CN115399798B - Photon counting multi-spectral CT imaging device and method - Google Patents
Photon counting multi-spectral CT imaging device and method Download PDFInfo
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Abstract
The application provides a photon counting multi-energy spectrum CT imaging device and method, wherein the imaging device comprises a ray generating device, a surface array detector, a sheet microchannel plate, a photomultiplier element, a data transmission industrial personal computer and an image reconstruction industrial personal computer, wherein the surface array detector comprises a sheet scintillation crystal which is configured to convert rays into visible light, the sheet microchannel plate is coupled with the sheet scintillation crystal one to one and is configured to selectively pass the visible light converted by the sheet scintillation crystal, the photomultiplier element is coupled with the sheet microchannel plate to convert the visible light which is selected to pass through into scintillation pulse signals, the data transmission industrial personal computer is configured to be in communication connection with the ray generating device and the surface array detector to control the ray generating device and receive detection data of the surface array detector, and the image reconstruction industrial personal computer is configured to be in communication connection with the data transmission industrial personal computer to receive the detection data of the surface array detector and reconstruct images. The application can reduce optical crosstalk and improve spatial resolution.
Description
Technical Field
The application relates to the technical field of CT imaging, in particular to a photon counting multi-energy spectrum CT imaging device and method.
Background
Existing CT detectors include semiconductor detectors and solid state scintillation detectors (i.e., integrating detectors). CT manufacturers currently in international mainstream have begun to lay out in the photon counting field based on semiconductor detectors. The existing photon counting X-ray detector is mainly based on semiconductor silicon, cadmium telluride, cadmium zinc telluride and the like, and although the photon counting detector has excellent X-ray detection performance, the problems of intolerance and polarization effect of high flux X-rays, complicated readout circuit, high price, environmental protection risk caused by cadmium metal and the like of the cadmium telluride and the cadmium zinc telluride detector limit the application of the photon counting X-ray detector greatly. The solid-state scintillation detector used in the CT system includes a scintillation crystal and a photoelectric conversion device, and the high-energy radiation is converted into a visible light signal by the scintillation crystal, and the visible light signal is further converted into a scintillation pulse signal by the photoelectric conversion device, and in this process, the imaging spatial resolution has an important influence on the final imaging quality, and the current imaging spatial resolution needs to be improved. Taking small animal photon counting multi-energy spectrum CT imaging as an example, the small animal CT needs to have a single photoelectric conversion device as small as possible to improve imaging spatial resolution, the scintillation crystal of the existing detector is coupled with the photoelectric conversion device one to one, and the single scintillation crystal needs to be light-shielded, namely, a layer of anti-reflection material for preventing light crosstalk is wrapped outside the single crystal. The single scintillation crystal cannot be cut to a required small enough size, and the overall size of a single pixel wrapped with the anti-reflection material is further increased, so that the size of the single pixel of the detector cannot be small, the imaging spatial resolution is affected, and the single scintillation crystal cannot be used for small animal micro CT imaging.
Disclosure of Invention
The present application is directed to a photon counting multi-energy spectrum CT imaging apparatus and method, which solves at least one of the above-mentioned problems.
The application provides a photon counting multi-energy spectrum CT imaging device which comprises a ray generating device, a surface array detector, a sheet-shaped micro-channel plate, a photomultiplier element, a data transmission industrial personal computer and an image reconstruction industrial personal computer, wherein the surface array detector comprises a sheet-shaped scintillation crystal which is configured to convert rays into visible light, the sheet-shaped micro-channel plate is coupled with the sheet-shaped scintillation crystal one to one and is configured to selectively pass the visible light converted by the sheet-shaped scintillation crystal, the photomultiplier element is coupled with the sheet-shaped micro-channel plate to convert the selected visible light into scintillation pulse signals, the data transmission industrial personal computer is configured to be in communication connection with the ray generating device and the surface array detector so as to control the ray generating device and receive detection data of the surface array detector, and the image reconstruction industrial personal computer is configured to be in communication connection with the data transmission industrial personal computer so as to receive the detection data of the surface array detector and reconstruct images.
According to one embodiment of the application, the thickness ratio of the sheet-shaped scintillation crystal to the sheet-shaped microchannel plate collimator is between 1:3 and 1:5.
According to one embodiment of the application, silicone grease is arranged between the sheet-shaped scintillation crystal and the sheet-shaped microchannel plate collimator, and silicone grease is arranged between the sheet-shaped microchannel plate collimator and the photomultiplier.
According to one embodiment of the application, the ratio of the thickness of the sheet-shaped microchannel plate collimator to the diameter of the microchannel is between 8:1 and 10:1.
According to one embodiment of the present application, the photon counting multi-energy spectrum CT imaging apparatus further comprises a multi-voltage threshold digital readout acquisition card configured to digitally acquire the scintillation pulse signal.
According to one embodiment of the application, the multi-voltage threshold digital readout acquisition card is configured to digitally acquire the scintillation pulse signal and acquire amplitude information of the scintillation pulse signal, and classify and count the scintillation pulse signal according to an energy interval corresponding to the amplitude information of the scintillation pulse signal.
According to one embodiment of the application, the multi-voltage threshold digital readout acquisition card is provided with a multi-voltage threshold digital readout circuit, the energy interval is preset according to the energy of photons in the multi-voltage threshold digital readout circuit, the multi-voltage threshold digital readout circuit comprises a plurality of digital readout channels, each readout channel comprises a plurality of comparators, the comparators are configured to preset a plurality of thresholds corresponding to the amplitude of a scintillation pulse signal, the threshold intervals correspond to different energy intervals, the amplitude information of the scintillation pulse signal is the threshold interval corresponding to the amplitude of the pulse signal, and a plurality of counting elements are in one-to-one correspondence with the comparators and are configured to count the scintillation pulse signal in a classification mode according to the energy interval corresponding to the amplitude information of the scintillation pulse signal.
According to one embodiment of the application, the comparator is a multi-voltage threshold digital readout acquisition card with a plurality of low voltage differential signal input ports LVDS.
According to one embodiment of the present application, the photon counting multi-energy spectrum CT imaging apparatus further comprises an image reconstruction module configured to reconstruct images of the digitized information acquired by the multi-voltage threshold digitized readout acquisition card.
According to one embodiment of the present application, the photon counting multi-energy spectrum CT imaging apparatus further comprises a replaceable power supply, wherein the replaceable power supply supplies power to the radiation generating apparatus, the area array detector, the data transmission industrial personal computer and the image reconstruction industrial personal computer.
According to one embodiment of the application, the replaceable power source is a modular battery pack.
According to one embodiment of the application, the photon counting multi-energy spectrum CT imaging device further comprises a rotating element, and the ray generating device, the area array detector, the replaceable power supply, the data transmission industrial personal computer and the image reconstruction industrial personal computer are uniformly distributed on the rotating element.
According to one embodiment of the application, the rotating element is provided with an opening through which the motion control bed is movable.
According to one embodiment of the present application, the photon counting multi-energy spectrum CT imaging apparatus further comprises a grating element configured to monitor a rotation angle signal of the rotating element and feed back to the data transmission industrial personal computer.
The photon counting multi-energy spectrum CT imaging method comprises the following steps of adopting an image reconstruction industrial personal computer to conduct rapid pre-scanning so as to adjust a motion control bed to a scanning position matched with a ray generating device, enabling the image reconstruction industrial personal computer to control the ray generating device to start through a data transmission industrial personal computer, adopting a surface array detector to count a ray energy division interval attenuated by a measured object so as to generate projection data, and enabling the data transmission industrial personal computer to receive the projection data and transmit the projection data to the image reconstruction industrial personal computer for image reconstruction.
According to one embodiment of the application, the method for counting the radiation energy-division intervals attenuated by the object to be measured by adopting the area array detector to generate projection data comprises the steps of detecting the radiation by adopting the area array detector to acquire a scintillation pulse signal, digitally acquiring the scintillation pulse signal by utilizing a multi-voltage threshold digital readout acquisition card and acquiring amplitude information of the scintillation pulse signal, and determining the corresponding energy intervals according to the amplitude information of the scintillation pulse signal to classify and count the scintillation pulse signal to generate the projection data.
According to one embodiment of the application, the multi-voltage threshold digital readout acquisition card is utilized to digitally acquire the scintillation pulse signals and acquire the amplitude information of the scintillation pulse signals, the corresponding energy interval is determined according to the amplitude information of the scintillation pulse signals so as to classify and count the scintillation pulse signals, and the multi-voltage threshold digital readout acquisition card is adopted to realize the multi-voltage threshold digital readout.
According to one embodiment of the application, the energy interval is preset according to the photon energy in a multi-voltage threshold digital readout circuit, the energy interval corresponds to the threshold interval, the multi-voltage threshold digital readout circuit comprises a plurality of digital readout channels, each readout channel comprises a plurality of comparators and counting elements corresponding to the comparators one by one, the plurality of comparators are adopted to preset a plurality of thresholds, the amplitude of the scintillation pulse signal is compared with the preset plurality of thresholds, the highest threshold reached by the scintillation pulse signal is obtained to determine the threshold interval corresponding to the amplitude of the scintillation pulse signal, the energy interval corresponding to the scintillation pulse signal is determined according to the threshold interval corresponding to the amplitude of the scintillation pulse signal, and the scintillation pulse signal is classified and counted according to the energy interval by adopting the plurality of counting elements.
According to one embodiment of the application, presetting a plurality of thresholds in the multi-voltage threshold digital readout acquisition card and comparing the amplitude of the scintillation pulse signal with the preset plurality of thresholds are realized by adopting a comparator of the multi-voltage threshold digital readout acquisition card.
According to one embodiment of the application, the multi-voltage threshold digitizing readout circuit comprises a plurality of digitizing readout channels, each readout channel comprising a plurality of the comparators.
According to one embodiment of the application, the replaceable power supply is used for supplying power to the image reconstruction industrial personal computer, the motion control bed, the ray generating device, the data transmission industrial personal computer and the photon counting detection device.
The photon counting multi-energy spectrum CT imaging device and the method provided by the application adopt the planar array detector comprising the sheet-shaped scintillation crystal, the sheet-shaped microchannel plate and the photomultiplier element array, so that the detector pixel is determined by the minimum size of the photomultiplier element, at the moment, a single photomultiplier element can be made to have a required small size, the resolution is improved, the sheet-shaped microchannel plate selects visible light converted by the scintillation crystal, and the visible light with a certain angle enters the photomultiplier element through the microchannel to reduce the optical crosstalk, so that the outside of the scintillation crystal does not need to be wrapped with anti-reflection materials, and the detection area of the scintillation crystal can be effectively utilized.
Drawings
Embodiments of the present disclosure are described in detail below with reference to the accompanying drawings. The accompanying drawings, which are incorporated in and constitute a part of this disclosure, are included to provide a further understanding of the disclosure. The exemplary embodiments of the present disclosure and their description are for the purpose of explaining the present disclosure and are not to be construed as unduly limiting the present disclosure. In the accompanying drawings:
FIG. 1 shows a schematic diagram of the structure of a detector of a photon counting multi-energy spectrum CT imaging device according to an example embodiment of the application;
FIG. 2 shows another schematic structural diagram of a photon counting multi-energy spectrum CT imaging device, according to an example embodiment of the application;
FIG. 3 illustrates a front view of a photon counting multi-energy spectrum CT imaging device, according to an exemplary embodiment of the present application;
Fig. 4 shows a left side view of a photon counting multi-energy spectrum CT imaging device according to an example embodiment of the application.
Detailed Description
Hereinafter, only certain exemplary embodiments are briefly described. As will be recognized by those of skill in the pertinent art, the described embodiments may be modified in various different ways without departing from the spirit or scope of the present invention. Accordingly, the drawings and description are to be regarded as illustrative in nature and not as restrictive.
In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings are merely for convenience in describing the present invention and simplifying the description, and do not indicate or imply that the devices or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present invention. Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more of the described features. In the description of the present invention, the meaning of "a plurality" is two or more, unless explicitly defined otherwise.
In the description of the present invention, unless explicitly specified and limited otherwise, the terms "mounted," "connected," and "connected" are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected, mechanically connected, electrically connected, or communicable with each other, directly connected, indirectly connected via an intermediary, or in communication between two elements or in an interaction relationship between two elements. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art according to the specific circumstances.
In the present invention, unless expressly stated or limited otherwise, a first feature "above" or "below" a second feature may include both the first and second features being in direct contact, as well as the first and second features not being in direct contact but being in contact with each other through additional features therebetween. Moreover, a first feature being "above," "over" and "on" a second feature includes the first feature being directly above and obliquely above the second feature, or simply indicating that the first feature is higher in level than the second feature. The first feature being "under", "below" and "beneath" the second feature includes the first feature being directly above and obliquely above the second feature, or simply indicating that the first feature is less level than the second feature.
The following disclosure provides many different embodiments, or examples, for implementing different features of the invention. In order to simplify the present disclosure, components and arrangements of specific examples are described below. They are, of course, merely examples and are not intended to limit the invention. Furthermore, the present invention may repeat reference numerals and/or letters in the various examples, which are for the purpose of brevity and clarity, and which do not themselves indicate the relationship between the various embodiments and/or arrangements discussed. In addition, the present invention provides examples of various specific processes and materials, but one of ordinary skill in the art will recognize the application of other processes and/or the use of other materials.
The preferred embodiments of the present application will be described below with reference to the accompanying drawings, it being understood that the preferred embodiments described herein are for illustration and explanation of the present application only, and are not intended to limit the present application.
As shown in fig. 1, the disclosed photon counting multi-spectral CT imaging apparatus has a planar array detector 100 according to an exemplary embodiment of the present application, the planar array detector 100 including a sheet-shaped scintillator crystal 110 configured to convert rays including X-rays, gamma-rays, and high-energy rays such as neutron rays, proton rays, beta-rays, and the like into visible light, a sheet-shaped microchannel plate 120 coupled one-to-one with the sheet-shaped scintillator crystal 110 configured to selectively pass the visible light converted by the sheet-shaped scintillator crystal 110, and a photomultiplier element 130 coupled with the sheet-shaped microchannel plate 120 in an array of photomultiplier elements 130 to convert the selected visible light into scintillation pulse signals, wherein the sheet-shaped microchannel plate 120 selects visible light at an angle to be incident to the photomultiplier element 130 through its microchannels to reduce optical crosstalk.
The detector 100 in the application adopts a planar array detector with the flaky (or planar) scintillation crystal 110, the flaky microchannel plate 120 and the array of the photomultiplier elements 130 coupled, so that the detector pixels are determined by the minimum size of the photomultiplier elements 130, the single photomultiplier elements 130 can be processed to the required small size at the moment, the resolution is improved, and the visible light converted by X-photons is selected by the flaky microchannel plate 120 to be incident on the photomultiplier elements 130 through the microchannels thereof at a certain angle so as to reduce the light crosstalk, so that the outside of the scintillation crystal does not need to wrap an anti-reflection material, and the detection area of the scintillation crystal can be effectively utilized. The application reduces optical crosstalk by adding the sheet microchannel plate 120 between the sheet (or planar) scintillation crystal 110 and the photomultiplier 130 to filter out visible light photons incident into the photomultiplier at a large oblique angle, i.e., selecting visible light photons in a certain angle direction to enter the photomultiplier through the microchannel.
In one embodiment, the photomultiplier elements 130 of the area array detector are silicon photomultipliers (i.e., sipms). The sheet (planar) scintillator crystal 110 is coupled one-to-one with the sheet (planar) microchannel plate 120 and with the SiPM array to form a scintillator crystal/microchannel plate/SiPM planar array detector, the pixels of which are determined by the SiPM minimum size. The size of a single SiPM can be reduced to 200 mu m or even smaller, and CT imaging with higher resolution of small animal CT can be realized by adopting a detector with smaller pixel size and different adjustable magnification ratios. Meanwhile, because the SiPM photon chip is used, the method has certain advantages in the aspects of sensitivity, gain and dynamic range, can detect lower light intensity, even count single photons, and is particularly suitable for low-dose and ultra-low-dose CT imaging.
In a preferred embodiment, the scintillation crystal 110 of the face array detector of the present application employs lutetium yttrium silicate crystals with low background radiation, but is not limited thereto. The use of the scintillation crystal 110 in place of the semiconductor overcomes the intolerance of photon counting detector photosensitive elements based on semiconductor materials to high flux X-rays.
In an embodiment, the thickness ratio of the sheet-shaped scintillation crystal 110 to the sheet-shaped microchannel plate 120 along the radiation direction is between 1:3 and 1:5, so as to improve the effect of reducing the optical crosstalk. In a preferred embodiment, the ratio of the thickness of the plate-shaped microchannel plate 120 to the diameter of the microchannels is between 8:1 and 10:1, so that the effect of reducing optical crosstalk can be further improved. Further, the visible light is selected to be incident to the photomultiplier through the micro-channel of the sheet-shaped micro-channel plate at an angle of 0-30 degrees to reduce optical crosstalk.
In an embodiment, silicone grease is disposed between the sheet-shaped scintillation crystal 110 and the sheet-shaped microchannel plate 120, and silicone grease is disposed between the sheet-shaped microchannel plate 120 and the photomultiplier 130, so that visible light is better incident on the silicon photomultiplier.
In an embodiment, the detector 100 may further comprise a multi-voltage threshold (MVT) digital readout acquisition card configured to digitally acquire the scintillation pulse signal. The digital readout is realized by adopting the multi-voltage threshold digital readout acquisition card, so that the position, energy and time information of a single event can be accurately extracted, the high-precision restoration of signals is completed, and the accurate acquisition of the data of the multi-energy spectrum CT is realized.
In an embodiment, the photon counting multi-energy spectrum CT imaging device of the present application may further include an image reconstruction module configured to reconstruct images of the digitized information acquired by the multi-voltage threshold digitized readout acquisition card. The structural design of the image reconstruction module may adopt the prior art, and will not be described herein.
In an embodiment, the photon counting multi-energy spectrum CT imaging device of the present application may further comprise a radiation generating device configured to emit radiation to the detecting device, which may include X-rays, gamma rays, neutron rays, proton rays, beta rays, etc.
As shown in fig. 2, a photon counting multi-energy spectrum CT imaging device according to another embodiment of the present application has a detector 200, the detector 200 has at least one energy interval divided according to photon energy, and a multi-voltage threshold digital readout acquisition card 210 in the detector 200 is configured to digitally acquire a scintillation pulse signal and acquire amplitude information of the scintillation pulse signal, and the scintillation pulse signal is classified and counted according to the energy interval corresponding to the amplitude information of the scintillation pulse signal.
In one embodiment, the multi-voltage threshold digital readout acquisition card 210 is equipped with a multi-voltage threshold (MVT) digital readout circuit, wherein the energy interval is preset according to the energy of the photons in the multi-voltage threshold digital readout circuit, and each readout channel comprises a plurality of digital readout channels, a plurality of comparators, a plurality of counting elements and a plurality of counting elements, wherein the plurality of comparators are configured to preset a plurality of thresholds corresponding to the amplitude of the scintillation pulse signal, the threshold intervals are formed between two adjacent thresholds, the threshold intervals correspond to different energy intervals, the amplitude information of the scintillation pulse signal is the threshold interval corresponding to the amplitude of the pulse signal, and the plurality of counting elements are in one-to-one correspondence with the plurality of comparators and are configured to count the scintillation pulse signal in a classification mode according to the energy interval corresponding to the amplitude information of the scintillation pulse signal.
The radiation photons reaching the photon counting detection means are recorded in pulses by means of a dedicated digital readout circuit MVT provided with a multi-voltage threshold digital readout acquisition card 210, the amplitude of the recorded pulses being related to the photon energy and the photon counts of different energies being added to the corresponding energy segments. The amplitude of the pulse corresponds to the energy of the radiation photon and the number of pulses corresponds to the number of photons. By setting a plurality of electronic system thresholds corresponding to the amplitude of the scintillation pulse signal, the pulse with lower energy can be filtered, and the influence of low-energy noise on an imaging result is eliminated. And meanwhile, pulse signals with different amplitude heights are screened, energy information of the pulse signals is identified and accumulated corresponding to different energy regions, and wider energy spectrum distribution is counted according to the set energy regions to obtain imaging information of different energy regions. Meanwhile, the special multi-voltage threshold digital readout acquisition card 120 can realize multi-channel measurement, so that the use of a large number of ADCs is avoided, and the cost of the photon counting detection device is greatly reduced.
In one embodiment, the comparator is a multi-voltage threshold digital readout capture card 210 chip with a plurality of low voltage differential signal input ports LVDS.
In view of the fact that a solid state scintillation detector, namely an integral detector, which is commonly used in the current CT system is adopted, total deposition energy of X-rays is obtained through charge integration for a certain time, the result reflects average attenuation characteristics of the X-rays, energy information of the X-rays is lost, and the greatest problem of the energy integral detector is that dark current exists, so that the signal to noise ratio of images is deteriorated under the condition of low dosage. Therefore, the application adopts a photon counting detector, can divide the energy of photons into one or more energy intervals, counts the photons in each detected energy interval to realize multi-energy spectrum CT imaging, can eliminate electronic noise caused by dark current by setting a proper threshold value, is beneficial to reducing radiation dose, obtains higher signal-to-noise ratio and realizes low-dose CT imaging, and simultaneously adopts a special multi-voltage threshold value digital readout acquisition card to realize simultaneous measurement of a plurality of energy channels.
An embodiment of the application provides a photon counting detection system, which comprises a photon counting detection device, a data transmission industrial personal computer and an image reconstruction industrial personal computer, wherein the data transmission industrial personal computer is configured to be in communication connection with the photon counting detection device to receive detection data of a detector, and the image reconstruction industrial personal computer is configured to be in communication connection with the data transmission industrial personal computer to receive the detection data and reconstruct an image. The data transmission industrial personal computer can adopt a computer, a singlechip, an ARM (ARM) (Acorn RISCMachine) or an FPGA (Field-Programmable gate array) and the like, is connected with the photon counting detection device in a CAMERA LINK mode to receive projection data detected by the photon counting detection device, is used as an upper computer, is in wireless interconnection with the data transmission industrial personal computer, and can control and store data and perform image processing on the whole system. In one embodiment, the image reconstruction industrial personal computer is a computer, preferably an industrial computer with superior performance.
As shown in fig. 3, an embodiment of the present application provides a small photon counting multi-energy spectrum CT imaging device, including:
The system comprises a ray generation device 400, a detector 200, a data transmission industrial personal computer 600 and an image reconstruction industrial personal computer 700, wherein the data transmission industrial personal computer 600 is configured to be in communication connection with the ray generation device 400 and the detector 200 so as to control the ray generation device 400 and receive detection data of the detector 200, and the image reconstruction industrial personal computer 700 is configured to be in communication connection with the data transmission industrial personal computer 600 so as to receive the detection data of the detector 200 for image reconstruction. The specific designs of the data transmission industrial personal computer 600 and the image reconstruction industrial personal computer 700 may refer to a photon counting detection system, and will not be described herein.
As shown in fig. 3, the animal photon counting multi-energy spectrum CT imaging system 10000 provided by the present application further comprises a motion control bed 500, a radiation generating device 400, a detector 200, a data transmission industrial personal computer 600 configured to be in communication connection with the radiation generating device 400 and the detector 200 so as to control the radiation generating device 400 and receive projection data of the detector 200, and an image reconstruction industrial personal computer 700 configured to be in communication connection with the data transmission industrial personal computer 600 so as to receive projection data of the detector 200 and perform image reconstruction. The multi-row-surface array photon counting detection device formed by the scintillation crystal/micro-channel plate/SiPM detector unit of the detector 200 and the multi-voltage threshold digital readout acquisition card detects the rays transmitted through an object to be detected (small animal), counts the rays with different energies, and realizes photon counting multi-energy spectrum CT imaging of the small animal.
In the embodiment of the present application, the radiation generating device 400 is used to emit radiation to the detector 200, and in the preferred embodiment, an X-ray tube is used as the radiation generating device, which has a heavy weight and requires a large power. The radiation is attenuated by the object (animal) to be measured, reaches the photon counting detection device, and is detected by the detector 200 to generate projection data.
In one embodiment, the data transmission industrial personal computer 600 and the image reconstruction industrial personal computer 700 are all industrial personal computers with wireless transmission. The weight of the data transmission industrial personal computer 600 and the image reconstruction industrial personal computer 700 is lighter than that of the X-ray tube.
The data transmission industrial personal computer 600 sends a corresponding control signal to the ray generation device 400 to control the ray to be turned on, and the projection data generated by the detection of the detector 200 after the ray is attenuated by the object to be detected (small animal) is transmitted to the data transmission industrial personal computer.
The image reconstruction industrial personal computer 700 is installed on a CT support, has an operation interface of a CT imaging system, and is preset with a scanning protocol. By adjusting the software in the operation interface of the CT imaging system, the rapid pre-scanning of the tested object, such as a small animal, can be controlled. The image reconstruction industrial personal computer arranged on the CT bracket is used as an upper computer, is in wireless interconnection with the data transmission industrial personal computer, and can control the whole system, store data and process images. The data transmission industrial personal computer transmits data to an image reconstruction industrial personal computer arranged on the CT bracket, and after scanning is completed, the image reconstruction industrial personal computer reconstructs the received projection data, carries out post-processing and visualizes.
In one embodiment, the animal photon counting multi-spectral CT imaging system 10000 further comprises a replaceable power supply 1200, and the replaceable power supply 1200 is used to power the system.
In one embodiment of the present application, the replaceable power supply 1200 employed is a modular battery pack. The storage battery is a custom capacity storage battery, has different voltage and current outputs, meets different power supply demands such as a ray generation device, a photon counting detector, an industrial personal computer with wireless transmission and the like, can be combined by adopting storage batteries with different specifications according to the power consumption demands of different equipment, can enable the equipment to be integrally and reasonably balanced, can also conveniently and timely supply electric quantity, improves the scanning efficiency, and can ensure the CT scanning power supply demands of a certain quantity by adopting modularized combined storage batteries. The modularized combined storage battery comprises a storage battery for supplying power to the ray generation device, a storage battery for supplying power to the photon counting detection device, a storage battery for supplying power to the data transmission industrial personal computer, an image reconstruction industrial personal computer and the like, and further comprises standby storage batteries of different specifications, wherein the electric quantity of each storage battery is related to the parts supplied with power, in one example, the power required by the ray generation device is the largest, the power required by the industrial personal computer is the smallest, the corresponding equipped storage batteries have different capacities, the storage battery for supplying power to the ray generation device has the largest and the heaviest capacity, the storage battery for supplying power to the industrial personal computer has the smallest capacity and the weight is the lightest.
In one embodiment, the replaceable power supply 1200 is equipped with a battery level detection system. The battery electric quantity detection system is used for monitoring electric quantity in real time and is in communication connection with the data transmission industrial personal computer, and real-time electric quantity information is transmitted to the data transmission industrial personal computer. The CT scanning required electric quantity is preset in the battery electric quantity detection system, the electric quantity is monitored in real time in the scanning process, when the fact that the current power supply battery electric quantity is insufficient to support the completion of the scanning work is monitored in the ongoing scanning process, the current power shortage is automatically calculated, an auxiliary battery with the proper electric quantity matched with the power shortage is automatically selected from the modularized battery combination, power is continuously supplied to the completion of the scanning, and the scanning efficiency is improved by timely selecting the proper standby storage battery to supply the electric quantity. In another embodiment, the battery may be charged when the amount of power is insufficient for one CT scan.
In one embodiment, animal photon counting multi-spectral CT imaging system 10000 further comprises a rotating element 300. The data transmission industrial personal computer 600 has a motion controller therein to control the rotary member 300. In the preferred embodiment, the rotating element 300 is a moving turntable, but is not limited thereto. In one embodiment, the motion turntable is driven to rotate by a direct-drive servo motor, and the rear end of the motion turntable is connected with the direct-drive servo motor 1000 through a hollow slewing bearing terminal. The motion turntable is used for fixing devices such as a ray generating device, a photon counting detection device, a modularized combined storage battery, a data transmission industrial personal computer 600 and the like. The data transmission industrial personal computer 600 is installed on the motion turntable, the motion controller in the data transmission industrial personal computer is used for controlling the motion turntable, and the control of components on the motion turntable is realized through the data transmission industrial personal computer 600, including the motion control of the motion control bed 500, the acquisition control of the detector 200, the storage and transmission of projection data, and the real-time monitoring of the battery power of the replaceable power supply 1200.
Based on the heaviest ray generating device 400 and the lightest detector 200 of the data transmission industrial personal computer 600 times with wireless transmission, the ray generating device 400, the detector 200, the replaceable power supply 1200 and the data transmission industrial personal computer 600 are distributed on the rotating element 300 in a polygonal shape so as to ensure the stability of the rotation center of gravity of the whole movement turntable. The motion turntable controls the ray generating device and the photon counting detection device to integrally rotate relative to the measured object so as to acquire projection data of the measured object under different angles.
In one embodiment, the animal photon counting multi-spectral CT imaging system 10000 further comprises a grating element 1100, wherein the grating element 1100 is disposed on the rotating element and configured to monitor and feed back the rotation angle signal of the rotating element 300 to the data transmission industrial personal computer 600. In particular embodiments, grating elements 1100 include, but are not limited to, grating scales. The grating ruler is arranged on the motion turntable and used for obtaining the accurate rotating position of the motion turntable during CT imaging. The grating ruler, the ray generating device 400, the detector 200, the replaceable power supply 1200, the data transmission industrial personal computer 600 and the like are arranged in a polygonal shape. The rotation angle signal of the motion turntable is fed back to the data transmission industrial personal computer through the grating ruler, so that the detector 200 can record the projection of each angle. After the whole 360-degree scanning is completed, the image reconstruction industrial personal computer 700 will receive the projection data of the full angle and reconstruct, post-process and visualize. The replaceable power supply 1200 also includes a battery that powers the grating ruler.
According to the embodiment of the application, the storage battery supplies power for all equipment such as the ray generating device, the photon counting detection device, the replaceable power supply, the data transmission industrial personal computer, the grating element and the like which are arranged on the movement turntable in a polygonal mode, and can be charged, disassembled and replaced, and the storage battery is a storage battery with customized capacity and has different voltage and current outputs, so that different power supply requirements of the ray generating device, the photon counting detector and the industrial personal computer with wireless transmission are met. According to the embodiment of the application, the storage battery is used for replacing the slip ring for supplying power, a certain number of CT scanning power supply requirements can be ensured, and the power supply is provided with the battery power detection system, so that the power can be monitored in real time by interacting information with the industrial personal computer with wireless transmission. The electric quantity is insufficient for CT scanning, and the other group of matched batteries which are charged are replaced or the charging is waited.
In one embodiment, the rotating element 300 is provided with an opening 310, and preferably, the opening 310 is disposed at the center of the rotating element 300, and when the rotating disc is used as the rotating element, the opening 310 is disposed at the center of the rotating disc. The aperture 310 has a larger aperture than the object to be measured (small animal) and the maximum effective field of view for detection, and is equipped with a position calibration fixture for laser calibration. The rear end of the motion turntable is connected with the direct-drive servo motor 1000 through a hollow slewing bearing terminal.
In one embodiment, the motion control bed 500 performs positioning and precession when the object (small animal) is measured, and the motion control bed 500 is driven by the back and forth motion servo motor 900 and the up and down motion servo motor 800 to perform back and forth and up and down motions.
The motion control bed 500 may be moved through the aperture 310 in the center of the motion carousel. The aperture 310 of the motion turret is larger than the object to be tested (small animal) and the maximum effective detection field of view diameter, and the motion turret is equipped with a position calibration tooling for laser calibration of the motion control bed. According to one embodiment of the invention, the motion control bed determines the origin of coordinates of the correction coordinates according to laser collimation, one laser beam is arranged in the center of the ray generation device and irradiates the center of the detector, and the other laser beam irradiates the center of the motion turntable. And adjusting the initial position of the motion control bed according to the pre-scanned image so as to determine the primary irradiation range of cone beam CT and the initial position of spiral CT.
According to one embodiment of the present invention, the CT system uses a lead plate as a shield case, while a door for replacing the object to be measured is also a lead plate as a shield case. When the object door is not closed, the ray generating device cannot be started. In addition, the CT system is designed with a double-path emergency stop light for controlling the ray generating device, the direct-drive servo motor, the front-back motion servo motor and the servo motor controller of the up-down motion servo motor to simultaneously and emergently stop working.
The working flow of the small animal photon counting multi-energy spectrum CT imaging system of the embodiment of the application is as follows:
A cone beam small animal photon counting multi-energy spectrum CT imaging operation control flow for local high resolution scanning of small animal critical tissue comprises fixing small animal to be detected on a motion control bed 500 after anesthesia, closing a lead shielding door of a detected object, opening an operation interface of a CT imaging system in an image reconstruction industrial personal computer 700 with wireless transmission installed on a CT bracket, carrying out rapid pre-scanning to determine whether the position of the detected object (small animal) is proper or not, if not, adjusting by software in the operation interface of the CT imaging system until the position is reached, selecting a scanning protocol, sending a scanning instruction to a data transmission industrial personal computer 600 installed on the motion turntable by wireless transmission, controlling the motion turntable by the motion controller in the data transmission industrial personal computer 600, sending a corresponding control signal to a ray generating device 400 by the data transmission industrial personal computer 600, after the ray is started, reaching a detector 200 after the attenuation of the detected object, generating projection data after the detection by the detector 200, feeding back a rotation angle signal of the motion turntable to the data transmission industrial personal computer 600 by a grating ruler, and recording the projection of each angle by the detector 200. The data transmission industrial personal computer 600 installed on the motion turntable transmits data to the image reconstruction industrial personal computer 700 installed on the CT bracket, and after the whole 360-degree scanning is completed, the image reconstruction industrial personal computer installed on the CT bracket receives all-angle projection data, performs reconstruction, post-processing and visualization, and finally displays the projection data in an image reconstruction industrial personal computer interface.
In the embodiment of the application, the whole body scanning of the small animal is realized by switching to a spiral scanning mode by spiral CT. And (3) running a control flow:
The method comprises the steps of fixing a small animal to be detected on a motion control bed after anesthesia, closing a lead shielding door of the detected object, opening an operation interface of a CT imaging system in an image reconstruction industrial personal computer 700 with wireless transmission arranged on a CT bracket, carrying out quick pre-scanning, determining whether an initial measurement position of the detected object (small animal) is proper or not, adjusting by software in the operation interface of the CT imaging system until the initial measurement position reaches the proper position, selecting a scanning protocol, controlling the motion control bed 500 by a scanning instruction, simultaneously controlling the motion turntable by the data transmission industrial personal computer 600 through wireless transmission, controlling the motion turntable by the motion controller in the data transmission industrial personal computer 600, sending corresponding control signals to a ray generating device 400 by the data transmission industrial personal computer 600, generating projection data after the rays are started and attenuated by the detected object to reach a detector 200, and recording projections of each angle by the detector 200 by feeding back a rotation angle signal of the motion turntable to the data transmission industrial personal computer 600 through a grating ruler. The data transmission industrial personal computer 600 installed on the motion turntable transmits data to the image reconstruction industrial personal computer 700 installed on the CT bracket, when the whole 360-degree scanning is completed, the image reconstruction industrial personal computer 700 installed on the CT bracket reconstructs the projection data at all angles, performs post-processing and visualization, and finally displays the projection data in the interface of the image reconstruction industrial personal computer 700.
Cone-beam CT for small animals is currently widely used, and cone-beam CT generally uses flat panel detectors. The existing detector array of the detecting device for the small animal photon counting multi-energy spectrum CT imaging system cannot be large in size (only one row or a few rows), so that the application of cone beam CT is limited to a certain extent. The application adopts a multi-row surface array detector, can meet the requirements of cone beam CT imaging, and realizes local high-resolution scanning of some key tissues of small animals. And whole body scanning of the small animals is completed by switching spiral scanning modes. Therefore, the application can meet various requirements and use environments of multi-energy spectrum CT imaging by adopting a multi-row area array detector and a switchable cone beam and spiral scanning scheme.
The application also provides a small photon counting multi-energy spectrum CT imaging method, which comprises the following steps:
the image reconstruction industrial personal computer is adopted to perform rapid pre-scanning so as to adjust the motion control bed to a scanning position matched with the ray generation device;
the image reconstruction industrial personal computer controls the ray generation device to start through the data transmission industrial personal computer;
the detector of the embodiment of the application is adopted to count the ray energy-dividing intervals after the attenuation of the measured object so as to generate projection data;
and the data transmission industrial personal computer receives the projection data and transmits the projection data to the image reconstruction industrial personal computer for image reconstruction.
In one embodiment, the replaceable power supply is used for supplying power to the image reconstruction industrial personal computer, the motion control bed, the ray generating device, the data transmission industrial personal computer and the photon counting detection device. In a preferred embodiment, the replaceable power source is a modular battery pack.
In one embodiment, counting the energy-division intervals of the radiation attenuated by the object using a photon counting detector to generate projection data comprises:
the detector provided by the embodiment of the application is adopted to detect the ray so as to obtain a scintillation pulse signal;
And digitally acquiring the scintillation pulse signals by using a multi-voltage threshold digital readout acquisition card, acquiring amplitude information of the scintillation pulse signals, and determining a corresponding energy interval according to the amplitude information of the scintillation pulse signals so as to classify and count the scintillation pulse signals to generate projection data.
In an embodiment, the multi-voltage threshold digital readout acquisition card is used for digitally acquiring the scintillation pulse signals and acquiring amplitude information of the scintillation pulse signals, and corresponding energy intervals are determined according to the amplitude information of the scintillation pulse signals so as to classify and count the scintillation pulse signals, and the multi-voltage threshold digital readout acquisition card is used for realizing the multi-voltage threshold digital readout circuit.
In the embodiment of the application, the step of digitally acquiring the scintillation pulse signal by using the multi-voltage threshold digital readout acquisition card and acquiring the amplitude information of the scintillation pulse signal comprises the steps of presetting a plurality of thresholds in the multi-voltage threshold digital readout acquisition card, comparing the amplitude of the scintillation pulse signal with the preset plurality of thresholds, and acquiring the highest threshold reached by the scintillation pulse signal to determine a threshold interval corresponding to the amplitude of the scintillation pulse signal.
In an embodiment, the presetting of the plurality of thresholds in the multi-voltage threshold digital readout acquisition card is implemented using a comparator of the multi-voltage threshold digital readout acquisition card. Specifically, a multi-voltage threshold digital readout circuit is configured in the multi-voltage threshold digital readout acquisition card, and the multi-voltage threshold digital readout circuit comprises a plurality of digital readout channels, and each readout channel comprises a plurality of comparators. In a preferred embodiment, the comparator is a multi-voltage threshold digital readout acquisition card chip with multiple low voltage differential signal input ports LVDS.
In an embodiment, a threshold interval is formed between two adjacent thresholds, and the amplitude information of the scintillation pulse signal is the threshold interval corresponding to the amplitude of the pulse signal.
In one embodiment, comparing the amplitude of the scintillation pulse signal with a plurality of preset thresholds is implemented by using a comparator of a multi-voltage threshold digital readout acquisition card. The comparator is a plurality of low voltage differential signal input ports LVDS of a chip of the multi-voltage threshold digital readout acquisition card.
In an embodiment, an energy interval is preset in the multi-voltage threshold digital readout acquisition card according to the energy of the photon, and the energy interval corresponds to the threshold interval.
In one embodiment, the step of determining the corresponding energy interval according to the amplitude information to classify and count the scintillation pulse signals includes determining the energy interval corresponding to the scintillation pulse signals according to the threshold interval corresponding to the amplitude of the scintillation pulse signals, and classifying and counting the scintillation pulse signals according to the energy interval.
In a preferred embodiment, the classified counting of the scintillation pulse signals by energy intervals is implemented using a counting element.
In one embodiment, each read channel of the multi-voltage threshold digitizing read circuit includes a plurality of counting elements.
In another embodiment of the present application, the step of digitally collecting the scintillation pulse signal by using the multi-voltage threshold digital readout collection card and obtaining the amplitude information of the scintillation pulse signal, determining the corresponding energy interval according to the amplitude information of the scintillation pulse signal to classify and count the scintillation pulse signal is implemented by using a multi-voltage threshold digital readout circuit configured therein.
In a preferred embodiment, an energy interval is preset in the multi-voltage threshold digital readout acquisition card according to photon energy, the energy interval corresponds to the threshold interval, the multi-voltage threshold digital readout acquisition card comprises a plurality of digital readout channels, each readout channel comprises a plurality of comparators and counting elements corresponding to the comparators one by one, the plurality of comparators are adopted to preset the plurality of thresholds, the amplitude of a scintillation pulse signal is compared with the preset plurality of thresholds, the highest threshold reached by the scintillation pulse signal is obtained, so that the threshold interval corresponding to the amplitude of the scintillation pulse signal is determined, the energy interval corresponding to the scintillation pulse signal is determined according to the threshold interval corresponding to the amplitude of the scintillation pulse signal, and the scintillation pulse signal is counted according to the energy interval classification by adopting the plurality of counting elements.
The apparatus described in the embodiments of the present application may incorporate the method features described in the embodiments of the present application and vice versa.
Various embodiments are described herein, but the description of the various embodiments is not exhaustive and the same or similar features or portions between the various embodiments may be omitted for the sake of brevity. Herein, "one embodiment," "some embodiments," "example," "specific example," or "some examples" means that it is applicable to at least one embodiment or example, but not all embodiments, according to the present application. The above terms are not necessarily meant to refer to the same embodiment or example. Those skilled in the art may combine and combine the features of the different embodiments or examples described in this specification and of the different embodiments or examples without contradiction.
Finally, it should be noted that the foregoing description is merely exemplary embodiments of the disclosure, and not intended to limit the disclosure, and although the disclosure has been described in detail with reference to the foregoing embodiments, it will be apparent to those skilled in the art that modifications may be made to the technical solutions described in the foregoing embodiments, or equivalents may be substituted for some of the technical features thereof. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present disclosure should be included in the protection scope of the present disclosure.
Claims (21)
1. A photon counting multi-energy spectrum CT imaging apparatus, comprising:
A radiation generating device;
A planar array detector including a sheet-shaped scintillator crystal configured to convert rays into visible light, a sheet-shaped microchannel plate coupled one-to-one with the sheet-shaped scintillator crystal and configured to selectively pass the visible light converted by the sheet-shaped scintillator crystal, a photomultiplier coupled with the sheet-shaped microchannel plate to convert the selected visible light into a scintillation pulse signal, a detector including a photodetector coupled with the sheet-shaped microchannel plate and configured to convert the visible light into a scintillation pulse signal;
The data transmission industrial personal computer is configured to be in communication connection with the ray generation device and the area array detector so as to control the ray generation device and receive detection data of the area array detector;
The image reconstruction industrial personal computer is configured to be in communication connection with the data transmission industrial personal computer so as to receive detection data of the area array detector and reconstruct an image.
2. The photon counting multi-energy spectrum CT imaging device of claim 1, wherein the thickness ratio of the sheet scintillation crystal to the sheet microchannel plate collimator is between 1:3-1:5.
3. The photon counting multi-energy spectrum CT imaging device of claim 1, wherein the ratio of the thickness of the sheet microchannel plate collimator to the diameter of the microchannel is between 8:1 and 10:1.
4. The photon counting multi-energy spectrum CT imaging device of claim 1, wherein silicone grease is disposed between the sheet-like scintillation crystal and the sheet-like microchannel plate collimator, and silicone grease is disposed between the sheet-like microchannel plate collimator and the photomultiplier element.
5. The photon counting multi-energy spectrum CT imaging device of claim 1, further comprising a multi-voltage threshold digital readout acquisition card configured to digitally acquire the scintillation pulse signal.
6. The photon counting multi-energy spectrum CT imaging device of claim 5, wherein the multi-voltage threshold digital readout acquisition card is configured to digitally acquire a scintillation pulse signal and obtain amplitude information of the scintillation pulse signal, and to classify and count the scintillation pulse signal according to an energy interval corresponding to the amplitude information of the scintillation pulse signal.
7. The photon counting multi-energy spectrum CT imaging device of claim 6, wherein the multi-voltage threshold digital readout acquisition card is equipped with a multi-voltage threshold digital readout circuit within which the energy interval is preset according to the energy of the photons, the multi-voltage threshold digital readout circuit comprising a plurality of digital readout channels, each readout channel comprising:
the device comprises a plurality of comparators, a plurality of pulse signal detection circuit and a plurality of pulse signal detection circuit, wherein the comparators are configured to preset a plurality of thresholds corresponding to the amplitude of the pulse signal, and threshold intervals are formed between two adjacent thresholds, and the threshold intervals correspond to different energy intervals;
and the counting elements are in one-to-one correspondence with the comparators and are configured to count the scintillation pulse signals in a classifying manner according to the energy intervals corresponding to the amplitude information of the scintillation pulse signals.
8. The photon counting multi-energy spectrum CT imaging device of claim 7, wherein the comparator is a plurality of low voltage differential signal input ports LVDS of a multi-voltage threshold digital readout acquisition card.
9. The photon counting multi-energy spectrum CT imaging device of claim 5, further comprising an image reconstruction module configured to reconstruct images of digitized information acquired by the multi-voltage threshold digitized readout acquisition card.
10. The photon counting multi-energy spectrum CT imaging modality of claim 1, further comprising a replaceable power source that powers the radiation generating means, the area array detector, the data transmission industrial personal computer, and the image reconstruction industrial personal computer.
11. The photon counting multi-energy spectrum CT imaging device of claim 10, wherein the replaceable power source is a modular battery pack.
12. The photon counting multi-energy spectrum CT imaging modality of claim 10, further comprising a rotating element, wherein the radiation generating means, the area array detector, the interchangeable power supply, the data transmission industrial personal computer, and the image reconstruction industrial personal computer are uniformly arranged on the rotating element.
13. The photon counting multi-energy spectrum CT imaging device of claim 12, wherein the rotating member is provided with an aperture through which the motion control bed is movable.
14. The photon counting multi-energy spectrum CT imaging device of claim 12, further comprising a grating element configured to monitor the rotational angle signal of the rotating element and feed back to a data transmission industrial personal computer.
15. A photon counting multi-spectral CT imaging method according to claim 1, comprising the steps of:
the image reconstruction industrial personal computer is adopted to perform rapid pre-scanning so as to adjust the motion control bed to a scanning position matched with the ray generation device;
the image reconstruction industrial personal computer controls the ray generation device to start through the data transmission industrial personal computer;
Counting the ray energy-division intervals attenuated by the measured object by adopting a plane array detector to generate projection data;
and the data transmission industrial personal computer receives the projection data and transmits the projection data to the image reconstruction industrial personal computer for image reconstruction.
16. The photon counting multi-energy spectrum CT imaging method of claim 15, wherein counting the energy bins of the radiation attenuated by the object using the area array detector to generate projection data comprises:
detecting the rays by adopting the area array detector to obtain a scintillation pulse signal;
And digitally acquiring the scintillation pulse signals by using a multi-voltage threshold digital readout acquisition card, acquiring amplitude information of the scintillation pulse signals, and determining a corresponding energy interval according to the amplitude information of the scintillation pulse signals so as to classify and count the scintillation pulse signals to generate projection data.
17. The photon counting multi-spectral CT imaging method according to claim 16, wherein,
The method comprises the steps of digitally collecting the scintillation pulse signals by using a multi-voltage threshold digital reading collecting card, acquiring amplitude information of the scintillation pulse signals, determining corresponding energy intervals according to the amplitude information of the scintillation pulse signals so as to classify and count the scintillation pulse signals, and realizing the multi-voltage threshold digital reading collecting card.
18. The photon counting multi-energy spectrum CT imaging method of claim 17, wherein the energy interval is preset according to the energy of the photons in a multi-voltage threshold digital readout circuit, the energy interval corresponding to the threshold interval, the multi-voltage threshold digital readout circuit comprising a plurality of digital readout channels, each readout channel comprising a plurality of comparators and a counting element in one-to-one correspondence with the plurality of comparators;
Presetting a plurality of thresholds by adopting the plurality of comparators, comparing the amplitude of the scintillation pulse signal with the preset thresholds, and acquiring the highest threshold reached by the scintillation pulse signal to determine a threshold interval corresponding to the amplitude of the scintillation pulse signal;
And determining an energy interval corresponding to the scintillation pulse signal according to a threshold interval corresponding to the amplitude of the scintillation pulse signal, and classifying and counting the scintillation pulse signal according to the energy interval by adopting the plurality of counting elements.
19. The photon counting multi-energy spectrum CT imaging method of claim 17, wherein presetting a plurality of thresholds in a multi-voltage threshold digital readout acquisition card, comparing the amplitude of the scintillation pulse signal with the preset plurality of thresholds is implemented using a comparator of the multi-voltage threshold digital readout acquisition card.
20. The photon counting multi-energy spectral CT imaging method according to claim 17, wherein the multi-voltage threshold digitizing readout circuit comprises a plurality of digitizing readout channels, each readout channel comprising a plurality of comparators.
21. The photon counting multi-energy spectrum CT imaging method of claim 15, wherein the image reconstruction industrial personal computer, the motion control bed, the radiation generating device, the data transmission industrial personal computer, the photon counting detecting device are powered by a replaceable power supply.
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| CN101052895A (en) * | 2004-10-29 | 2007-10-10 | 皇家飞利浦电子股份有限公司 | GOS ceramic scintillating fiber optics X-ray imaging plate for use in medical DF and RF imaging and in CT |
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| JPH09206296A (en) * | 1996-02-02 | 1997-08-12 | Matsushita Electric Ind Co Ltd | X-ray photographing device |
| CN101052895A (en) * | 2004-10-29 | 2007-10-10 | 皇家飞利浦电子股份有限公司 | GOS ceramic scintillating fiber optics X-ray imaging plate for use in medical DF and RF imaging and in CT |
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