 40 can translate along the X-ray axial direction, and the position of the high-precision detector 40 can be adjusted according to the size of the sample 130.

Preferably, referring to fig. 1-2, the present invention further includes a second side plate 110 and a fourth slide rail assembly 120. The second side plate 110 is vertically arranged on the detector sliding table 100, the fourth slide rail assembly 120 comprises a fourth slide rail and a fourth sliding table, the fourth slide rail is fixedly connected to the second side plate 110, and the high-precision detector 40 is fixedly connected to the fourth sliding table; further, a linear motor can be arranged to be connected with the fourth sliding table to drive the fourth sliding table to move up and down. The fourth slide rail assembly 120 functions to provide the high-precision probe 40 with a height adjustment function.

The height of the X-ray catheter 20 can also be adjusted by replacing the catheter holder 30 of a different height. By the matching adjustment of the catheter bracket 30, the third slide rail assembly 90 and the fourth slide rail assembly 120, the X-ray tube 10, the sample 130 and the high-precision detector 40 can be located on the same axis.

Preferably, the X-ray tube 20 is an ultra-scope tube, and the interior of the ultra-scope tube is in a vacuum state. The inner surface of the super mirror guide pipe has a multilayer spraying effect, the reflection effect can be effectively improved, and the transmission efficiency of the super mirror guide pipe can be ensured by the internal vacuum. It should be noted that the hyperscope catheter is prior art in the field and is directly available, and the detailed description of the specific materials thereof is omitted.

Preferably, the two end openings of the hyperscope conduit are provided with aluminum alloy windows for sealing. The aluminum alloy has good neutron penetrability, and can reduce the energy loss of X rays.

The device has two imaging modes, one is a parallel X-ray imaging mode, and the other is a common industrial CT mode, and can be flexibly switched according to actual detection requirements. (a) When a parallel X-ray imaging mode is employed: referring to fig. 6 to 7, the height of the X-ray tube 10, the horizontal position and height of the sample 130, and the horizontal position and height of the high-precision detector 40 are adjusted, the X-rays are reflected into parallel light by the parabolic focusing guide 21, and are reflected for multiple times by the linear guide 22 to improve uniformity, the high-precision detector 40 receives the X-rays penetrating through the sample 130 and images, and the higher the detector resolution, the higher the imaging resolution, and the same principle as that of a general camera. (b) When a common industrial CT imaging mode is adopted, referring to fig. 8 to 9, it is only necessary to remove the X-ray catheter 20 and the catheter support 30 and adjust the positions of the X-Y moving platform 60 and the detector slide table 100, and then a conventional industrial CT imaging operation can be performed.

Through the detailed explanation of the above embodiments, it can be understood that the present invention has the following technical effects:

(1) because the ray penetrating through the sample is parallel light, the imaging resolution is determined by the detector resolution and is not determined by the size of the target focus of the ray tube, and the imaging resolution can be improved by improving the detector resolution. Compared with the traditional industrial CT which needs to adopt an X-ray tube with small target focus size (low power), the X-ray tube can improve the imaging resolution, and the high-resolution X-ray tube can achieve high imaging resolution by adopting a high-precision detector, so that the high-power X-ray tube can be used as a ray source without influencing the imaging quality. The high-power X-ray tube has high ray energy and can penetrate through a thicker sample, so that the detection of the thick sample is effectively finished; meanwhile, the imaging time is shortened, and the detection efficiency is greatly improved.

(2) The X-ray tube has a height adjustment function.

(3) The sample has the functions of horizontal movement in the X direction and the Y direction and rotation.

(4) The detector has translation and height adjustment functions.

(5) The transmission efficiency of the X-ray is improved through the super-scope catheter.

(6) Possess two kinds of formation of image modes, can carry out nimble switching according to the detection demand.

The above embodiments are only preferred embodiments of the present invention, and the protection scope of the present invention is not limited thereby, and any insubstantial changes and substitutions made by those skilled in the art based on the present invention are within the protection scope of the present invention.