CN112890845A

CN112890845A - CT collimating device and CT equipment with same

Info

Publication number: CN112890845A
Application number: CN202110347907.5A
Authority: CN
Inventors: 陈俊; 林晓珍; 梁宏锋
Original assignee: Wuhan United Imaging Life Science Instrument Co Ltd
Current assignee: Wuhan United Imaging Life Science Instrument Co Ltd
Priority date: 2021-03-31
Filing date: 2021-03-31
Publication date: 2021-06-04

Abstract

The invention provides a CT collimating device and CT equipment with the same. The CT collimation device comprises: the mounting base plate is provided with a ray opening; the shielding component is arranged on the mounting base and can shield the ray opening at a high speed; the filter assembly comprises at least two groups of filter plates, and different filter conditions can be provided between the at least two groups of filter plates in a combined mode. Through the combination of different groups of filters in the filtering subassembly, have in order to provide manifold filtering condition, satisfy the experimental demand of different operating modes, and then improve the adaptability to different scanning objects.

Description

CT collimating device and CT equipment with same

Technical Field

The invention relates to the technical field of computed tomography imaging equipment, in particular to a CT (computed tomography) collimation device and CT equipment with the same.

Background

For the current CT (computed tomography) equipment, the filtering devices all adopt a fixed combination mode, and the number of combinations is small, and most of the combinations are three to four. In the scientific research process, the influence of different influence parameters on the experimental result needs to be considered, the filtering device in the form can not realize the free combination of multiple filtering, and the whole size structure is larger, so that the accuracy of the imaging result is influenced.

Disclosure of Invention

Accordingly, it is desirable to provide a CT collimator capable of increasing the number of filter combinations and a CT apparatus having the CT collimator, in order to solve the problem of poor imaging effect caused by the small number of filter combinations in the prior art.

The above purpose is realized by the following technical scheme:

a CT collimation apparatus comprising:

the mounting base plate is provided with a ray opening;

the shielding component is arranged on the mounting base and can shield the ray opening at a high speed;

the filter assembly comprises at least two groups of filter plates, and different filtering conditions can be provided between the two groups of filter plates in a combined mode.

In one embodiment, the shielding component comprises a shielding power source, a shielding transmission component and a shielding flashboard, the shielding power source is arranged on the mounting base plate, and the shielding transmission component is in transmission connection with the shielding power source and the shielding flashboard.

In one embodiment, the shutter transmission assembly includes a crank link member connecting the shutter power source and the shutter.

In one embodiment, the shutter drive assembly further includes a guide member provided to the mounting base plate, and the shutter plate is movable relative to the mounting base plate by the guide member.

In one embodiment, the filter assembly includes a first filter switching structure and a second filter switching structure, and the two sets of filter segments are respectively disposed on the first filter switching structure and the second filter switching structure.

In one embodiment, the first filtering switching structure includes a first power source and a first transmission assembly, the first power source is disposed on the installation bottom plate, the first transmission assembly is connected to the first power source, the first transmission assembly is located on a side of the ray opening away from the shielding shutter, and the first transmission assembly is provided with a plurality of different filters.

In one embodiment, the first transmission assembly includes a first switching gear and a second switching gear, the first switching gear is mounted on the first power source, the second switching gear is rotatably mounted on the mounting base plate, the second switching gear is provided with a plurality of different filters, and the second switching gear can drive at least one filter to align with the ray opening.

In one embodiment, the second switching gear has a plurality of first radiation windows with different sizes, and at least part of the first radiation windows are used for installing the filter plates.

In one embodiment, the second filtering switching structure includes a second power source and a second transmission assembly, the second power source is disposed on the mounting board, the second transmission assembly is connected to the second power source, a plurality of different filters are mounted on the second transmission assembly, and the second transmission assembly and the first transmission assembly are stacked, so that the filters of the second transmission member and the filters of the first transmission assembly can be selectively overlapped.

In one embodiment, the second transmission assembly includes a combination gear and a combination carrier plate, the combination gear is mounted to the second power source, the combination carrier plate is movably mounted to the mounting base plate, a plurality of different filters are mounted on the combination carrier plate, and the combination carrier plate can drive at least one of the filters to align with the ray opening.

In one embodiment, the combined carrier plate has a plurality of second radiation windows with different sizes, and at least part of the second radiation windows are used for installing the filter plates.

In one embodiment, the shape and size of the first radiation window is the same and/or different from the shape and size of the second radiation window.

A CT device comprises an electronic component, a fixed frame, a rotating frame and a CT collimating device according to any technical characteristic, wherein the rotating frame is rotatably connected to the fixed frame, the electronic component at least comprises a ray generator and a ray detector, the ray generator and the ray detector are symmetrically arranged on the rotating frame, and the CT collimating device is arranged on the rotating frame and corresponds to the ray generator.

After the technical scheme is adopted, the invention at least has the following technical effects:

according to the CT collimating device and the CT equipment with the same, the shielding component can open or close the ray opening of the mounting base plate so as to control the emission of rays. Meanwhile, at least two groups of filter plates of the filter assembly can be combined with each other to provide different filter conditions and meet different experimental requirements. Through the combination of different groups of filter plates in the filtering assembly, the problem that the imaging effect is poor that the present filter equipment combination quantity of effectual solution leads to is few to provide manifold filtering condition, satisfy the experimental demand of different operating modes, and then improve the adaptability to different scanning objects.

Drawings

FIG. 1 is a perspective view of a CT collimator according to an embodiment of the present invention;

FIG. 2 is a perspective view of a shutter assembly of the CT collimation apparatus shown in FIG. 1 with a radiation opening open;

fig. 3 is a perspective view of the CT collimator shown in fig. 1 from another angle.

Wherein: 100. a CT collimating device; 110. mounting a bottom plate; 111. a radiation opening; 120. a shielding component; 121. shielding a power source; 122. a shielding transmission component; 1221. a crank link member; 12211. a crank; 12212. a connecting rod; 1222. a guide member; 12221. a first guide portion; 12222. a second guide portion; 123. a shutter plate; 130. a switching structure; 131. a first power source; 132. a first transmission assembly; 1321. a first switching gear; 1322. a second switching gear; 13221. a first ray window; 140. a filter plate; 150. a second filtering switching structure; 151. a second power source; 152. a second transmission assembly; 1521. a combination gear; 1522. combining the carrier plates; 15221. a second radiation window; 1523. a slider.

Detailed Description

In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein.

In the description of the present invention, it is to be understood that the terms "central," "longitudinal," "lateral," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counterclockwise," "axial," "radial," "circumferential," and the like are used in the orientations and positional relationships indicated in the drawings for convenience in describing the invention and to simplify the description, and are not intended to indicate or imply that the referenced device or element must have a particular orientation, be constructed and operated in a particular orientation, and are not to be considered limiting of the invention.

Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present invention, "a plurality" means at least two, e.g., two, three, etc., unless specifically limited otherwise.

In the present invention, unless otherwise expressly stated or limited, the terms "mounted," "connected," "secured," and the like are to be construed broadly and can, for example, be fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; they may be directly connected or indirectly connected through intervening media, or they may be connected internally or in any other suitable relationship, unless expressly stated otherwise. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.

In the present invention, unless otherwise expressly stated or limited, the first feature "on" or "under" the second feature may be directly contacting the first and second features or indirectly contacting the first and second features through an intermediate. Also, a first feature "on," "over," and "above" a second feature may be directly or diagonally above the second feature, or may simply indicate that the first feature is at a higher level than the second feature. A first feature being "under," "below," and "beneath" a second feature may be directly under or obliquely under the first feature, or may simply mean that the first feature is at a lesser elevation than the second feature.

It will be understood that when an element is referred to as being "secured to" or "disposed on" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like as used herein are for illustrative purposes only and do not denote a unique embodiment.

Referring to fig. 1 to 3, a CT collimation device 100 of the present invention is disclosed. The CT collimator 100 is applied to a CT (computed tomography) apparatus, and is disposed on a rotating gantry of the CT apparatus and covers a radiation generator of the CT apparatus. Optionally, the CT device is a common CT device, and may also be a Micro CT device. The CT device can image a scanning area of a scanning object, optionally, the scanning object can be a patient, and the scanning area can be a focus position of the patient; of course, in other embodiments of the present invention, the scanning object may also refer to a small animal, and the scanning region corresponds to a lesion region of the small animal; the scanning object can also be a metal material in industry to detect whether the metal material has damage. The CT collimation apparatus 100 may perform collimation on the radiation (X-ray) emitted from the radiation generator to adjust the width of the radiation. The adjusted rays can be accurately aligned to a scanning area, the irradiation accuracy is improved, and the rays are prevented from irradiating a non-scanning area.

The CT collimation device 100 can enable rays of a ray generator to be emitted in a pulse mode, so that the rays cannot be emitted through the CT collimation device 100 under the condition that the rays are not needed in the scanning process; when the ray is to be used, the ray can pass through the CT collimating device 100, the irradiation dose of the ray can be reduced, the damage to a scanned object is reduced, meanwhile, the ray detector can be protected, and the service life of the ray detector is prolonged.

Referring to fig. 1 and 2, in one embodiment, a CT collimation device 100 includes a mounting base 110, a shielding assembly 120, and a filtering assembly. The mounting base plate 110 is provided to the rotating gantry, and the mounting base plate 110 has a radiation opening 111 through which radiation from the radiation generator passes. The shielding assembly 120 is movably disposed on the mounting base 110 and can open or close the radiation opening 111. The filtering assembly is disposed on the mounting base plate 110 and used for filtering rays, and the filtering assembly includes at least two sets of filtering plates 140.

The mounting base 110 serves as a load bearing support for carrying various components of the CT collimation device 100 to securely support the various components of the CT collimation device 100. The mounting plate 110 may also form the CT collimation device 100 as a single unit to facilitate connection of the CT collimation device 100 to a rotating gantry. The mounting base plate 110 has a radiation opening 111 provided therethrough. Optionally, a transparent member, such as transparent glass, a resin lens, or other members that do not interfere with the passage of radiation, may be installed in the radiation opening 111. Of course, in other embodiments of the present invention, the radiation opening 111 may be a hollow window, i.e. no component is installed in the radiation opening 111.

After the mounting plate 110 is mounted on the rotating gantry, the mounting plate 110 covers the ray generator, and at this time, the ray generator faces the ray opening 111. The radiation emitted by the radiation generator can exit through the radiation opening 111. The radiation emitted through the radiation opening 111 is projected to the radiation detector after passing through a scanning region of the scanning object. The ray detector receives rays passing through the scanning area and processes information of the rays so as to image the scanning area of the scanned object, thereby facilitating diagnosis.

Since the radiation generator emits continuous radiation, the scanning object is forced to receive a large dose of radiation, which damages the health of the scanning object, and the detector continuously receives the X-rays, which also affects the service life of the detector. To this end, the CT collimation device 100 of the present invention adds a shielding assembly 120 on the mounting base 110, and the shielding assembly 120 can move relative to the mounting base 110 to open or close the radiation opening 111 on the mounting base 110.

Specifically, when the shielding assembly 120 closes the ray opening 111, the shielding assembly 120 covers the ray opening 111, so that the shielding assembly 120 corresponds to the ray generator, at this time, the ray emitted by the ray generator is blocked by the shielding assembly 120, and the ray cannot penetrate through the shielding assembly 120 and enter the scanning object. When the shielding assembly 120 opens the radiation opening 111, the shielding assembly 120 is separated from the radiation opening 111, and the radiation opening 111 is an open structure and is no longer shielded. At this time, the radiation emitted from the radiation generator may be emitted through the radiation opening 111 and projected to the radiation detector after passing through the scanning region of the scanned object.

In the scanning process, under the condition that rays are not needed, such as in a data acquisition stage and the like, the shielding component 120 can be used for shielding the ray opening 111 so that the rays cannot penetrate through the ray opening 111 to be emitted, and then the rays are prevented from being emitted into a scanned object; when the radiation is to be used, the shielding component 120 opens the radiation opening 111 again, so that the radiation is emitted through the radiation opening 111 and enters the scanned object. By opening and closing the ray opening 111 through the shielding component 120, the ray generator can generate rays to form a pulse type, so as to achieve the purpose of controlling the time of ray window outgoing.

A filter assembly is disposed on the mounting base 110 and is positioned near the radiation opening 111, and the filter assembly can filter the radiation emitted by the radiation generator. The filter assembly comprises at least two sets of filters 140. At least two groups of filter plates 140 can be mutually combined to allow rays to pass through, so that different experimental requirements of different Micro CT devices are met.

After the CT collimation device 100 of the embodiment is adopted, the shielding component 120 shields or opens the ray opening 111, so that the problem that the ray generator in the existing Micro CT equipment can only continuously emit X rays is effectively solved, the rays are emitted in a pulse mode, and the shielding component 120 can be used for shielding a ray window under the condition that the rays are not needed in the scanning process; when the ray is to be used, the shielding component 120 opens the ray opening 111 again, so that the irradiation dose of the ray can be reduced, the damage to a scanned object is reduced, meanwhile, the ray detector can be protected, and the service life of the ray detector is prolonged.

In one embodiment, different filtering conditions may be provided between two sets of filter segments 140 in the filtering assembly by combination. The filtering component comprises at least two groups of filtering sheets 140, wherein the two groups of filtering sheets 140 can be combined to provide filtering conditions, and the three groups of filtering sheets 140 or even more can be combined to provide filtering conditions. In an embodiment of the present invention, the filtering component includes two sets of filters 140 for providing filtering conditions, and this will be described in detail later.

Each group of filters 140 includes a plurality of filters 140, and one filter 140 in each group may provide a respective filtering condition in combination with the respective filters 140 of the other groups. Make each filter 140 in two sets of to make up through this kind of mode, the effectual current filter equipment of solution makes up the poor problem of imaging effect that quantity leads to a little, increases the quantity of filtering condition, provides manifold filtering condition, can image through the combination of different filters 140, satisfies the experimental demand of different operating modes, the medical diagnosis of being convenient for or experimental result analysis.

In an embodiment, the shielding assembly 120 includes a shielding power source 121, a shielding transmission assembly 122 and a shielding shutter 123, the shielding power source 121 is disposed on the mounting base plate 110, the shielding transmission assembly 122 is in transmission connection with the shielding power source 121 and the shielding shutter 123, and the shielding shutter 123 can open or close the radiation opening 111. The shielding power source 121 powers the movement of the shielding assembly 120 such that the shielding assembly 120 can move relative to the mounting base 110 to open or close the radiation opening 111. Alternatively, the shielding power source 121 is a rotary electromagnet, and the power of the shielding power source 121 is provided by rotation of the rotary electromagnet. The rotary electromagnet can complete the suction action within a time of several to several hundred milliseconds, so that the shutter 123 can complete the action of opening or closing the radiation opening 111 within the time range. Of course, in other embodiments of the present invention, the shielding power source 121 may also be other power components capable of responding to movement in a short time.

The movement of the shielding shutter 123 to open or close the radiation opening 111 may be realized by forward and reverse rotation of the shielding power source 121, i.e., the rotary electromagnet, which is realized by changing the forward and reverse of the input voltage. When the shielding shutter 123 is covered on the radiation opening 111, the shielding shutter 123 closes the radiation opening 111, and the radiation from the radiation generator cannot be emitted. When the shielding shutter 123 is separated from the radiation opening 111, the shielding shutter 123 opens the radiation opening 111, and the radiation of the radiation generator can be emitted through the radiation opening 111. The movement of the shielding shutter 123 is realized by the matching of the shielding power source 121 and the shielding transmission component 122, and the shielding transmission component 122 is connected with the shielding power source 121 to realize the transmission of the power of the shielding power source 121 so as to drive the shielding shutter 123 to move.

One end of the shielding transmission component 122 is connected to the output end of the shielding power source 121, and the other end of the shielding transmission component 122 is connected to the shielding shutter 123. When the shielding power source 121 works, the shielding power source 121 drives the shielding transmission component 122 to move, and then the shielding transmission component 122 drives the shielding shutter 123 to move, so that the shielding shutter 123 opens or closes the ray opening 111. Alternatively, the shutter 123 is made of a material capable of shielding radiation, such as tungsten, lead, or the like. Thus, when the shielding shutter 123 closes the ray opening 111, rays of the ray generator cannot be emitted through the ray shutter, and the ray generator plays a role in blocking rays; only when the shielding shutter 123 opens the radiation opening 111, the radiation of the radiation generator can be emitted through the radiation opening 111.

Alternatively, the shutter plate 123 has a flat plate-like structure. Illustratively, the shielding shutter 123 is movably disposed on the mounting base 110, and the shielding transmission assembly 122 can drive the shielding shutter 123 to move linearly to open or close the radiation opening 111. Of course, the shielding shutter 123 may also be rotatably disposed on the mounting base plate 110, and the shielding transmission assembly 122 drives the shielding shutter 123 to rotate relative to the mounting base plate 110 to open or close the radiation opening 111.

Optionally, the shielding shutter 123 is of a telescopic plate structure, and the shielding transmission assembly 122 drives the shielding shutter 123 to perform telescopic motion; specifically, when the shielding transmission assembly 122 drives the shielding shutter 123 to extend out, the shielding shutter 123 closes the ray opening 111, and when the shielding transmission assembly 122 drives the shielding shutter 123 to retract, the shielding shutter 123 opens the ray opening 111. Optionally, the shielding shutter 123 is of a folding structure, and the shielding transmission assembly 122 drives the shielding shutter 123 to perform an extending motion or a folding motion so as to open or close the radiation opening 111.

Alternatively, the shutter 123 may be located on a side of the mounting base 110 facing the scanning object, on a side of the mounting base 110 facing the ray generator, or in the mounting base 110. Illustratively, the shutter 123 is located on a side of the mounting base plate 110 facing the scanning object, i.e., is disposed away from the ray generator. Therefore, interference between the movement of the shielding gate plate 123 and other parts can be avoided, and the movement accuracy is ensured.

In one embodiment, the shutter driving assembly 122 includes a crank link 1221, and the crank link 1221 connects the shutter power source 121 and the shutter 123. One end of the crank link 1221 is connected to the output end of the shielding power source 121, and the other end of the crank link 1221 is connected to the shielding shutter 123. When sheltering from power supply 121 output rotary motion, shelter from power supply 121 and can drive crank connecting rod spare 1221 and rotate, and then crank connecting rod spare 1221 can drive and shelter from flashboard 123 motion to the messenger shelters from flashboard 123 and can open or close ray opening 111.

Alternatively, the crank link 1221 includes a crank 12211 connected to the shutter power source 121 and a link 12212 rotatably connected to the crank 12211, and the other end of the link 12212 is connected to the shutter 123. When the shielding power source 121 rotates, the crank 12211 is driven to rotate synchronously, and then the crank 12211 drives the connecting rod 12212 to rotate synchronously to drive the shielding shutter 123 to move, so that the shielding shutter 123 opens or closes the ray opening 111.

Alternatively, the crank link 1221 may bring the shutter 123 to open or close the radiation opening 111 in a movable manner, which may reduce the occupied space. In one embodiment, the shutter drive assembly 122 further includes a guide 1222, the guide 1222 is disposed on the mounting base plate 110, and the shutter plate 123 is moved relative to the mounting base plate 110 by the guide 1222. The guide 1222 may guide the movement of the shielding shutter 123 such that the shielding shutter 123 can only move linearly, reducing a space occupied when the shielding shutter 123 moves. Specifically, when the crank link 1221 drives the shielding shutter 123 to move, due to the limiting effect of the guide 1222, the rotation of the crank link 1221 can drive the shielding shutter 123 to move linearly along the installation bottom plate 110 through the guide portion, so as to open or close the radiation opening 111.

Optionally, the guide 1222 includes a first guide portion 12221 and a second guide portion 12222 that are a sliding fit. The first guide portion 12221 is disposed on the mounting base plate 110, and the second guide portion 12222 is slidably disposed on the first guide portion 12221 and connected to the shutter 123. Illustratively, the first guiding portion 12221 is a slide rail, and the second guiding portion 12222 is a slider. Of course, the arrangement positions of the slide rail and the slide block can be interchanged. In other embodiments of the present invention, the guiding element 1222 may also be other guiding components, such as the matching of guiding holes and guiding rods.

Alternatively, the end of the crank link 1221 may be directly connected to the shutter 123, and at this time, the guide 1222 may movably connect the shutter 123 to the mounting plate, and the crank link 1221 may move the shutter 123 along the first guide 12221 through the second guide 12222. Still alternatively, the end of the crank link 1221 may be indirectly connected to the shutter 123, such as the crank link 1221 being connected to the second guide portion 12222 and the second guide portion 12222 being connected to the shutter 123. This also enables control of the movement of the shutter 123. Alternatively, the second guide portion 12222 may be an integral structure with the shutter plate 123.

Of course, in other embodiments of the present invention, the shielding transmission assembly 122 may also include a linear moving member, and the linear moving member connects the shielding power source 121 and the shielding shutter 123. One end of the linear motion member is connected to the shielding power source 121, and the other end of the linear motion member is connected to the shielding shutter 123. The shielding power source 121 drives the shielding shutter 123 to perform a linear motion through the linear motion member, so as to open or close the radiation opening 111.

Optionally, the linear motion member is a gear tooth condition. A gear of a gear tooth condition is installed at an output end of the shielding power source 121, and a rack of the gear tooth condition is engaged with the gear and installed at the shielding shutter 123. The shielding power source 121 moves the shielding shutter 123 by the gear tooth condition to open or close the radiation opening 111. Still alternatively, the linear motion member is a ball screw member, which is mounted on the output end of the shielding power source 121, and a nut of the ball screw member is connected to the shielding shutter 123. The shielding power source 121 drives the shielding shutter 123 to move through the ball screw rod, so as to open or close the ray opening 111. Of course, in other embodiments of the present invention, the linear motion member may also be other components capable of outputting linear motion.

In one embodiment, the number of the shielding assemblies 120 is two, and the two shielding assemblies 120 are symmetrically arranged. By the relative movement of the two shielding assemblies 120, the movement space of the shielding shutter 123 can be reduced, and the length dimension of the CT collimation device 100 in the movement direction of the shielding shutter 123 can be reduced. Of course, in other embodiments of the present invention, the number of the shielding components 120 may be one.

In one embodiment, the shielding assembly 120 further has a limiting member, which can contact with the shielding transmission assembly 122 for limiting the movement displacement of the shielding transmission assembly 122. The limiting member is disposed on the shielding power source 121 and is configured to limit the movement displacement of the shielding transmission assembly 122, so as to avoid the over-travel operation of the shielding transmission assembly 122. The limiting part can limit the shielding transmission assembly 122 when the shielding shutter 123 opens the ray opening 111, namely, the limiting part limits the rotation angle of the shielding power source 121, and the shielding power source 121 is prevented from rotating excessively or continuously. Further, the limiting member may abut against the crank 12211 of the crank link member 1221, limiting the rotational angle of the crank 12211. Optionally, the limiting member is a limiting post.

In one embodiment, the CT collimation device 100 further comprises a filtering assembly, wherein the filtering assembly comprises a plurality of filtering switching structures, the number of the filtering switching structures is equal to the number of the groups of the filtering slices 140, and each filtering switching structure is provided with one group of the filtering slices 140. The corresponding filter plates 140 are driven to move through the corresponding filter switching structures, so that the combination of different filter plates 140 on a plurality of filter switching structures can be realized, and the purpose of providing different filter adjustment is achieved. Illustratively, the number of the filter switching structures is two, and the two sets of filter segments 140 are driven by the two filter switching structures to move, so that the combination of the two sets of filter segments is realized. Of course, in other embodiments of the present invention, the number of the filtering switching structures may also be more, and the working principle of the more filtering switching structures is substantially the same as that of the two filtering switching structures, which is not described herein in detail.

Referring to fig. 1 and 3, in an embodiment, the CT collimation apparatus 100 further includes a filtering assembly including a first filtering switching structure 130 and a second filtering switching structure 150. The two sets of filters 140 are respectively disposed on the first filter switching structure 130 and the second filter switching structure 150. The first filter switching structure 130 and the second filter switching structure 150 are disposed on the mounting base plate 110, the first filter switching structure 130 can drive the filter 140 thereon to move to the ray opening 111, and the second filter switching structure 150 can drive the filter 140 thereon to move to the ray opening 111. The filters 140 of the first filter switching structure 130 and the second filter switching structure 150 move to the ray opening 111 and are overlapped, and the ray passes through the filters 140 of the first filter switching structure 130 and the second filter switching structure 150 respectively to be emitted.

The first filter switching structure 130 and the second filter switching structure 150 are movable relative to the mounting base plate 110 to select an appropriate filter 140 to be aligned with the radiation opening 111. In this way, the combination of the filters 140 of the first filter switching structure 130 and the second filter switching structure 150 can be realized. The first filter switching structure 130 and the second filter switching structure 150 have different types of filters 140. The different types refer to the material, thickness and size of the filter 140. When the first filter switching structure 130 and the second filter switching structure 150 move relative to the mounting base plate 110, the first filter switching structure 130 and the second filter switching structure 150 can drive the corresponding filter 140 to move relative to the mounting base plate 110, so as to switch the different types of filter 140. The ray emitted from the ray generator passes through the filter 140 and enters the scanning area of the scanned object, and is received by the ray detector.

It will be appreciated that current filters generally use a fixed combination and that no choice of filter class is possible. In the scientific research process, because the influence of different influence parameters on the experimental result needs to be considered, the type factor of the filter is one of the variables influencing the imaging result, and thus, a sufficient number of filter slices are needed to meet the experimental research requirement. Therefore, the CT collimation device 100 of the present invention adds the first filtering switching structure 130 and the second filtering switching structure 150 on the mounting base plate 110, and the switching combination of the different types of filters 140 is realized through the first filtering switching structure 130 and the second filtering switching structure 150, so as to meet the experimental requirements.

Specifically, a plurality of different types of filters 140 are disposed on the first filter switching structure 130, and when the first filter switching structure 130 moves relative to the mounting base plate 110, the filters 140 on the first filter switching structure 130 may be aligned with the ray opening 111. Correspondingly, the second filter switching structure 150 is also provided with a plurality of different types of filters 140, and the filters 140 on the second filter switching structure 150 can be aligned with the ray openings 111 when the second filter switching structure 150 moves relative to the mounting base plate 110. Thus, the ray of the ray generator can be incident into the scan object through the filter 140. Moreover, the first filtering switching structure 130 and the second filtering switching structure 150 drive the filter 140 to move, so that the required filter 140 can be selected to be aligned with the ray opening 111, and different experimental research requirements are met.

Alternatively, the first filter switching structure 130 and the second filter switching structure 150 may be located on a side of the mounting base plate 110 facing the scanning object, or on a side of the mounting base plate 110 facing the ray generator, as long as it is ensured that the rays of the ray generator can be emitted through the filters 140 on the first filter switching structure 130 and the second filter switching structure 150. Illustratively, the first filter switching structure 130 and the second filter switching structure 150 are disposed on a side of the mounting substrate 110 facing the ray generator. Still alternatively, a side of the mounting base plate 110 facing the ray generator has a mounting space in which the first filter switching structure 130 and the second filter switching structure 150 are at least partially located. Therefore, the interference between the first filter switching structure 130 and the second filter switching structure 150 and other components can be avoided, and the accuracy of the movement can be ensured.

In an embodiment, the first filter switching structure 130 includes a first power source 131 and a first transmission assembly 132, the first power source 131 is disposed on the mounting base plate 110, the first transmission assembly 132 is connected to the first power source 131, the first transmission assembly 132 is located on a side of the ray opening 111 away from the shutter 123, and a plurality of different filters 140 are mounted on the first transmission assembly 132. The first power source 131 provides power for movement of the first transmission assembly 132 such that the first transmission assembly 132 can be moved relative to the mounting base 110 to select a desired filter 140 on the first transmission assembly 132 to be aligned with the radiation opening 111. Alternatively, the first power source 131 may be a driving motor, a rotary electromagnet, or other rotating component capable of quick response.

The first power source 131 and the first transmission assembly 132 are disposed on two sides of the mounting base plate 110, so that the occupied space can be reduced. Illustratively, the first power source 131 is disposed on the surface of the mounting base plate 110 having the shielding assembly 120, and the first transmission assembly 132 is disposed on the side of the mounting base plate 110 facing the ray generator and is installed in the mounting space. The output end of the first power source 131 extends through the mounting base plate 110 and is connected to the first transmission assembly 132, and the first transmission assembly 132 is provided with a plurality of filter plates 140. The first transmission component 132 is disposed corresponding to the ray opening 111, and when the first power source 131 drives the first transmission component 132 to move, the first transmission component 132 can drive the required filter 140 to move to the ray opening 111 for the ray to pass through.

In one embodiment, the first transmission assembly 132 includes a first switching gear 1321 and a second switching gear 1322 engaged with each other, the first switching gear 1321 is mounted on the first power source 131, the second switching gear 1322 is rotatably mounted on the mounting base plate, a plurality of different filters 140 are mounted on the second switching gear 1322, and the second switching gear 1322 can drive at least one filter 140 to align with the radiation opening 111. The first switching gear 1321 is mounted on the output end of the first power source 131, the first switching gear 1321 is engaged with the second switching gear 1322, and the second switching gear 1322 is rotatably disposed on the mounting base plate 110 through a bearing and the like. Thus, when the first power source 131 drives the first switching gear 1321 to rotate, the first switching gear 1321 can drive the second switching gear 1322 to rotate synchronously.

The second switching gear 1322 is provided with a plurality of different filter plates 140. That is, at least one of the shape, size, material, and thickness of each filter segment 140 on the second switching gear 1322 is different. In this way, the second switching gear 1322 drives the required filter 140 to move to the ray opening 111, and the ray is transmitted through the corresponding type of filter 140. Optionally, a plurality of filters 140 are located on the same circumferential dimension. That is, the distances from the respective filter sheets 140 to the center of the second switching gear 1322 are equal. Thus, when the second switching gear 1322 rotates, any filter 140 moves to the ray opening 111 along with the second switching gear 1322 and aligns with the ray opening 111, so that the ray can pass through the filter 140 and then be emitted through the ray opening 111.

Optionally, the diameter of the second switching gear 1322 is larger than the diameter of the first switching gear 1321. Therefore, the bearing area of the second switching gear 1322 can be increased, so that more filter plates 140 can be conveniently borne, and the switching requirement can be met. Illustratively, the number of filter plates 140 on the second switching gear 1322 is four. In other embodiments of the invention, the first drive assembly 132 may also be a chain drive, a belt drive, or the like. Of course, the first transmission assembly 132 can also realize the switching of the filter plate 140 through one gear.

Alternatively, the second switching gear 1322 is made of a material capable of shielding X-rays, such as tungsten, lead, or the like. Thus, when the body portion of the second switching gear 1322 corresponds to the radiation opening 111, the radiation of the radiation generator cannot be emitted through the second switching gear 1322, which acts as a radiation blocking function; when the filter 140 of the second switching gear 1322 corresponds to the ray opening 111, the ray generated by the ray generator can penetrate through the filter 140 and exit through the ray opening 111.

In one embodiment, the second switching gear 1322 has a plurality of first radiation windows 13221 with different sizes, and at least a portion of the first radiation windows 13221 are used for mounting the filter 140. The first radiation window 13221 is provided to penetrate in the axial direction, and the filter 140 or a hollow window is provided in the first radiation window 13221 so that the radiation can smoothly pass through. That is, the filter 140 may be installed in all of the plurality of first ray windows 13221, or the filter 140 may be installed in part, and a part of the windows is not installed.

In an embodiment, the second filter switching structure 150 further includes a second power source 151 and a second transmission assembly 152, the second power source 151 is disposed on the mounting base plate 110, the second transmission assembly 152 is connected to the second power source 151, a plurality of different filters 140 are mounted on the second transmission assembly 152, and the second transmission assembly 152 and the first transmission assembly 132 are stacked, so that the filters 140 of the second transmission assembly 152 and the filters 140 of the first transmission assembly 132 are selectively overlapped. The second power source 151 provides power for the movement of the second transmission assembly 152, so that the second transmission assembly 152 can move relative to the mounting base plate 110 to select the overlapping arrangement of the second transmission assembly 152 and the first transmission assembly 132, and to make the filter plate 140 on the second transmission assembly 152 coincide with the filter plate 140 on the second switching gear 1322. Alternatively, the second power source 151 may be a driving motor or other components capable of outputting rotational power.

The second power source 151 and the second transmission assembly 152 are disposed at both sides of the mounting base plate 110, so that the occupied space can be reduced. Illustratively, the second power source 151 is disposed on the surface of the mounting base plate 110 having the shielding assembly 120, and the second transmission assembly 152 is disposed on the side of the mounting base plate 110 facing the ray generator and is installed in the installation space. The output end of the second power source 151 extends through the mounting base plate 110 and is connected to a second transmission assembly 152, and a plurality of filter plates 140 are mounted on the second transmission assembly 152. The second transmission assembly 152 is disposed corresponding to the ray opening 111, and when the second power source 151 drives the second transmission assembly 152 to move, the second transmission assembly 152 can drive the required filter 140 to move to the ray opening 111 for the ray to pass through.

Moreover, the second transmission assembly 152 and the first transmission assembly 132 are stacked along the emitting direction of the ray, and a certain space (gap) exists between the two to avoid interference when the two move. Furthermore, there is no limitation to the stacking order of the second transmission assembly 152 and the first transmission assembly 132, and the filter 140 on which part the ray first passes. Illustratively, the first drive assembly 132 is located between the second drive assembly 152 and the mounting plate 110. That is, the radiation passes through the filter 140 of the second transmission assembly 152 and then passes through the filter 140 of the first transmission assembly 132 before being emitted. After the second power source 151 drives the second transmission assembly 152 to move, the filter 140 on the second transmission assembly 152 can move to the ray opening 111 and coincide with the filter 140 on the first transmission assembly 132, and rays of the ray generator sequentially pass through the two filters 140 and then are emitted.

In one embodiment, the second transmission assembly 152 includes a combination gear 1521 and a combination support plate 1522, the combination gear 1521 is mounted on the second power source 151, the combination support plate 1522 is movably mounted on the mounting base plate, a plurality of different filters 140 are mounted on the combination support plate 1522, the combination support plate 1522 can drive at least one filter 140 to be aligned with the radiation opening 111, and at least one filter 140 of the combination support plate 1522 can be overlapped with at least one filter 140 of the second switching gear 1322. The combination gear 1521 is installed at the output end of the second power source 151, and the combination carrier plate 1522 is meshed with the combination gear 1521. When the second power source 151 drives the combination gear 1521 to move, the combination gear 1521 can drive the combination carrier 1522 to move synchronously, so that the filter 140 of the combination carrier 1522 can be aligned to the ray opening 111.

Optionally, the combined carrier 1522 is disposed in a flat plate shape, and a combined rack is disposed on an edge of the combined carrier 1522 and engaged with the combined gear 1521. The second power source 151 drives the combined carrier 1522 to move linearly through the combined gear 1521, so that the combined carrier 1522 moves up and down along the direction shown in fig. 3, and the filter 140 on the combined carrier 1522 can move to the ray opening 111. Optionally, the combined carrier 1522 may also be a gear, and the combined carrier 1521 drives the combined carrier 1522 to rotate, so that the filter 140 on the combined carrier 1522 can move to the ray opening 111.

Alternatively, when the center line of the filter 140 coincides with the center line of the combination gear 1521, the filter 140 corresponds to a ray window. At this time, the rays may be emitted through the filter 140. It can be understood that the second power source 151 is a stepping motor or a servo motor, and the rotation angle information of the combination gear 1521 can be obtained in the movement process, so that the position information of the combination gear 1521 and the filter plate 140 on the combination carrier plate 1522 can be calculated through the rotation angle information, and whether the center lines coincide is determined, and the filter plate 140 is controlled to accurately move to the ray window.

It should be noted that, if the assembly carrier 1522 is a gear, the movement principle thereof is substantially the same as that of the first transmission assembly 132, and thus the description thereof is omitted. The present invention is described by taking the combination carrier 1522 as an example. In other embodiments of the present invention, the second driving assembly 152 may also be other driving components capable of moving or rotating the combination carrier plate 1522.

Referring to fig. 1 and 3, a plurality of different filters 140 are disposed on the combined carrier 1522. That is, at least one of the parameters of the shape, size, material, thickness, etc. of each filter 140 on the combined carrier 1522 is different. Thus, the combined carrier 1522 drives the required filter 140 to move to the ray opening 111, and the ray is transmitted through the corresponding type of filter 140. The filters 140 on the combined carrier plate 1522 are arranged at intervals along the same straight direction. Thus, when the combination gear 1521 drives the combination carrier 1522 to make a linear motion, any filter 140 can move to the ray opening 111 and be aligned with the ray opening 111, so that the rays can conveniently penetrate through the filter 140 of the combination carrier 1522 to be emitted. Illustratively, the number of filter plates 140 on the combined carrier plate 1522 is two.

Optionally, the combined carrier plate 1522 is made of a material capable of shielding rays, such as tungsten, lead, and the like, which can shield X-rays. Thus, when the body portion of the combined carrier plate 1522 corresponds to the radiation opening 111, the radiation of the radiation generator cannot pass through the combined carrier plate 1522 to be emitted, so as to block the radiation; when the filter 140 of the combined carrier plate 1522 corresponds to the ray opening 111, the ray generated by the ray generator can penetrate through the filter 140 and exit through the ray opening 111.

In an embodiment, the second driving assembly 152 further includes a sliding member 1523, and the sliding member 1523 is disposed on the mounting base 110 and movably connected to the assembly carrier plate 1522. The sliding member 1523 can guide the movement of the combined carrier plate 1522, so that the combined carrier plate 1522 can only move linearly, and the filter plates 140 of the combined carrier plate 1522 can be accurately overlapped with the filter plates 140 of the second switching gear 1322. Specifically, the combined carrier 1522 is connected to the sliding member 1523, and when the combined carrier 1522 moves, the combined carrier 1522 can move synchronously along the sliding member 1523.

Optionally, the slider 1523 includes a first sliding portion and a second sliding portion that are in sliding engagement. The first sliding portion is disposed on the mounting base 110, and the second sliding portion is slidably disposed on the first sliding portion and connected to the combined carrier 1522. Illustratively, the first sliding part is a slide rail, and the second sliding part is a slider. Of course, the arrangement positions of the slide rail and the slide block can be interchanged. In other embodiments of the present invention, the sliding component 1523 may also be other components capable of sliding, such as the matching of a sliding hole and a guide rod, etc.

In an embodiment, the combined carrier 1522 has a plurality of second radiation windows 15221 with different sizes, and at least a portion of the second radiation windows 15221 is used for mounting the filter 140. The second radiation window 15221 is disposed to pass through the radiation exit, and the filter 140 or a hollow window is installed in the second radiation window 15221 to allow the radiation to pass through smoothly. That is, the filter 140 may be installed in all of the second ray windows 15221, or the filter 140 may be installed in part, and a part of the second ray windows 15221 is not installed.

When the switching structure 130 works, the first power source 131 drives the first switching gear 1321 to rotate, and then the first switching gear 1321 drives the second switching gear 1322 to rotate, so as to select the filter plate 140 on the second switching gear 1322, and thus the desired filter plate 140 corresponds to the ray opening 111. The second power source 151 drives the combination gear 1521 to rotate, and then the combination gear 1521 drives the combination carrier 1522 to move, so as to select the filter plate 140 on the combination carrier 1522, and make the required filter plate 140 correspond to the ray opening 111. At this time, the filter 140 on the combined carrier plate 1522 and the filter 140 on the second transmission gear are stacked along the emitting direction of the rays. The rays emitted by the ray generator can sequentially pass through the filter 140 on the combined carrier plate 1522 and the filter 140 on the second transmission gear to be emitted along the rays.

It should be noted that the number of the filter plates 140 on the combined carrier plate 1522 is plural, and the number of the filter plates 140 on the second switching gear 1322 is plural. The first power source 131 may realize switching of different types of filter segments 140, and the second power source 151 may realize switching of different types of filter segments 140. Illustratively, the second switching gear 1322 has four different types of filters 140, and the combined carrier plate 1522 has two different types of filters 140, so that eight different types of filters 140 can be combined by adjusting, and the number of experimental variables that can be provided is greatly increased. Moreover, when the filter 140 is not installed in the second ray window 15221 or the second ray window 15221 of the second switching gear 1322 on the carrier plate, an experiment of a single filter 140 can also be realized.

In an embodiment, the shape and size of the first radiation window 13221 is the same and/or different than the shape and size of the second radiation window 15221. The size of the mounting window of the filter 140 is decisive for the width of the radiation beam. The shape of the first ray window 13221 and the second ray window 15221 limits the shape of the filter 140, and thus limits the width of the ray beam, which plays a role in collimation. Optionally, the shape and size of the first radiation window 13221 are the same as the shape and size of the second radiation window, and at this time, the radiation can be emitted along the first radiation window 13221 and the second radiation window 15221.

Optionally, the shape and size of the first radiation window 13221 is different from the shape and size of the second radiation window 15221. That is, the sizes of the installation windows of the filter segments 140 are all different. In this way, the width of the beam of rays can be changed during the switching combination of the filters 140, thereby performing the collimation function. Moreover, the width of the beam is determined by the smaller of the first radiation window 13221 and the second radiation window 15221.

In other embodiments of the present invention, the switching structure 130 may include at least one second transmission assembly 152 and the first transmission assembly 132. That is, the filter 140 has different layers along the ray emitting direction to satisfy different combination experiment conditions of the filter 140. It should be noted that the structures and the working principles of the second transmission assembly 152 and the first transmission assembly 132 in the present embodiment have been mentioned above, and are not repeated herein.

Referring to fig. 1 to 3, the CT collimation apparatus 100 of the present invention can realize fast switch switching of the ray opening 111 through the shielding assembly 120, so that the rays output by the ray generator and the shielding assembly 120 cooperate to realize pulse type wire releasing, so as to achieve the purpose of controlling the time of ray window exit, and effectively reduce the dose radiation received by the scanned object, and at the same time, because the number of rays irradiated on the ray detector is small, the CT collimation apparatus 100 can also protect the ray detector, and effectively improve the service life of the ray detector. Moreover, the switching structure 130 can realize automatic switching of different combinations of the filter plates 140, improve adaptability to different scanning objects, and realize the function of ray beam collimation.

The invention also provides Micro CT equipment, which comprises an electronic component, a fixed rack, a rotating rack and the CT collimation device 100 in the embodiment, wherein the rotating rack is rotationally connected to the fixed rack, the electronic component at least comprises a ray generator and a ray detector, the ray generator and the ray detector are symmetrically arranged on the rotating rack, and the CT collimation device 100 is arranged on the rotating rack and corresponds to the ray generator. The ray generator is a bulb tube which can emit X-rays. The ray generator can emit rays to a scanning area of a scanning object, and the ray detector receives the rays passing through the scanning area and processes information of the rays so as to image the scanning area of the scanning object, thereby facilitating medical diagnosis or experimental result analysis.

After the Micro CT equipment adopts the CT collimating device 100 of the embodiment, rays can be emitted in a pulse mode, so that a ray window can be shielded by using the shielding component 120 under the condition that the rays are not needed in the scanning process; when the ray is to be used, the shielding component 120 opens the ray opening 111 again, so that the irradiation dose of the ray can be reduced, the damage to a scanned object is reduced, meanwhile, the ray detector can be protected, and the service life of the ray detector is prolonged.

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

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

Claims

1. A CT collimation apparatus, comprising:

the mounting base plate is provided with a ray opening;

the filter assembly comprises at least two groups of filter plates, and different filter conditions can be provided between the at least two groups of filter plates in a combined mode.

2. The CT collimation device as recited in claim 1, wherein the shielding assembly comprises a shielding power source, a shielding transmission assembly and a shielding shutter, the shielding power source is disposed on the mounting base plate, and the shielding transmission assembly is in transmission connection with the shielding power source and the shielding shutter.

3. The CT collimation device of claim 2, wherein the shutter drive assembly comprises a crank link connecting the shutter power source and the shutter paddle.

4. The CT collimation device of claim 3, wherein the shutter drive assembly further comprises a guide disposed on the mounting base plate, the shutter paddle being movable relative to the mounting base plate via the guide.

5. The CT collimation device as recited in claim 1, wherein the filter assembly comprises a first filter switching structure and a second filter switching structure, and the two sets of filters are respectively disposed on the first filter switching structure and the second filter switching structure.

6. The CT collimation device as recited in claim 5, wherein the first filtering switching structure comprises a first power source and a first transmission assembly, the first power source is disposed on the mounting base plate, the first transmission assembly is connected to the first power source, the first transmission assembly is located on a side of the ray opening away from the shielding shutter, and the first transmission assembly is provided with a plurality of different filters.

7. The CT collimation apparatus as recited in claim 6, wherein the first transmission assembly comprises a first switching gear and a second switching gear engaged with each other, the first switching gear being mounted to the first power source, the second switching gear being rotatably mounted to the mounting base, the second switching gear having a plurality of distinct filters mounted thereon, the second switching gear being adapted to drive at least one of the filters to align with the radiation aperture.

8. The CT collimation apparatus of claim 7, wherein the second switching gear has a plurality of first radiation windows of different sizes, at least a portion of the first radiation windows being configured to receive the filter.

9. The CT collimation device as recited in claim 8, wherein the second filtering switching structure comprises a second power source and a second transmission assembly, the second power source is disposed on the mounting plate, the second transmission assembly is connected to the second power source, the second transmission assembly is mounted with a plurality of different filters, and the second transmission assembly and the first transmission assembly are stacked, so that the filters of the second transmission member and the filters of the first transmission assembly are selectively overlapped.

10. The CT collimation apparatus as recited in claim 9, wherein the second transmission assembly comprises a combination gear and a combination carrier plate engaged with each other, the combination gear is mounted to the second power source, the combination carrier plate is movably mounted to the mounting plate, the combination carrier plate has a plurality of different filters mounted thereon, and the combination carrier plate drives at least one of the filters to align with the radiation opening.

11. The CT collimation apparatus of claim 10, wherein the composite carrier has a plurality of second radiation windows of different sizes, at least a portion of the second radiation windows being configured to receive the filters.

12. The CT collimation apparatus of claim 11, wherein a shape and size of the first radiation window is the same as and/or different from a shape and size of the second radiation window.

13. A CT device comprising an electronic component, a stationary gantry, a rotating gantry, and a CT collimating apparatus as claimed in any one of claims 1 to 12, wherein the rotating gantry is rotatably connected to the stationary gantry, the electronic component comprises at least a radiation generator and a radiation detector, the radiation generator and the radiation detector are symmetrically disposed on the rotating gantry, and the CT collimating apparatus is disposed on the rotating gantry and corresponds to the radiation generator.