Patent Description:
CT is an abbreviation of Computed Tomography. The imaging principle of CT is as follows: X-ray beams and X-ray detectors with very high sensitivity are used to scan the cross section of a certain part of a human body layer by layer. A scintillating material on the X-ray detectors receives X-ray passing through this layer, the X-ray is converted into visible light, then the visible light is converted into an electrical signal by a photoelectric converter, the electrical signal is amplified, then converted into a digital signal through analog-digital conversion, and finally the digital signal is input into a computer for processing. In the computer, the selected layer is divided into a plurality of cubes with the same volume, which are called as voxels. After the information obtained by layer-by-layer cross-sectional scanning is calculated, an X-ray attenuation or absorption coefficient of each voxel is obtained, and then a matrix, i.e., a voxel digital matrix, is obtained through arrangement. The digital information in the voxel digital matrix is converted into small square blocks with unequal gray levels from black to white, which are called as pixels in the sense of 2D projection. A CT image is formed through arrangement according to the layer dividing mode.

The applicant has disclosed a static real-time CT imaging system in the <CIT>. The system comprises an annular photon counting detector, an annular scanning X-ray source and a scanning sequence controller, wherein under the control of the scanning sequence controller, the annular scanning X-ray source emits a narrow beam of X-ray, which passes through the object to be measured and arrives at the corresponding annular photon counting detector. The annular photon counting detector sends the corresponding exposure information to a data acquisition processing unit and a human-computer interaction unit through a scanning host and a main control unit, and image reconstruction is completed in the data acquisition processing unit and the human-computer interaction unit. In the invention, by changing the X-ray projection position in turn through electronic control, the scanning speed is increased by tens of times, and dynamic 3D images can be obtained; by adopting the photon counting detector, absorption data and energy data can be obtained, and thus real-time data reconstruction is realized; by adopting the narrow beam of X-ray, high-quality images can be obtained at one-tenth dose of the traditional CT imaging system, and the patient is prevented from being excessively radiated.

On the other hand, cone-beam CT is a new stage in the development of CT. The cone-beam CT uses a flat panel detector to perform a series of radiation projection measurement from different angles to the object to be measured, and then obtains isotropic 3D structure information through a 3D reconstruction algorithm. In cone-beam CT detection, because of the limitation of the cone angle of the X-ray source and the size of the flat panel detector, it is often encountered that the size of the object to be measured exceeds the imaging field of view (FOV) of the cone-beam CT. In this case, the whole object to be measured cannot be scanned or reconstructed well by adopting conventional scanning methods and reconstruction algorithms. If the method of multi-time block-by-block scanning and reconstruction is adopted, the projection data corresponding to each block will be truncated vertically or horizontally. However, for the common CT reconstruction algorithm, if it is required that the object to be measured is completely covered by X-ray, the reconstruction effect is not ideal in the case of projection truncation.

In order to meet the needs of large visual field, the <CIT> has discloses a detector-biased large-field-of-view cone-beam X-ray oblique scanning 3D digital imaging method. In this method, a planar array detector is biased, and a cone-beam X-ray generated by an X-ray source obliquely transilluminates the imaging area of the component at a certain angle relative to the length and width surface of the component. In the scanning process, the ray source and the planar array detector are stationary, the component rotates for <NUM> degrees at equal angular step around the rotating axis, and the planar array detector obtains the ray signal modulated by the component at each rotating angle. With the same system hardware and scanning speed, the invention can double the oblique scanning imaging field of view. The patent publication <CIT> discloses a prior art system and method wherein the views between adjacent focal spots are interpolated by swinging the X-ray generation unit with an amplitude equal to the angle that separates the two focal spots.

In view of the shortcomings of the prior art, the primary technical problem to be solved by the invention is to provide a static real-time CT imaging system adaptable to large visual field requirements.

Another technical problem to be solved by the invention is to provide a method for realizing real-time imaging based on the CT imaging system.

The invention is defined by the enclosed claims.

Compared with the prior art, the static real-time CT imaging system and the imaging method, by emitting wide beam of X-rays through the multifocal annular X-ray sources, in cooperation with the non-inverse geometry imaging mode between the X-ray source and detector, can adapt to the large visual field requirements (i.e., FOV reaches about <NUM>-<NUM>).

The technical content of the invention will be further described below in detail with reference to the drawings in combination with the specific embodiments.

<FIG> is a mechanical structural schematic view of a static real-time CT imaging system. The static real-time CT imaging system specifically comprises a scanning bed unit <NUM>, a scanning frame unit <NUM>, a human-computer interaction unit <NUM>, a power supply control unit <NUM>, a ray source control unit <NUM>, a movement control unit <NUM>, a data acquisition processing unit <NUM>, a system main control unit <NUM> and an image data storage unit <NUM>, wherein the human-computer interaction unit <NUM>, the power supply control unit <NUM>, the ray source control unit <NUM>, the movement control unit <NUM>, the data acquisition processing unit <NUM>, the system main control unit <NUM> and the image data storage unit <NUM> may be provided inside an annular CT scanning component, the annular CT scanning component is mounted on the scanning frame unit <NUM>, and the scanning bed unit <NUM> passes through a circular space in the middle of the scanning frame unit <NUM>.

In one embodiment of the invention, the human-computer interaction unit <NUM>, the power supply control unit <NUM>, the ray source control unit <NUM>, the movement control unit <NUM>, the data acquisition processing unit <NUM> and the image data storage unit <NUM> are respectively connected with the system main control unit <NUM> to obtain operation instructions. <FIG> and <FIG> are mechanical structural schematic views of the scanning frame unit <NUM> in the static real-time CT imaging system. The scanning frame unit <NUM> further comprises a support <NUM>, a main bearing <NUM>, a driving motor <NUM>, a belt pulley <NUM>, a belt <NUM>, a rotating support <NUM>, a multifocal annular X-ray tube <NUM> and an annular photon detector <NUM>. It should be noted that, in the imaging process of the static real-time CT imaging system, the rotating support <NUM> does not need to perform rotation imaging like ordinary CT, and the rotating support <NUM> is relatively stationary for most of the time. When necessary, the driving motor <NUM> can drive the belt pulley <NUM>, the belt <NUM> and so on, such that the multifocal annular X-ray tube <NUM> on the rotating support <NUM> oscillates at a small angle along the circumference direction. This is to perform angle interpolation for fine reconstruction, which is not essentially a rotation imaging method like ordinary CT.

The static real-time CT imaging system, by emitting wide beam of X-rays through the multifocal annular X-ray sources, in cooperation with the non-inverse geometry imaging mode between the X-ray source and the detector, can adapt to the large visual field requirements (i.e., FOV reaches about <NUM>-<NUM>). This will be described below in detail.

The static real-time CT imaging system adaptable to large visual field requirements is composed of a multifocal annular X-ray source and an annular photon detector, wherein the multifocal annular X-ray source <NUM> and the annular photon detector <NUM> are mounted on the rotating support <NUM>, both of the multifocal annular X-ray source <NUM> and the annular photon detector <NUM> are on the same axis, and the axis is the Z axis commonly known in the field of CT. As illustrated in <FIG>, the multifocal annular X-ray source emits a wide beam of X-ray, and the corresponding annular photon detector operates in overlapping manner. For example, the No. <NUM> scanning X-ray source operates corresponding to the No. <NUM>, <NUM>, <NUM>, <NUM> and <NUM> photon detectors, the No. <NUM> scanning X-ray source operates corresponding to the No. <NUM>, <NUM>, <NUM>, <NUM> and <NUM> photon detectors, and the No. <NUM> scanning X-ray source operates corresponding to the No. <NUM>, <NUM>, <NUM>, <NUM> and <NUM> photon detectors, and so on. The corresponding operating mode is entire ring readout, that is, projection areas corresponding to a plurality of focuses are read out at one time. The focal plane of the multifocal annular X-ray source and the Z-direction central plane of the annular photon detector may overlap or not overlap. Considering from the angle of engineering implementation, it is easier to realize in engineering when the focal plane and the Z-direction central plane do not overlap. As illustrated in <FIG>, when the focal plane and the Z-direction central plane do not overlap, the X-rays are obliquely emitted to the surface of the detector (i.e., the detector modules in the annular photon detector are not perpendicular to the corresponding incident X-rays). Necessary geometric correction is required during imaging. Specific geometric correction algorithm is a common technical means commonly known by one skilled in the art, which will be not repetitively described here.

The multifocal annular X-ray source may consist of a plurality of independent scanning X-ray sources closely and uniformly arranged in an annular shape, may consist of annular X-ray sources with a plurality of focuses on which a plurality of cathodes are uniformly distributed, or may be composed of arc-shaped X-ray sources with a plurality of focuses on which a plurality of cathodes are uniformly distributed. The annular photon detector preferably is composed of a plurality of photon counting detector modules closely and uniformly arranged in an annular shape. A non-inverse geometry imaging method is used between the scanning X-ray source and the corresponding photon counting detector module. The number of the scanning X-ray sources arranged on the circumference may be consistent or inconsistent with the number of the photon counting detectors. As mentioned above, the photon counting detectors which form the annular photon detector may also be replaced by direct conversion, energy differentiation type or scintillator-based integration type X-ray detectors.

When the static real-time CT imaging system operates, the multifocal annular X-ray source is controlled by the ray source control unit and emits a wide beam of X-ray along the circumference direction, and the effect is equivalent to the circumferential rotation of the existing spiral CT. It should be noted that each scanning X-ray source of the multifocal annular X-ray source can emit X-rays clockwise or counter-clockwise. As illustrated in <FIG>, each scanning X-ray source of the multifocal annular X-ray source can successively emit X-rays along the circumferential direction sequentially or at an interval of a plurality of scanning X-ray sources. As illustrated in <FIG>, the multifocal annular X-ray source can emit X-rays simultaneously from one scanning X-ray source or simultaneously from a plurality of scanning X-ray sources in parallel. The maximum number of the scanning X-ray sources that emit X-rays in parallel is based on the premise that the X-rays emitted in parallel do not interfere with each other on the photon counting detectors, and preferably the circumferential distribution of the scanning X-ray sources that emit X-rays in parallel is circumferential uniform distribution.

The X-rays emitted by the multifocal annular X-ray source pass through the object to be measured and irradiate the corresponding photon counting detectors of the annular photon detector. The data acquisition processing unit is composed of a plurality of distributed subsystems, and embedded GPUs are integrated in the subsystems. The X-ray information received by the photon counting detectors is acquired and reconstructed by the data acquisition processing unit. The reconstructed image information is then transmitted to the image data storage unit and the human-computer interaction unit to complete image storage and visualization in the image data storage unit and the human-computer interaction unit. Of course, the existing CT data acquisition processing mode may be adopted, i.e., the data acquisition processing unit only acquires data, and then transmits the data to the image data storage unit for reconstruction and storage.

In the prior art, the number of focuses in the multifocal annular X-ray source determines the maximum circumferential projection density during static scanning. This projection density sometimes fails to meet some medical imaging needs which have higher requirements. In order to increase the maximum circumferential projection density, the static real-time CT imaging system provided by the invention can adopt the interpolation scanning mode. The circumferential projection density is enabled to be higher through the interpolation scanning mode, the energy spectrum scanning function can be realized and the multifocal parallel scanning speed is larger. As illustrated in <FIG>, during interpolation scanning, the multifocal annular X-ray source rotates at a uniform speed for an angle not less than the included angle range between two adjacent focuses, and within the period of moving in the included angle range, the multifocal annular X-ray source completes a plurality of times of X-ray emission, it is equivalent to adding a plurality of focuses between two focuses, and the number of times of X-ray emission is equal to the number of times of interpolation scanning.

During interpolation scanning, only the multifocal annular X-ray source may oscillate at a small angle along the circumferential direction, or the multifocal annular X-ray source and the annular photon detector may oscillate relative to each other along the circumferential direction, or the rotating support does not move as a whole, and the scanning bed carries the human body to oscillate along the circumferential direction. Referring to the oscillating interpolation principle illustrated in <FIG>, in one embodiment of the invention, if <NUM> focuses are uniformly distributed along the circumferential direction and the distance between adjacent focuses is <NUM>, the multifocal annular X-ray source and the annular photon detector oscillate for <NUM>° (<NUM>/<NUM>=<NUM>) relative to each other, and the focuses increase the projection number through oscillating interpolation in the range of <NUM>, such that the projection number can be greatly increased and the quality of image reconstruction is effectively improved.

In the static real-time CT imaging system, the multifocal annular X-ray source can be illuminated alternately by adopting a grid-control reflecting target mode. This mode has the features of large power and high brightness, which is hundreds of times higher than the brightness of the deflected electron beam transmission target commonly used in the prior art. In order to realize the above mode, the multifocal annular X-ray source is preferably realized by splicing a plurality of arc-shaped multifocal stationary anode grid-control ray sources. The details are as follows:
As illustrated in <FIG>, the arc-shaped multifocal stationary anode grid-control ray source comprises an arc-shaped ray source housing <NUM>, a ray tube support <NUM>, a plurality of stationary anode reflected ray tubes <NUM> and a plurality of grid control switches <NUM>, wherein the plurality of stationary anode reflected ray tubes <NUM> are fixed on the arc-shaped ray source housing <NUM> through the ray tube support <NUM>, and the focuses of the plurality of stationary anode reflected ray tubes <NUM> are distributed on the same distribution circle. More preferably, the focuses of the plurality of stationary anode reflected ray tubes <NUM> are uniformly distributed relative to the same distribution circle in a certain angle range α (<NUM>°≥α><NUM>°); the plurality of grid control switches <NUM> and the plurality of stationary anode reflected ray tubes <NUM> are correspondingly connected to control the on/off of the plurality of stationary anode reflected ray tubes <NUM>.

Taking the azimuth illustrated in <FIG> as an example, the specific structure of the arc-shaped multifocal stationary anode grid-control ray source will be described below.

As illustrated in <FIG>, the arc-shaped ray source housing <NUM> is preferably a closed housing consisting of an inner arc plate, an outer arc plate, a left side plate, a right side plate, a front side plate and a rear side plate. The ray tube support <NUM>, the plurality of stationary anode reflected ray tubes <NUM> and the plurality of grid control switches <NUM> are all provided inside the arc-shaped ray source housing <NUM>. The included angle θ between the outer edge of the left side plate and the outer edge of the right side plate of the arc-shaped ray source housing <NUM> may be arbitrarily selected in the range of <NUM>°-<NUM>°, and θ is preferably <NUM>°/N, where N is a positive integer, e.g., θ is equal to <NUM>°, <NUM>°, <NUM>°, <NUM>°, etc. When θ=<NUM>°/N and N><NUM>, N arc-shaped ray source housings <NUM> are spliced around the circumference, such that N arc-shaped multifocal stationary anode grid-control ray sources can form an entire ring structure, and the focuses of the plurality of stationary anode reflected ray tubes <NUM> can be distributed on the same distribution circle. It can be understood that, when θ=<NUM>°/N and N=<NUM>, the entire arc-shaped ray source housing is a circular ring structure, and the left side plate and the right side plate do not exist in theory.

As illustrated in <FIG>, the ray tube support <NUM> is preferably an arc-shaped support. The ray tube support <NUM> is fixed on the inner arc wall plate of the arc-shaped ray source housing <NUM> through bolts and other connectors, and the plurality of stationary anode reflected ray tubes <NUM> are fixed on the ray tube support <NUM>.

A plurality of through holes are uniformly provided in the ray tube support <NUM>, and the anode terminals of the plurality of stationary anode reflected ray tubes <NUM> respectively stretch out of the through holes in the ray tube support <NUM>, and the plurality of stationary anode reflected ray tubes <NUM> are respectively fixed on the ray tube support <NUM> through flanges. In the actual structure, by finely adjusting the fixing positions and angles of the stationary anode reflected ray tubes <NUM> on the ray tube support <NUM>, the focuses of the plurality of stationary anode reflected ray tubes <NUM> can be adjusted to the same circle. Hereinafter, the circle where the focuses of the plurality of stationary anode reflected ray tubes <NUM> are located is referred to as the distribution circle of the plurality of stationary anode reflected ray tubes <NUM>.

The inner and outer end surfaces of the arc-shaped ray source housing <NUM> are arc surfaces, and the inner arc plate and the outer arc plate are respectively and concentrically provided with the distribution circle of the plurality of stationary anode reflected ray tubes <NUM>. Of course, the inner arc plate and the outer arc plate may also be provided approximately concentrically. It is the most preferred that the inner arc plate and the outer arc plate are concentrically provided. The left and right end surfaces of the arc-shaped ray source housing <NUM> form an included angle θ and it is the most preferred that the extension lines of the left side plate and right side plate pass through the center of the distribution circle of a plurality of stationary anode emission ray tubes <NUM>.

The focuses of the plurality of stationary anode reflected ray tubes <NUM> are uniformly distributed relative to the distribution circle in a certain angle range α, the angle range α is less than or equal to the angle θ between the out edge of the left side plate and the out edge of the right side plate of the arc-shaped ray source housing <NUM>. In the actual structure, when the wall thickness of the left side plate and the right plate is small and the number of the stationary anode reflected ray tubes <NUM> provided in one arc-shaped ray source housing <NUM> is small, α and θ are approximately equal. More preferably, in the n stationary anode reflected ray tubes <NUM> provided in the same arc-shaped ray source housing <NUM>, the angle between two adjacent stationary anode reflected ray tubes <NUM> is θ/n, and the angle between the leftmost and rightmost stationary anode reflected ray tubes <NUM> and the outer edge of the adjacent side plate is θ/2n. When the wall thickness of the left side plate and the right side plate is large or the number of the stationary anode reflected ray tubes <NUM> provided in one arc-shaped ray source housing <NUM> is large, α<θ, the angle between two adjacent stationary anode reflected ray tubes <NUM> is α/n, and the angle between the leftmost and rightmost stationary anode reflected ray tubes <NUM> and the outer edge of the adjacent side plate may be larger than α/2n or smaller than α/2n.

In the embodiment of the invention, the anode terminals of the used stationary anode reflected ray tubes <NUM> generate X-ray beams by using reflective stationary anode targets. The two ends of each stationary anode reflected ray tube <NUM> are an anode terminal and a cathode terminal respectively. A grid is provided near the cathode in the stationary anode reflected ray tube <NUM>. As illustrated in <FIG>, each stationary anode reflected ray tubes <NUM> is provided with an independent grid control switch <NUM>. The grid control switch <NUM> is fixed with the tube body of the stationary anode reflected ray tube <NUM> through a support, and the output end of the grid control switch <NUM> is connected to the grid of the stationary anode reflected ray tube <NUM> through a conducting wire to control the on/off of the stationary anode reflected ray tube <NUM> and realize the control of the ray output. The emitted X-ray beam <NUM> after being reflected by the anode terminal is as illustrated in <FIG> and Fig. 3B. Of course, the on/off of a plurality of adjacent stationary anode reflected ray tubes <NUM> may also be controlled by the same grid control switch <NUM>. However, among the above control modes, it is preferred to adopt the control mode that the stationary anode reflected ray tubes <NUM> correspond to the grid control switches <NUM> one to one, as illustrated in the drawings.

As illustrated in <FIG>, by connecting the left side plates and the right side plates of N arc-shaped ray source housings <NUM> from head to tail, the N arc-shaped multifocal stationary anode grid-control ray sources can be spliced to form an "entire ring structure", such that the focuses of the plurality of stationary anode reflected ray tubes <NUM> can be distributed on the same distribution circle as uniformly as possible. By controlling the grid control switches <NUM> in the entire ring structure, the stationary anode reflected ray tubes <NUM> sequentially emit X-ray beams, such that sequential ray output for scanning in the direction of <NUM>° can be realized. In the entire ring structure, the X-ray beam <NUM> emitted by each stationary anode reflected ray tube <NUM> illuminates the center of the entire ring.

When the angle between two adjacent stationary anode reflected ray tubes <NUM> provided in the same arc-shaped ray source housing <NUM> is θ/n, and the angle between the leftmost and rightmost stationary anode reflected ray tubes <NUM> and the outer edge of the adjacent side plate is θ/2n, by forming an entire ring structure through the N arc-shaped multifocal stationary anode grid-control ray sources, the focuses of all stationary anode reflected ray tubes <NUM> in the N arc-shaped multifocal stationary anode grid-control ray sources can be enabled to be uniformly distributed on the distribution circle. When the angle between two adjacent stationary anode reflected ray tubes <NUM> provided in the same arc-shaped ray source housing <NUM> is other values, in the entire ring structure consisting of N arc-shaped multifocal stationary anode grid-control ray sources, the focuses of all stationary anode reflected ray tubes <NUM> provided in N arc-shaped ray source housings <NUM> are distributed on the same distribution circle, and the focuses of the plurality of stationary anode reflected ray tubes <NUM> in each arc-shaped ray source housing <NUM> are uniformly distributed.

In the invention, a plurality of arc-shaped ray source housings may be spliced to form an entire ring structure, such that the focuses of all stationary anode reflected ray tubes in the plurality of arc-shaped multifocal stationary anode grid-control ray sources are uniformly distributed on the same distribution circle, so as to form a complete multifocal annular X-ray source. In the arc-shaped multifocal stationary anode grid-control ray sources, a plurality of grid control switches are correspondingly connected with a plurality of stationary anode reflected ray tubes, and the grid control switches can control the on/off of the circuit of the stationary anode reflected ray tubes, thus realizing the control of ray output. The arc-shaped multifocal stationary anode grid-control ray sources have the advantages that the structure is simple, the cost is low, rays with sufficient intensity can be generated, and a sufficient number of focuses are distributed in the circumferential direction.

As illustrated in <FIG>, the static real-time CT imaging system can realize multi-mode energy spectrum scanning by using the multifocal annular X-ray source. The details are as follows:
Firstly, the multifocal annular X-ray source may perform energy spectrum scanning by using the instantaneous energy switching of a single scanning X-ray source, and can instantaneously switch to a variety of energy levels (such as switching between <NUM> kV, <NUM> kV and <NUM> kV illustrated in <FIG>). The number of specifically switched energy levels is determined by the design requirement. After a certain scanning X-ray source performs energy spectrum scanning through instantaneous energy switching, a next scanning X-ray source under the control of scanning sequence performs energy spectrum scanning by adopting the same way until the entire scanning operation is completed. Secondly, the multifocal annular X-ray source may perform energy spectrum scanning by adopting circumferential intermittent energy switching. That is to say, all scanning X-ray sources of the multifocal annular X-ray source complete one circumferential scanning at the same energy level under the control of sequence, then are all switched to another energy level to repetitively complete the next circumferential scanning until switching to all energy levels is completed. Thirdly, the multifocal annular X-ray source may also be perform energy spectrum scanning by adopting a circumferential multi-energy spectrum scanning mode, i.e., the scanning X-ray sources distributed on the circumference are divided into a plurality of groups, each group is unified for one energy level, and after one circumferential scanning is completed under the control of sequence, the energy level of each group of scanning X-ray sources is switched to the corresponding next energy level, and the next circumferential scanning is repetitively completed until switching to all energy levels is completed.

It should be noted that the photon counting detectors in the invention may also be replaced by an integration type detectors to achieve the same function. The imaging effect of the integration type detectors is worse than that of the photon counting detectors, but the function is relatively stable due to the mature technology of the integration type detectors.

<FIG> is a flowchart that the static real-time CT imaging system provided by the invention realizes image reconstruction. In the static real-time CT imaging system, the data acquisition processing unit <NUM> is composed of a main control computer, a real-time reconstruction system and a visualization processor. The system main control unit <NUM> comprises a scanning sequence controller, high-speed data transmission channels, etc. The data processing function of the main control computer is accomplished by a main processor for parallel reconstruction of data and a storage device for storing voxel data. The scanning host comprises a plurality of photon counting detector modules <NUM>-XX (XX is a positive integer, the same below). Each photon counting detector module comprises a plurality of photon counting detector units, e.g., the photon counting detector module <NUM> comprises photon counting detector units <NUM>-XX.

In one preferred embodiment of the invention, each photon counting detector module is composed of <NUM>*<NUM>=<NUM> photon counting detector units, and each photon counting detector unit is composed of <NUM>*<NUM> photon counting detector pixels. The size of each pixel is <NUM>*<NUM>. The external size of each photon counting detector module is <NUM>*<NUM>. The annular photon detector totally is composed of <NUM> photon counting detector modules. The diameter of the formed annular photon detector is about <NUM> and the width is <NUM>. There are a plurality of data acquisition channels, each of which corresponds to one or more photon counting detector modules. The data acquired by the plurality of photon counting detector modules <NUM>-XX are transmitted to the data preprocessing module of the scanning host through the data acquisition channels <NUM>-XX. The data preprocessing module is composed of a GPU, an ASIC or DSP, performs frame data preprocessing to original pixel exposure information transmitted by the data acquisition channels or the data subjected to data rearrangement and data correction, so as to form a frame data block, which is then transmitted to the parallel reconstruction module of the data acquisition processing unit through the high-speed data parallel transmission channels in the main control unit. The parallel reconstruction module may consist of a plurality of parallel GPUs or may consist of special ASIC. The reconstruction module reconstructs the uploaded frame or block data into block data. Since the above process is multi-channel parallel processing, the reconstruction speed can meet the requirement of real-time visual display.

An acquisition controller in the data acquisition processing unit <NUM> transmits commands to each photon counting detector module through an acquisition command channel under the control of scanning sequence controller to acquire pixel exposure information. Herein, the independent acquisition command channel is a multi-channel wide-digit bus, which ensures that all acquisition modules synchronously receive acquisition commands in parallel to ensure that the acquired frame data are data of the same frame period. The acquired pixel exposure information data are firstly integrated at the level of the photon counting detector units, then the data of the photon counting detector units are subjected to integration and process for the second time by the photon counting detector modules, including data splicing and module-level pixel data correction. Finally, the integrated or preliminarily reconstructed X-ray data are transmitted to a data preprocessor by the photon counting detector modules through parallel optical fiber data transmission channels.

The data preprocessor firstly performs frame data preprocessing to the X-ray data from different photon counting detector modules, including frame data rearrangement, frame data correction, frame data caching and real-time output of frame data. The real-time output frame data are transmitted to the real-time reconstruction system and the main control computer. Herein, the main task of the data preprocessor is to organize the data from the plurality of photon counting detector modules into complete data frames and data blocks, which are sent to the main control computer according to the format of frames and blocks. The data frame here refers to a data layer covering a complete range of <NUM>°, and the data block refers to an array consisting of a plurality of data layers. The purpose of this data preprocessing mechanism is to complete the preliminary processing of some data processing tasks before the tasks are transmitted to the computer. The mechanism compiles the data acquired according to various acquisition orders edited by the controller into data formats of frames and blocks, and transfers the standard frame and block data to the main control computer for processing. Sometimes, we can put part of the preprocessing function of frame and block data in the data preprocessor, or put this part of data processing after the transmission to the main control computer, which is then completed by the main control computer. This part of preprocessing includes but not limited to error correction of single pixel, hardening correction, flat field correction of frame data, geometric correction of frame data or block data, time drift correction, energy correction, scattered ray suppression, etc..

In the prior art, multi-row spiral CT needs to rotate at high speed because of the X-ray source. In the process of rotation, it needs to transmit data to the computer by means of slip ring contact or wireless transmission. Compared with the existing multi-row spiral CT, the static real-time CT imaging system does not need a slip ring structure because of the absence of conventional rotation imaging links, and there is no mechanical movement false image. The static real-time CT imaging system can realize parallel data transmission by using optical fibers with better speed and reliability, the transmitted data flow increases, the reliability of data signals is improved, the overall structure is clearer and more reasonable, and the reliability and consistency of products are better. In this way, the real-time performance of the 3D reconstruction algorithm can be effectively guaranteed.

Claim 1:
A static real-time CT imaging system, comprising a scanning bed unit (<NUM>), a scanning frame unit (<NUM>), a human-computer interaction unit (<NUM>), a power supply control unit (<NUM>), a ray source control unit (<NUM>), a movement control unit (<NUM>), a data acquisition processing unit (<NUM>), a system main control unit (<NUM>) and an image data storage unit (<NUM>), wherein the scanning frame unit (<NUM>) comprises a multifocal annular X-ray source (<NUM>) and an annular photon detector (<NUM>);
the multifocal annular X-ray source (<NUM>) is composed of a plurality of scanning X-ray sources arranged in an annular shape, and the annular photon detector (<NUM>) is composed of a plurality of photon counting detector modules arranged in an annular shape;
each scanning X-ray source is configured to emit a wide beam of X-ray in turn which passes through the object to be measured and arrives at the corresponding photon counting detector module, and non-inverse geometry imaging is adopted between the scanning X-ray source and the corresponding photon counting detector module;
characterized in that
the multifocal annular X-ray source (<NUM>) is configured to rotate at a uniform speed for an angle larger than any included angle range separating two adjacent focuses, and within the period of moving in the included angle range, the multifocal annular X-ray source (<NUM>) is further configured to emit the wide beam of X-ray for many times to realize an interpolation scanning mode; and
the photon counting detector modules are configured to operate in an overlapping manner and to send the corresponding exposure information to the data acquisition processing unit (<NUM>), and the image is reconstructed in real time and visualized in the data acquisition processing unit (<NUM>).