WO2022041092A1 - Ct成像系统及其成像方法 - Google Patents

Ct成像系统及其成像方法 Download PDF

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Publication number
WO2022041092A1
WO2022041092A1 PCT/CN2020/111979 CN2020111979W WO2022041092A1 WO 2022041092 A1 WO2022041092 A1 WO 2022041092A1 CN 2020111979 W CN2020111979 W CN 2020111979W WO 2022041092 A1 WO2022041092 A1 WO 2022041092A1
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imaging
cold cathode
cathode
grid
imaging system
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PCT/CN2020/111979
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English (en)
French (fr)
Inventor
洪序达
梁栋
张其阳
蒋昌辉
郑海荣
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深圳先进技术研究院
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • A61B6/542—Control of apparatus or devices for radiation diagnosis involving control of exposure

Definitions

  • the invention relates to the technical field of X-ray imaging, in particular to a CT imaging system and an imaging method thereof.
  • Small animal micro-CT plays an important role in preclinical studies of small animal models represented by rats and mice, including bone structure and density imaging, tumor imaging, cardiac imaging, and lung imaging. Compared with other imaging methods, small animal micro-CT imaging has the advantages of high resolution, low cost, and high scanning efficiency. Currently, the resolution of small animal micro-CT imaging for in vitro imaging can reach 10 microns. However, for in vivo small animal imaging, the physiological motion of small animals is much faster than that of humans, which will bring significant motion artifacts and reduce the spatial resolution of CT imaging. Requirements for animal imaging.
  • the present invention provides a CT imaging system and an imaging method thereof, which can improve the temporal resolution and spatial resolution of CT imaging while reducing the radiation dose.
  • the specific technical scheme proposed by the present invention is: to provide a CT imaging system, the CT imaging system includes a cold cathode X-ray source, a probe, a control device, a rotating device, an imaging device, and a processor; the cold cathode X-ray source, The probes are respectively electrically connected to the control device, and the processor is electrically connected to the imaging device; the cold cathode X-ray source is used to generate X-rays for CT imaging, and the rotation device is used to control the scanning object Scanning angle, the probe is used for acquiring physiological signals of the scanning object at different scanning angles, and the control device is used for triggering the cold cathode X-ray source according to the physiological signals of the scanning object at different scanning angles
  • the imaging device is configured to acquire projection images of the X-rays passing through the scanning object at different scanning angles
  • the processor is configured to reconstruct the projection images to obtain CT images of the scanning object.
  • the cold cathode X-ray source includes at least one cold cathode X-ray tube, and each of the cold cathode X-ray tubes includes a vacuum cavity and a cathode, a grid, a focusing electrode, and an anode disposed in the vacuum cavity.
  • the grid is located between the cathode and the focusing electrode
  • the focusing electrode is located between the grid and the anode
  • the side of the anode facing the cathode is an inclined surface.
  • the cathode includes a substrate and an electron emission layer disposed on the substrate.
  • the material of the electron emission layer is selected from one of carbon nanotubes, graphene, zinc oxide nanorods, boron nitride nanotubes, and titanium dioxide nanotubes.
  • the grid includes a grid and a bracket, the bracket is provided with an opening, the opening corresponds to the electron emission layer, and the grid is fixed in the opening; the focusing electrode is provided with a focusing electrode The focusing hole corresponds to the opening, and the diameter of the light spot after passing through the focusing hole is 10-50 ⁇ m.
  • the angle between the side of the anode facing the cathode and the plane where the cathode is located is 10°-15°, and/or the vacuum degree of the vacuum chamber is 10 -5 -10 -7 Pa, and/or when the number of the cold cathode X-ray tubes is multiple, the multiple cold cathode X-ray tubes are arranged in a circular arc, and the coverage angle of the X-rays emitted by the multiple cold cathode X-ray tubes 1° to 90°.
  • the imaging device is a CMOS flat panel detector or a photon counting detector.
  • the CT imaging system further includes a power supply device, the power supply device includes a first power supply, a second power supply and a third power supply, the first power supply is used to provide a voltage for the grid, and the second voltage A source is used to power the focusing electrode and the third power source is used to power the anode.
  • the power supply device includes a first power supply, a second power supply and a third power supply
  • the first power supply is used to provide a voltage for the grid
  • the second voltage A source is used to power the focusing electrode
  • the third power source is used to power the anode.
  • the rotating device includes a carrying platform and an electromechanical control module.
  • the present application also provides an imaging method for a CT imaging system as described above, the imaging method comprising:
  • the rotating device rotates the scanning object to different scanning angles
  • the probe acquires the physiological signals of the scanning object under different scanning angles
  • the control device triggers the activation of the cold cathode X-ray source according to the physiological signals of the scanning object under different scanning angles;
  • the imaging device collects projection images of the X-rays through the scanning object under different scanning angles
  • the processor reconstructs the projection image to obtain a CT image of the scanned object.
  • the CT imaging system obtained by the present invention obtains the physiological signals of the scanning object under different scanning angles through the probe, and then triggers the opening of the cold cathode X-ray source through the control device according to the physiological signals of the scanning object under different scanning angles, so as to realize the corresponding X-ray exposure for each physiological signal, thereby significantly reducing the artifacts caused by motion, improving the spatial resolution of CT imaging, and because the cold cathode X-ray source can quickly respond to external trigger signals to start, start and shut down time
  • the interval is very short, thereby improving the temporal resolution of CT imaging, while reducing the radiation dose, enabling ultra-low-dose CT imaging.
  • FIG. 1 is a schematic structural diagram of a CT imaging system in an embodiment of the present invention.
  • Fig. 2 is the exit light path diagram of the cold cathode X-ray source in the embodiment of the present invention
  • FIG. 3 is a schematic structural diagram of a cold cathode X-ray tube in an embodiment of the present invention.
  • FIG. 5 is a flowchart of an imaging method of a CT imaging system in an embodiment of the present invention.
  • the CT imaging system includes a cold cathode X-ray source, a probe, a control device, a rotation device, an imaging device, and a processor.
  • the cold cathode X-ray source and the probe are respectively electrically connected to the control device
  • the processor is electrically connected to the imaging device
  • the cold cathode X-ray source is used to generate X-rays for CT imaging
  • the rotating device is used to control the scanning angle of the scanning object
  • the probe It is used to acquire the physiological signals of the scanning object under different scanning angles
  • the control device is used to trigger the opening of the cold cathode X-ray source according to the physiological signals of the scanning object under different scanning angles
  • the imaging device is used to collect X-rays through the scanning object in the Projection images under different scanning angles
  • the processor is used to reconstruct the projection images to obtain CT images of the scanned object.
  • the CT imaging system acquires the physiological signals of the scanning object at different scanning angles through the probe, and then triggers the activation of the cold cathode X-ray source through the control device according to the physiological signals of the scanning object at different scanning angles, so as to realize the corresponding X-ray exposure of a physiological signal, thereby significantly reducing motion-induced artifacts, improving the spatial resolution of CT imaging, and because the cold cathode X-ray source can quickly respond to an external trigger signal with a very short turn-on, turn-on, and turn-off time interval. This improves the temporal resolution of CT imaging, reduces radiation dose, and achieves ultra-low-dose CT imaging.
  • the CT imaging system in this embodiment includes a cold cathode X-ray source 1 , a probe 2 , a control device 3 , a rotation device 4 , an imaging device 5 , and a processor 6 .
  • the cold cathode X-ray source 1 and the probe 2 are respectively electrically connected to the control device 3
  • the processor 6 is electrically connected to the imaging device 5 .
  • the cold cathode X-ray source 1 is used to generate X-rays for CT imaging, the rotating device 4 is used to control the scanning angle of the scanning object 7, the probe 2 is used to obtain the physiological signals of the scanning object 7 under different scanning angles, and the control device 3 is used for The activation of the cold cathode X-ray source 1 is triggered according to the physiological signals of the scanning object 7 under different scanning angles.
  • the imaging device 5 is used to collect the projection images of X-rays passing through the scanning object 7 under different scanning angles. The projection image is reconstructed to obtain a CT image of the scanned object 7 .
  • the scanning angle of the scanning object 7 mentioned here refers to the angle at which the rotating device 4 drives the scanning object 7 to rotate. Specifically, the initial scanning angle of the scanning object 7 is 0°, that is, the first scanning angle is 0°, and the probe 2. After detecting the physiological signal of the scanning object 7, an electrical signal is sent to the control device 3. The control device 3 generates a trigger signal and triggers the cold cathode X-ray source 1 through the trigger signal. The cold cathode X-ray source 1 is turned on and generates X-rays incident to the scan.
  • the projection image after the X-rays pass through the scanning object 7 is collected by the imaging device 5, and the imaging device 5 sends the collected CT image to the processor 6, and then the rotating device 4 rotates to drive the scanning object 7 to rotate, and the rotating
  • the angle is ⁇ , for example, ⁇ is 0.5°, that is, the second scanning angle is ⁇
  • the probe 2 detects the physiological signal of the scanning object 7 again and sends an electrical signal to the control device 3, and the control device 3 generates a trigger signal and triggers
  • the signal triggers the cold cathode X-ray source 1, the cold cathode X-ray source 1 is turned on and generates X-rays that are incident on the scanning object 7, and the projection image after the X-rays pass through the scanning object 7 is collected by the imaging device 5, and the imaging device 5 will collect the image.
  • the obtained CT image is sent to the processor 6, and so on, until the scanning angle reaches a predetermined value or the number of scans reaches a predetermined number, and finally, the processor 6 reconstructs the received multiple projection images to obtain a CT image of the scanned object 7.
  • the probe 2 obtains the physiological signals of the scanning object 7 under different scanning angles, and then the probe 2 sends the obtained physiological signals of the scanning object 7 under different scanning angles to the control device, and the control device 3 then according to the scanning object 7 Physiological signals at different scanning angles are used to trigger the activation of the cold cathode X-ray source, realizing X-ray exposure corresponding to each physiological signal, thereby significantly reducing motion artifacts and improving the spatial resolution of CT imaging.
  • the cold cathode X-ray source can be activated quickly in response to an external trigger signal and the time interval between activation and deactivation is very short, the time resolution of microseconds can be achieved while the radiation dose can be reduced.
  • the application of the CT imaging system in this embodiment to the imaging of living small animals can effectively improve the spatial resolution and temporal resolution of CT imaging, and at the same time, it can also realize ultra-low dose CT imaging and avoid excessive X-ray radiation dose. It changes the physiological structure of small animals and affects the correct judgment of the development process of the disease and the effect of drugs in clinical research.
  • the cold cathode X-ray source 1 includes a cold cathode X-ray tube 10
  • the cold cathode X-ray tube 10 includes a vacuum chamber 11 , a cathode 12 and a grid disposed in the vacuum chamber 11 .
  • Focusing electrode 14 and anode 15, the grid 13 is located between the cathode 12 and the focusing electrode 14, the focusing electrode 14 is located between the grid 13 and the anode 15, and the side of the anode 15 facing the cathode 12 is a slope 150.
  • the vacuum degree of the vacuum chamber 11 in this embodiment is 10 -5 to 10 -7 Pa.
  • the cathode 12 is located at the bottom of the vacuum chamber 11, and is used for generating and generating electron beams.
  • the cathode 12 includes a substrate 120 and an electron emission layer 121 disposed on the substrate 120.
  • the material of the substrate 120 is a conductive material.
  • the substrate 120 may be a metal sheet, for example, the substrate 120 may be selected from a steel sheet, a copper sheet, a titanium sheet, and a molybdenum sheet; the substrate 120 may also be a silicon sheet coated with a metal material, and the metal material One selected from steel, copper, titanium and molybdenum.
  • the material of the electron emission layer 121 is selected from carbon nanotubes, graphene, zinc oxide nanorods, boron nitride nanotubes, and titanium dioxide nanotubes.
  • the shape of the electron emission layer 121 is an ellipse or a rectangle, so as to satisfy the structure of the reflective anode 15 to obtain the focal point of X-rays with uniform dimensions in all directions.
  • the grid 13 is used to provide the electric field required by the electron emission layer 121 to emit electron beams, and includes a grid 130 and a bracket 131 .
  • the bracket 131 is provided with an opening 130 , the opening 130 corresponds to the electron emission layer 121 , and the grid 130 is fixed in the opening 130 .
  • the grid 130 has a certain aperture ratio, so that the electron beam emitted by the electron emission layer 121 can be incident on the anode 15 through the grid 130 .
  • the material of the grid 130 may be tungsten or molybdenum.
  • the focusing electrode 14 is fixedly disposed above the grid 13 for focusing the electron beam emitted by the electron emission layer 121 .
  • the focusing electrode 14 is provided with a focusing hole 140.
  • the focusing hole 140 corresponds to the opening 130.
  • the shape of the focusing hole 140 can be a circle, an ellipse or a rectangle.
  • the tube current of the cold cathode X-ray tube 10 in this embodiment is 0.1-1 mA, and the tube voltage is 20-65 kV, so that the diameter of the light spot after focusing through the focusing hole 140 is 10-50 ⁇ m, that is, this embodiment
  • the size of the microfocus in the example is 10 to 50 ⁇ m.
  • the anodes 15 are arranged at intervals above the focusing electrode 14 and fixed on the top of the vacuum chamber 11 , which are used to accelerate the electron beam emitted by the electron emission layer 121 to obtain high-energy electrons, and bombard the target on the anode 15 with the high-energy electrons
  • the target material is a tungsten target.
  • the angle between the side of the anode 15 facing the cathode 12 and the plane where the cathode 12 is located is 10° to 15°, that is, the angle between the inclined plane 150 and the horizontal plane is 10° to 15°.
  • X-ray exit window 110 X-rays are reflected from the target disposed on the inclined surface 150 and exit from the window 110, as shown in FIG. 3, which shows the exit light path diagram of the cold cathode X-ray tube.
  • the material of the window 110 is aluminum or beryllium.
  • the cold cathode X-ray source 1 includes a plurality of cold cathode X-ray tubes 10 , preferably, the number of the plurality of cold cathode X-ray tubes 10 is 2-180, FIG. 4 shows a case where the cold cathode X-ray source 1 includes 11 cold cathode X-ray tubes 10 as an example. It should be noted that this is only shown here as an example, and is not intended to be limiting.
  • the plurality of cold cathode X-ray tubes 10 are arranged in an arc shape, and the coverage angle of the X-rays emitted by the plurality of cold cathode X-ray tubes 10 is 1° ⁇ 90°. In the actual process, a plurality of cold cathode X-ray tubes 10 can be turned on in sequence as required to emit X-rays from different angles.
  • the control device 3 includes a trigger circuit, and the trigger circuit is used to realize the switching of the cold cathode X-ray source 1 and the adjustment of the exposure time.
  • the control device 3 also includes a timing sequence.
  • the control circuit (not shown), the timing control circuit is used to control the trigger circuit to trigger the plurality of cold cathode X-ray tubes 10 in sequence at different time periods, so as to realize switching between different cold cathode X-ray tubes 10 .
  • the rotating device 4 in this embodiment includes a bearing platform 41 and an electromechanical control module 42 .
  • the carrying table 41 is used for carrying and fixing the scanning object 7
  • the electromechanical control module 42 is used for controlling the rotation angle of the carrying table 41 .
  • the control device 3 and the electromechanical control module 42 in this embodiment are all connected to the processor 6 .
  • the trigger circuit in the control device 3 is connected to the processor 6 , and the transmission stops when the trigger circuit stops triggering the cold cathode X-ray tube 10 .
  • the trigger instruction is sent to the processor 6.
  • the control device 3 stops working.
  • the processor 6 sends a rotation instruction to the electromechanical control module 42 after receiving the stop trigger instruction.
  • the electromechanical control module 42 sends feedback information to the processor 6.
  • the processor 6 controls the control device 3 to turn on after receiving the feedback information from the electromechanical control module 42.
  • the circuit triggers the cold cathode X-ray tube 10 when it receives the physiological signal of the scanning object 7 at a predetermined angle obtained by the probe 2 again.
  • the timing control circuit in the control device 3 controls the trigger circuit to trigger the plurality of cold cathode X-ray tubes 10 in sequence.
  • the imaging device 5 is a CMOS flat panel detector or a photon counting detector. Since the photon counting detector has the characteristics of high-speed data acquisition, high spatial resolution and high resolution capability, preferably, the imaging device 5 in this embodiment is For the photon counting detector, the pixel size of the photon counting detector is not greater than 50 ⁇ m, and the photon counting detector may be a cadmium telluride type photon counting detector or a cadmium zinc telluride type photon counting detector.
  • the CT imaging system of this embodiment further includes a power supply device 8.
  • the power supply device 8 includes a first power supply, a second power supply, and a third power supply (not shown).
  • the first power supply is used to provide voltage for the gate 13, and the second voltage supply It is used to supply power to the focusing electrode 14
  • the third power supply is used to supply power to the anode 15 .
  • the power supply device 8 can also be used as a power supply for the entire CT imaging system, and the third power supply in this embodiment is also used to supply power to the processor 6 .
  • the CT imaging system in this embodiment further includes a display 9, and the display 9 is electrically connected to the processor 6, and is used for intuitively displaying the processing result of the processor 6.
  • this embodiment also provides an imaging method of the above CT imaging system, and the imaging method includes the steps:
  • the rotating device 4 rotates the scanning object 7 to different scanning angles
  • the probe 2 acquires the physiological signals of the scanning object 7 under different scanning angles
  • control device 3 triggers the opening of the cold cathode X-ray source 1 according to the physiological signals of the scanning object 7 under different scanning angles;
  • the imaging device 5 collects projection images of the X-ray through the scanning object 7 under different scanning angles;
  • the processor 6 reconstructs the projection image to obtain a CT image of the scanning object 7 .
  • step S1 rotating the scanning object 7 to different scanning angles is realized by controlling the rotation angle of the carrying platform 41 by the electromechanical control module 42 in the rotating device 4, wherein the electromechanical control module 42 is connected to the processor 6 and can be controlled by the electromechanical control module 42.
  • the processor 6 sends instructions to the electromechanical control module 42 to achieve a predetermined angle of rotation.
  • the initial scanning angle of the scanning object 7 is 0°, that is, the first scanning angle is 0°.
  • the probe 2 starts to detect the scanning object 7.
  • the exposure time of the cold cathode X-ray source 1 is controlled by the control device 3.
  • the control device 3 controls the cold cathode X-ray source 1. closure.
  • the rotating device 4 drives the scanning object 7 to rotate, and the rotation angle is ⁇ , that is, the second scanning angle is ⁇ , and the probe 2 starts to detect the physiological signal of the scanning object 7 again.
  • the control device 3 After the physiological signal of the object 7 sends an electrical signal to the control device 3, the control device 3 generates a trigger signal again and triggers the cold cathode X-ray source 1 through the trigger signal, the cold cathode X-ray source 1 is turned on and generates X-rays incident on the scanning object 7,
  • the projection image after the X-ray passes through the scanning object 7 is collected by the imaging device 5, and the imaging device 5 sends the collected CT image to the processor 6, and so on, until the scanning angle reaches a predetermined value or the number of scans reaches a predetermined number, Finally, the processor 6 reconstructs the received multiple projection images to obtain a CT image of the scanning object 7 .
  • the probe 2 acquires the physiological signals of the scanning object 7 under different scanning angles, and then the control device 3 triggers the activation of the cold cathode X-ray source according to the physiological signals of the scanning object 7 under different scanning angles, X-ray exposure corresponding to each physiological signal is achieved, thereby significantly reducing motion artifacts and improving the spatial resolution of CT imaging.
  • the cold cathode X-ray source can be activated quickly in response to an external trigger signal and the time interval between activation and deactivation is very short, the time resolution of microseconds can be achieved while the radiation dose can be reduced.
  • the application of the imaging method in this embodiment to the imaging of living small animals can effectively improve the spatial resolution and temporal resolution of CT imaging, and at the same time, it can also realize ultra-low dose CT imaging, avoiding excessive X-ray radiation dose Change the physiological structure of small animals and affect the correct judgment of disease development process and drug effects in clinical research.

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Abstract

本发明提供了一种CT成像系统及其成像方法，所述CT成像系统包括冷阴极X射线源、探头、控制装置、旋转装置、成像装置、处理器；冷阴极X射线源、探头分别与控制装置电性连接，处理器与成像装置电性连接；冷阴极X射线源用于产生CT成像的X射线，旋转装置用于控制扫描对象的扫描角度，探头用于获取扫描对象在不同扫描角度下的生理信号，控制装置用于根据扫描对象在不同扫描角度下的生理信号触发冷阴极X射线源的开启，成像装置用于采集X射线透过所述扫描对象在不同扫描角度下的投影图像，处理器用于对投影图像进行重建获得扫描对象的CT图像。本发明提供的CT成像系统能够显著降低运动带来的伪影，提升CT成像的分辨率，同时能够实现超低剂量CT成像。

Description

CT成像系统及其成像方法 技术领域
本发明涉及X射线成像技术领域，尤其涉及一种CT成像系统及其成像方法。
背景技术
小动物显微CT在以大鼠和小鼠为代表的小动物模型临床前的研究中发挥着重要的作用，这些研究包括骨头结构和密度成像、肿瘤成像、心脏成像、肺部成像等。相比其他成像方法，小动物显微CT成像具有分辨率高、成本低、扫描效率高的优势。目前，小动物显微CT成像对于体外成像的分辨率可以达到10微米。但是，对于活体小动物成像，由于小动物的生理运动比人类要快得多，这将会带来显著的运动伪影而降低CT成像的空间分辨率，因此，该分辨率仍然不能满足活体小动物成像的要求。
发明内容
为了解决现有技术的不足，本发明提供一种CT成像系统及其成像方法，能够提升CT成像的时间分辨率和空间分辨率的同时减少辐射剂量。
本发明提出的具体技术方案为：提供一种CT成像系统，所述CT成像系统包括冷阴极X射线源、探头、控制装置、旋转装置、成像装置、处理器；所述冷阴极X射线源、探头分别与所述控制装置电性连接，所述处理器与所述成像装置电性连接；所述冷阴极X射线源用于产生CT成像的X射线，所述旋转装置用于控制扫描对象的扫描角度，所述探头用于获取所述扫描对象在不同扫描角度下的生理信号，所述控制装置用于根据所述扫描对象在不同扫描角度下的生理信号触发所述冷阴极X射线源的开启，所述成像装置用于采集所述X射线透过所述扫描对象在不同扫描角度下的投影图像，所述处理器用于对所述投影图像进行重建获得所述扫描对象的CT图像。
进一步地，所述冷阴极X射线源包括至少一个冷阴极X射线管，每一个所述冷阴极X射线管包括真空腔体及设置于所述真空腔体内的阴极、栅极、聚 焦极、阳极，所述栅极位于所述阴极与所述聚焦极之间，所述聚焦极位于所述栅极与所述阳极之间，所述阳极朝向所述阴极的一面为斜面。
进一步地，所述阴极包括衬底及设置于所述衬底上的电子发射层。
进一步地，所述电子发射层的材料选自碳纳米管、石墨烯、氧化锌纳米棒、氮化硼纳米管、二氧化钛纳米管中的一种。
进一步地，所述栅极包括栅网和支架，所述支架设有开口，所述开口与所述电子发射层对应，所述栅网固定于所述开口中；所述聚焦极上设有聚焦孔，所述聚焦孔与所述开口对应，通过所述聚焦孔后的光斑直径为10～50μm。
进一步地，所述阳极朝向所述阴极的一面与所述阴极所在的平面之间的夹角为10°～15°，和/或所述真空腔体的真空度为10 -5～10 -7Pa，和/或所述冷阴极X射线管的数量为多个时，多个所述冷阴极X射线管呈圆弧形排列，多个所述冷阴极X射线管发出的X射线的覆盖角度为1°～90°。
进一步地，所述成像装置为CMOS平板探测器或光子计数探测器。
进一步地，所述CT成像系统还包括供电装置，所述供电装置包括第一电源、第二电源及第三电源，所述第一电源用于为所述栅极提供电压，所述第二电压源用于为所述聚焦极供电，所述第三电源用于为所述阳极供电。
进一步地，所述旋转装置包括承载台及机电控制模块。
本申请还提供了一种如上任一所述的CT成像系统的成像方法，所述成像方法包括：
旋转装置将扫描对象旋转至不同的扫描角度；
探头获取所述扫描对象在不同扫描角度下的生理信号；
控制装置根据所述扫描对象在不同扫描角度下的生理信号触发冷阴极X射线源的开启；
成像装置采集所述X射线透过所述扫描对象在不同扫描角度下的投影图像；
处理器对所述投影图像进行重建获得所述扫描对象的CT图像。
本发明提供的CT成像系统通过探头获取扫描对象在不同扫描角度下的生理信号，然后通过控制装置根据所述扫描对象在不同扫描角度下的生理信号来触发冷阴极X射线源的开启，实现对应于每一个生理信号的X射线曝光，从而显著降低了运动带来的伪影，提升了CT成像的空间分辨率，且由于冷阴极X射线源能够快速响应外部触发信号而启动、启动和关闭时间间隔很短，从而提升了CT成像的时间分辨率，同时减少辐射剂量，实现超低剂量CT成像。
附图说明
图1为本发明实施例中的CT成像系统的结构示意图；
图2为本发明实施例中的冷阴极X射线源的出射光路图；
图3为本发明实施例中的冷阴极X射线管的结构示意图；
图4为本发明实施例中的冷阴极X射线源的另一出射光路图；
图5为本发明实施例中的CT成像系统的成像方法的流程图。
具体实施方式
以下，将参照附图来详细描述本发明的实施例。然而，可以以许多不同的形式来实施本发明，并且本发明不应该被解释为限制于这里阐述的具体实施例。相反，提供这些实施例是为了解释本发明的原理及其实际应用，从而使本领域的其他技术人员能够理解本发明的各种实施例和适合于特定预期应用的各种修改。在附图中，相同的标号将始终被用于表示相同的元件。
本申请提供的CT成像系统包括冷阴极X射线源、探头、控制装置、旋转装置、成像装置、处理器。冷阴极X射线源、探头分别与控制装置电性连接，处理器与成像装置电性连接，冷阴极X射线源用于产生CT成像的X射线，旋转装置用于控制扫描对象的扫描角度，探头用于获取扫描对象在不同扫描角度下的生理信号，控制装置用于根据扫描对象在不同扫描角度下的生理信号触发冷阴极X射线源的开启，成像装置用于采集X射线透过扫描对象在不同扫描角度下的投影图像，处理器用于对投影图像进行重建获得扫描对象的CT图像。
本申请提供的CT成像系统通过探头获取扫描对象在不同扫描角度下的生理信号，然后通过控制装置根据扫描对象在不同扫描角度下的生理信号来触发冷阴极X射线源的开启，实现对应于每一个生理信号的X射线曝光，从而显著降低了运动带来的伪影，提升了CT成像的空间分辨率，且由于冷阴极X射线源能够快速响应外部触发信号而启动、启动和关闭时间间隔很短，从而提升了CT成像的时间分辨率，同时减少辐射剂量，实现超低剂量CT成像。
下面通过具体的实施例并结合附图来对本申请中的CT成像系统及其成像方法进行详细的描述。
参照图1，本实施例中的CT成像系统包括冷阴极X射线源1、探头2、控制装置3、旋转装置4、成像装置5、处理器6。冷阴极X射线源1、探头2分别与控制装置3电性连接，处理器6与成像装置5电性连接。冷阴极X射线源1用于产生CT成像的X射线，旋转装置4用于控制扫描对象7的扫描角度，探头2用于获取扫描对象7在不同扫描角度下的生理信号，控制装置3用于根据扫描对象7在不同扫描角度下的生理信号触发冷阴极X射线源1的开启，成像装置5用于采集X射线透过扫描对象7在不同扫描角度下的投影图像，处理器6用于对投影图像进行重建获得扫描对象7的CT图像。
这里所说的扫描对象7的扫描角度指的是旋转装置4带动扫描对象7旋转的角度，具体地，扫描对象7初始的扫描角度为0°，即第一次的扫描角度为0°，探头2检测到扫描对象7的生理信号后发送电信号至控制装置3，控制装置3生成触发信号并通过触发信号触发冷阴极X射线源1，冷阴极X射线源1开启并产生X射线入射至扫描对象7，X射线透过扫描对象7后的投影图像被成像装置5采集，成像装置5再将采集到的CT图像发送给处理器6，然后，旋转装置4旋转带动扫描对象7转动，转动的角度为α，例如，α为0.5°，即第二次的扫描角度为α，探头2再次检测到扫描对象7的生理信号后发送电信号至控制装置3，控制装置3生成触发信号并通过触发信号触发冷阴极X射线源1，冷阴极X射线源1开启并产生X射线入射至扫描对象7，X射线透过扫描对象7后的投影图像被成像装置5采集，成像装置5再将采集到的CT图像发送给处理器6，以此类推，直到扫描角度达到预定值或者扫描次数达到预定次数，最后，处理器6对接收到的多个投影图像进行重建获得扫描对象7的CT图像。
本实施例通过探头2获取扫描对象7在不同扫描角度下的生理信号，然后探头2将获取的扫描对象7在不同扫描角度下的生理信号发送给控制装置，控制装置3再根据扫描对象7在不同扫描角度下的生理信号来触发冷阴极X射线源的开启，实现对应于每一个生理信号的X射线曝光，从而显著降低了运动带来的伪影，提升了CT成像的空间分辨率。此外，由于冷阴极X射线源能够快速响应外部触发信号而启动且启动和关闭时间间隔很短，能够实现微秒级的时间分辨率的同时减少辐射剂量。因此，本实施例中的CT成像系统应用到活体小动物成像上能够有效提升CT成像的空间分辨率和时间分辨率，同时，还能够实现超低剂量CT成像，避免过多的X射线辐射剂量而改变小动物的生理结构并影响对临床研究中疾病的发展过程和药物作用的正确判断。
参照图2、图3，具体地，冷阴极X射线源1包括一个冷阴极X射线管10，冷阴极X射线管10包括真空腔体11及设置于真空腔体11内的阴极12、栅极13、聚焦极14、阳极15，栅极13位于阴极12与聚焦极14之间，聚焦极14位于栅极13与阳极15之间，阳极15朝向阴极12的一面为斜面150。其中，本实施例中真空腔体11的真空度为10 -5～10 -7Pa。
阴极12位于真空腔体11的底部，其用于产生并发生电子束，阴极12包括衬底120及设置于衬底120上的电子发射层121，衬底120的材质为导电材料，具体地，衬底120可以是金属片材，例如，衬底120可以选自钢片、铜片、钛片、钼片中的一种；衬底120也可以是涂覆有金属材料的硅片，金属材料选自钢、铜、钛、钼中的一种。
较佳地，电子发射层121的材料选自碳纳米管、石墨烯、氧化锌纳米棒、氮化硼纳米管、二氧化钛纳米管中的一种。在本实施例中，电子发射层121的形状为椭圆形或长方形，以满足反射式的阳极15的结构能够获得各向尺寸一致的X射线的焦点。
栅极13用于提供电子发射层121发射电子束所需要的电场，其包括栅网130和支架131，支架131用于固定栅网130，以使得栅网130架设于电子发射层121的上方。支架131设有开口130，开口130与电子发射层121对应，栅网130固定于开口130中。栅网130具有一定的开口率，使得电子发射层121发射的电子束能够通过栅网130入射至阳极15上。其中，栅网130的材质可以为钨或钼。
相应地，聚焦极14固定设置于栅极13的上方，其用于对电子发射层121发射的电子束进行聚焦。聚焦极14设有聚焦孔140，聚焦孔140与开口130对应，聚焦孔140的形状可以是圆形、椭圆形或者长方形，通过调节聚焦孔140的开口大小可以获得所需尺寸的微焦点，这里所说的微焦点指的是直径较小的光斑。
较佳地，本实施例中的冷阴极X射线管10的管电流为0.1～1mA、管电压为20～65kV，这样可以使得通过聚焦孔140聚焦后的光斑直径为10～50μm，即本实施例中的微焦点的大小为10～50μm。
阳极15间隔设置于聚焦极14的上方并固定于真空腔体11的顶部，其用于对电子发射层121发射的电子束进行加速，以获得高能电子，通过高能电子轰击阳极15上的靶材产生X射线，较佳地，靶材为钨靶。阳极15朝向阴极12的一面与阴极12所在的平面之间的夹角为10°～15°，即斜面150与水平面之间的夹角为10°～15°，真空腔体11上设有供X射线出射的窗口110，X射线经设置在斜面150上的靶材反射后从窗口110出射，如图3所示，图3示出了冷阴极X射线管的出射光路图。其中，窗口110的材质为铝或铍。
参照图4，在本实施例的另一实施方式中，冷阴极X射线源1包括多个冷阴极X射线管10，较佳地，多个冷阴极X射线管10的数量为2～180，图4中作为示例示出了冷阴极X射线源1包括11个冷阴极X射线管10的情况，需要说明的是，这里仅仅是作为示例示出，并不用于限定。多个冷阴极X射线管10呈圆弧形排列，多个冷阴极X射线管10发出的X射线的覆盖角度为1°～90°。在实际过程中可以根据需要依次开启多个冷阴极X射线管10，以从不同的角度发射X射线。
控制装置3包括触发电路，触发电路用于实现冷阴极X射线源1的开关和曝光时间的调节，在冷阴极X射线源1包括多个冷阴极X射线管10时，控制装置3还包括时序控制电路(图未示)，时序控制电路用于控制触发电路在不同的时间段依次触发多个冷阴极X射线管10，以实现不同冷阴极X射线管10之间的切换。为了实现精确控制，本实施例中的旋转装置4包括承载台41及机电控制模块42。其中，承载台41用于承载并固定扫描对象7，机电控制模块42用于控制承载台41的旋转角度。
本实施例中的控制装置3、机电控制模块42均与处理器6连接，具体地，控制装置3中的触发电路与处理器6连接，当触发电路停止触发冷阴极X射线管10时发送停止触发指令至处理器6，此时，控制装置3停止工作，处理器6在接收 到停止触发指令后发送旋转指令给机电控制模块42，机电控制模块42根据旋转指令控制承载台41旋转预定角度，当承载台41带动扫描对象7旋转至预定角度后，机电控制模块42再发送反馈信息给处理器6，处理器6在接收到机电控制模块42的反馈信息后控制控制装置3的开启，当触发电路再次接收到探头2获取的扫描对象7在预定角度下的生理信号时触发冷阴极X射线管10。其中，当冷阴极X射线源1包括多个冷阴极X射线管10时，控制装置3中的时序控制电路控制触发电路依次触发多个冷阴极X射线管10。
成像装置5为CMOS平板探测器或光子计数探测器，由于光子计数探测器具有高速数据采集、高空间分辨率和高能力分辨能力的特性，因此，较佳地，本实施例中的成像装置5为光子计数探测器，光子计数探测器的像素尺寸不大于50μm，光子计数探测器可以是碲化镉型光子计数探测器或碲锌镉型光子计数探测器。
本实施例的CT成像系统还包括供电装置8，供电装置8包括第一电源、第二电源及第三电源(图未示)，第一电源用于为栅极13提供电压，第二电压源用于为聚焦极14供电，第三电源用于为阳极15供电。当然，供电装置8也可以作为整个CT成像系统的供电电源，本实施例中的第三电源还用于为处理器6供电。
本实施例中的CT成像系统还包括显示器9，显示器9与处理器6电连接，其用于对处理器6的处理结果进行直观的显示。
参照图5，本实施例还提供了上述CT成像系统的成像方法，所述成像方法包括步骤：
S1、旋转装置4将扫描对象7旋转至不同的扫描角度；
S2、探头2获取扫描对象7在不同扫描角度下的生理信号；
S3、控制装置3根据扫描对象7在不同扫描角度下的生理信号触发冷阴极X射线源1的开启；
S4、成像装置5采集X射线透过扫描对象7在不同扫描角度下的投影图像；
S5、处理器6对投影图像进行重建获得扫描对象7的CT图像。
在步骤S1中，将扫描对象7旋转至不同的扫描角度是通过旋转装置4中的机电控制模块42控制承载台41的旋转角度来实现，其中，机电控制模块42与处理器6连接，可以通过处理器6来发送指令给机电控制模块42，以实现预定角度的旋转。
下面对步骤S2～S5进行详细的描述，扫描对象7初始的扫描角度为0°，即第一次的扫描角度为0°，在扫描角度为0°时，探头2开始检测扫描对象7的生理信号并在检测到扫描对象7的生理信号后发送电信号至控制装置3，控制装置3生成触发信号并通过触发信号触发冷阴极X射线源1，冷阴极X射线源1开启并产生X射线入射至扫描对象7上，X射线透过扫描对象7后的投影图像被成像装置5采集，成像装置5再将采集到的CT图像发送给处理器6，其中，为了避免过多的辐射剂量，通过控制装置3控制冷阴极X射线源1的曝光时间，例如，每一次扫描需要的曝光时间为3s，则在冷阴极X射线源1持续工作3s后，控制装置3控制冷阴极X射线源1关闭。第一次扫描结束后，通过旋转装置4旋转带动扫描对象7转动，转动的角度为α，即第二次的扫描角度为α，探头2再次开始检测扫描对象7的生理信号并在检测到扫描对象7的生理信号后发送电信号至控制装置3，控制装置3再次生成触发信号并通过触发信号触发冷阴极X射线源1，冷阴极X射线源1开启并产生X射线入射至扫描对象7，X射线透过扫描对象7后的投影图像被成像装置5采集，成像装置5再将采集到的CT图像发送给处理器6，以此类推，直到扫描角度达到预定值或者扫描次数达到预定次数，最后，处理器6对接收到的多个投影图像进行重建获得扫描对象7的CT图像。
本实施例中的成像方法通过探头2获取扫描对象7在不同扫描角度下的生理信号，然后通过控制装置3根据扫描对象7在不同扫描角度下的生理信号来触发冷阴极X射线源的开启，实现对应于每一个生理信号的X射线曝光，从而显著降低了运动带来的伪影，提升了CT成像的空间分辨率。此外，由于冷阴极X射线源能够快速响应外部触发信号而启动且启动和关闭时间间隔很短，能够实现微秒级的时间分辨率的同时减少辐射剂量。因此，本实施例中的成像方法应用到活体小动物成像上能够有效提升CT成像的空间分辨率和时间分辨率，同时，还能够实现超低剂量CT成像，避免过多的X射线辐射剂量而改变小动物的生理结构并影响对临床研究中疾病的发展过程和药物作用的正确判断。
以上所述仅是本申请的具体实施方式，应当指出，对于本技术领域的普通技术人员来说，在不脱离本申请原理的前提下，还可以做出若干改进和润饰， 这些改进和润饰也应视为本申请的保护范围。

Claims (20)

  1. 一种CT成像系统，其中，包括冷阴极X射线源、探头、控制装置、旋转装置、成像装置、处理器；所述冷阴极X射线源、探头分别与所述控制装置电性连接，所述处理器与所述成像装置电性连接；所述冷阴极X射线源用于产生CT成像的X射线，所述旋转装置用于控制扫描对象的扫描角度，所述探头用于获取所述扫描对象在不同扫描角度下的生理信号，所述控制装置用于根据所述扫描对象在不同扫描角度下的生理信号触发所述冷阴极X射线源的开启，所述成像装置用于采集所述X射线透过所述扫描对象在不同扫描角度下的投影图像，所述处理器用于对所述投影图像进行重建获得所述扫描对象的CT图像。
  2. 根据权利要求1所述的CT成像系统，其中，所述冷阴极X射线源包括至少一个冷阴极X射线管，每一个所述冷阴极X射线管包括真空腔体及设置于所述真空腔体内的阴极、栅极、聚焦极、阳极，所述栅极位于所述阴极与所述聚焦极之间，所述聚焦极位于所述栅极与所述阳极之间，所述阳极朝向所述阴极的一面为斜面。
  3. 根据权利要求2所述的CT成像系统，其中，所述阴极包括衬底及设置于所述衬底上的电子发射层。
  4. 根据权利要求3所述的CT成像系统，其中，所述电子发射层的材料选自碳纳米管、石墨烯、氧化锌纳米棒、氮化硼纳米管、二氧化钛纳米管中的一种。
  5. 根据权利要求4所述的CT成像系统，其中，所述栅极包括栅网和支架，所述支架设有开口，所述开口与所述电子发射层对应，所述栅网固定于所述开口中；所述聚焦极上设有聚焦孔，所述聚焦孔与所述开口对应，通过所述聚焦孔后的光斑直径为10～50μm。
  6. 根据权利要求2所述的CT成像系统，其中，所述阳极朝向所述阴极的一面与所述阴极所在的平面之间的夹角为10°～15°，和/或所述真空腔体的真空度为10 -5～10 -7Pa，和/或所述冷阴极X射线管的数量为多个时，多个所述冷阴极X射线管呈圆弧形排列，多个所述冷阴极X射线管发出的X射线的覆盖角度为1°～90°。
  7. 根据权利要求2所述的CT成像系统，其中，所述成像装置为CMOS平板探测器或光子计数探测器。
  8. 根据权利要求2所述的CT成像系统，其中，所述CT成像系统还包括供电装置，所述供电装置包括第一电源、第二电源及第三电源，所述第一电源用于为所述栅极提供电压，所述第二电压源用于为所述聚焦极供电，所述第三电源用于为所述阳极供电。
  9. 根据权利要求1所述的CT成像系统，其中，所述旋转装置包括承载台及机电控制模块。
  10. 根据权利要求2所述的CT成像系统，其中，所述旋转装置包括承载台及机电控制模块。
  11. 根据权利要求3所述的CT成像系统，其中，所述旋转装置包括承载台及机电控制模块。
  12. 一种CT成像系统的成像方法，其中，所述CT成像系统包括冷阴极X射线源、探头、控制装置、旋转装置、成像装置、处理器；所述冷阴极X射线源、探头分别与所述控制装置电性连接，所述处理器与所述成像装置电性连接；所述冷阴极X射线源用于产生CT成像的X射线，所述旋转装置用于控制扫描对象的扫描角度，所述探头用于获取所述扫描对象在不同扫描角度下的生理信号，所述控制装置用于根据所述扫描对象在不同扫描角度下的生理信号触发所述冷阴极X射线源的开启，所述成像装置用于采集所述X射线透过所述扫描对象在不同扫描角度下的投影图像，所述处理器用于对所述投影图像进行重建获得所述扫描对象的CT图像，所述成像方法包括：
    旋转装置将扫描对象旋转至不同的扫描角度；
    探头获取所述扫描对象在不同扫描角度下的生理信号；
    控制装置根据所述扫描对象在不同扫描角度下的生理信号触发冷阴极X射线源的开启；
    成像装置采集所述X射线透过所述扫描对象在不同扫描角度下的投影图像；
    处理器对所述投影图像进行重建获得所述扫描对象的CT图像。
  13. 根据权利要求12所述的成像方法，其中，所述冷阴极X射线源包括至少一个冷阴极X射线管，每一个所述冷阴极X射线管包括真空腔体及设置于所述真空腔体内的阴极、栅极、聚焦极、阳极，所述栅极位于所述阴极与所述聚焦极之间，所述聚焦极位于所述栅极与所述阳极之间，所述阳极朝向所述阴极的一面为斜面。
  14. 根据权利要求13所述的成像方法，其中，所述阴极包括衬底及设置于所述衬底上的电子发射层。
  15. 根据权利要求14所述的成像方法，其中，所述电子发射层的材料选自碳纳米管、石墨烯、氧化锌纳米棒、氮化硼纳米管、二氧化钛纳米管中的一种。
  16. 根据权利要求15所述的成像方法，其中，所述栅极包括栅网和支架，所述支架设有开口，所述开口与所述电子发射层对应，所述栅网固定于所述开口中；所述聚焦极上设有聚焦孔，所述聚焦孔与所述开口对应，通过所述聚焦孔后的光斑直径为10～50μm。
  17. 根据权利要求13所述的成像方法，其中，所述阳极朝向所述阴极的一面与所述阴极所在的平面之间的夹角为10°～15°，和/或所述真空腔体的真空度为10 -5～10 -7Pa，和/或所述冷阴极X射线管的数量为多个时，多个所述冷阴极X射线管呈圆弧形排列，多个所述冷阴极X射线管发出的X射线的覆盖角度为1°～90°。
  18. 根据权利要求13所述的成像方法，其中，所述成像装置为CMOS平板探测器或光子计数探测器。
  19. 根据权利要求13所述的成像方法，其中，所述CT成像系统还包括供电装置，所述供电装置包括第一电源、第二电源及第三电源，所述第一电源用于为所述栅极提供电压，所述第二电压源用于为所述聚焦极供电，所述第三电源用于为所述阳极供电。
  20. 根据权利要求12所述的成像方法，其中，所述旋转装置包括承载台及机电控制模块。
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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101461714A (zh) * 2007-12-21 2009-06-24 Ge医疗系统环球技术有限公司 X射线ct设备
CN101897593A (zh) * 2009-05-26 2010-12-01 清华大学 一种计算机层析成像设备和方法
CN103033525A (zh) * 2011-09-30 2013-04-10 清华大学 Ct系统和ct图像重建方法
CN106510747A (zh) * 2016-12-21 2017-03-22 北京朗视仪器有限公司 一种双源双探测器锥形束ct系统
CN110090039A (zh) * 2019-05-10 2019-08-06 中国科学院深圳先进技术研究院 一种ct成像系统及ct成像方法

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101461714A (zh) * 2007-12-21 2009-06-24 Ge医疗系统环球技术有限公司 X射线ct设备
CN101897593A (zh) * 2009-05-26 2010-12-01 清华大学 一种计算机层析成像设备和方法
CN103033525A (zh) * 2011-09-30 2013-04-10 清华大学 Ct系统和ct图像重建方法
CN106510747A (zh) * 2016-12-21 2017-03-22 北京朗视仪器有限公司 一种双源双探测器锥形束ct系统
CN110090039A (zh) * 2019-05-10 2019-08-06 中国科学院深圳先进技术研究院 一种ct成像系统及ct成像方法

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