Multi-section linear array X-ray source static real-time CT imaging system and imaging method

Abstract

The invention discloses a multi-section type linear array X-ray source static real-time CT imaging system and an imaging method, and the multi-section type linear array X-ray source static real-time CT imaging system is provided with a scanning device and a ray source control unit; the scanning device is provided with a multi-section X-ray source array and a detector, the transmitting end of the multi-section X-ray source array faces the detector, and the multi-section X-ray source array is connected with the ray source control unit. The multi-section X-ray source array has the advantages that the multi-section X-ray source array can freely adjust the length and the included angle of the whole section, and the multi-section X-ray source array is suitable for a large-size measured object; 2, the multi-section X-ray source array can use fewer X-ray sources to realize the same wide view field, the design is more free, and the expansion is easier; 3, the distribution of ray sources can be relatively dispersed, the crossing of ray paths is less, and the interference of scattered signals can be obviously reduced; and 4, the exposure strategy of the scanning device can be controlled through the radiation source control unit, and the radiation dose utilization rate is optimized.

Description

Technical Field

[0001] The present invention relates to the technical field of static CT real-time imaging, and in particular to a multi-segment linear array X-ray source static real-time CT imaging system and an imaging method thereof. Background Art

[0002] Computed tomography (CT) uses an X-ray beam and a highly sensitive detector to scan a target layer by layer. After penetrating the object, the X-rays are received by a scintillating material within the detector and converted into visible light. This light is then converted into an electrical signal by a photoelectric converter. After amplification and analog-to-digital conversion, the electrical signal is generated and transmitted to a computer for processing. In the computer, the scanned area is divided into multiple cubic units of equal volume, called voxels. The X-ray attenuation coefficient for each voxel is calculated and arranged into a digital matrix, known as the voxel matrix. The values in the matrix are mapped to small blocks of varying grayscale levels, called pixels, on a two-dimensional plane. These blocks are arranged in a sequential order to form a CT image. This technology is widely used in fields such as medical diagnosis and industrial inspection.

[0003] Chinese patent application No. 202310118999.9 discloses a static real-time CT imaging system and an imaging method thereof, wherein the static real-time CT imaging system includes a left ray tube ring, a right ray tube ring and a detector ring, wherein the ray tube rings are composed of multiple X-ray tubes, and the detector rings are divided into a left detector sub-ring, a middle detector sub-ring and a right detector sub-ring. Although the static real-time CT imaging system uses dual ray tube rings and segmented detector rings to achieve large-field dynamic imaging, the design of the dual ray tube rings and segmented detector rings increases the complexity of the system and increases manufacturing and maintenance costs. In addition, the design of the dual ray tube rings may make it difficult to finely control the radiation distribution in some cases, which may pose a potential risk to patients.

[0004] In the Chinese patent application with the Chinese patent application number 201880000723.8, a static real-time CT imaging system and an imaging method thereof that adapt to the requirements of a large field of view are disclosed. The system includes a multi-focus annular X-ray tube and an annular photon counting detector. In this static real-time CT imaging system, the multi-focus annular X-ray tube emits a wide beam of X-rays. Although it expands the scanning field of view, the wide beam design may aggravate the scattered signal. The scattered signal will interfere with the signal acquisition of the photon counting detector, thereby reducing the image signal-to-noise ratio, especially when imaging complex structures or high-density objects. Secondly, the interleaved working mode of the multi-focus annular X-ray tube and the photon counting detection module in the static real-time CT imaging system requires highly precise timing control and calibration. Even a slight timing deviation or hardware mismatch may lead to inconsistency in the projection data, thereby affecting the quality of image reconstruction.

[0005] Therefore, in view of the shortcomings of the existing technology, it is necessary to provide a multi-segment linear array X-ray source static real-time CT imaging system and an imaging method thereof to solve the shortcomings of the existing technology. Summary of the Invention

[0006] A first objective of the present invention is to overcome the shortcomings of the prior art and provide a multi-segment linear array X-ray source static real-time CT imaging system. This multi-segment linear array X-ray source static real-time CT imaging system can achieve large field of view, high-efficiency, real-time three-dimensional imaging, and can flexibly control the exposure sequence, range, and X-ray energy.

[0007] The above-mentioned purpose of the present invention is achieved through the following technical measures:

[0008] A multi-segment linear array X-ray source static real-time CT imaging system is provided, comprising:

[0009] Scanning device - generates projection data by emitting X-rays so that the X-rays pass through the object to be measured;

[0010] The ray source control unit controls the scanning device to emit X-rays in a time sequence through a time sequence exposure mode to control the exposure sequence and exposure range, and can also control the energy of the X-rays.

[0011] The scanning device is provided with a multi-segment X-ray source array and a detector, wherein the emission end of the multi-segment X-ray source array faces the detector, and the multi-segment X-ray source array is connected to the ray source control unit.

[0012] The multi-segment X-ray source array is composed of more than three linear ray source segments, and all the linear ray source segments are connected end to end from front to back.

[0013] Each linear ray source section is provided with a plurality of mutually independent ray tubes, and the ray tubes in the same linear ray source section are arranged linearly.

[0014] Preferably, the above-mentioned ray source control unit is provided with a high-voltage switch controller for independently controlling each of the ray tube switches, and the high-voltage switch controller is provided with multiple high-voltage switch modules, and each ray tube is connected to one high-voltage switch module.

[0015] The multi-segment linear array X-ray source static real-time CT imaging system of the present invention is further provided with:

[0016] Data acquisition and processing unit - collects projection data from the detection module in the detector; then performs interpolation and enhancement operations on the projection data, fills in the information between adjacent projection points through an algorithm, optimizes data sampling density, and obtains image data;

[0017] Data storage unit - storing the image data of the data acquisition and processing unit;

[0018] Carrier: used to fix the scanning device;

[0019] User interaction unit - for inputting clinical parameters;

[0020] System main control unit - based on the clinical parameters input by the user interaction unit and according to the built-in algorithm, it generates the corresponding coding scheme, transmits the coding instructions to the high-voltage switch controller, and controls the data acquisition and processing unit to work.

[0021] Preferably, the multi-segment X-ray source array is provided with a plurality of tube holders and a plurality of filters for adjusting the X-ray spectrum, the X-ray tubes are assembled on the carrier frame through the tube holders, the high-voltage switch module is fixed on the surface of the X-ray tubes, and the filters are fixed on the X-ray tubes.

[0022] Preferably, the number of the tube supports, the number of the filters, and the number of the X-ray tubes correspond one to one.

[0023] Preferably, the above-mentioned linear ray source segment is provided with three segments, and the three linear ray source segments are respectively defined as a left linear ray source segment, a middle linear ray source segment and a right linear ray source segment.

[0024] Preferably, the rear end of the left linear ray source segment is connected to the front end of the middle linear ray source segment, the rear end of the middle linear ray source segment is connected to the front end of the right linear ray source segment, the front end of the left linear ray source segment is connected to the detector, and the rear end of the right linear ray source segment is connected to the detector.

[0025] A front end of the left linear ray source segment and a rear end of the right linear ray source segment are connected by a virtual straight line, and the left linear ray source segment, the middle linear ray source segment, the right linear ray source segment and the virtual straight line form an isosceles trapezoid.

[0026] Preferably, the base angle of the isosceles trapezoid is 60°.

[0027] Preferably, the above-mentioned detector is an arc-shaped detector.

[0028] Preferably, the detector is composed of a plurality of detachable detection modules, and the plurality of detection modules are sequentially spliced from front to back to form the arc-shaped detector.

[0029] Preferably, the detection module is at least one of a photon counting detector and an integrating detector.

[0030] Preferably, the above-mentioned sequential exposure mode is a segmented exposure mode or a synchronous pulse mode.

[0031] A second object of the present invention is to provide an imaging method that overcomes the shortcomings of the prior art. This imaging method can achieve real-time three-dimensional imaging with a large field of view and high efficiency.

[0032] The above-mentioned purpose of the present invention is achieved through the following technical measures:

[0033] An imaging method is provided, which is performed using the above-mentioned multi-segment linear array X-ray source static real-time CT imaging system.

[0034] In the imaging method of the present invention, the high-voltage switch controller controls the three-segment X-ray source array to emit X-rays in a time-sequential exposure manner, and dynamically adjusts the output energy of each ray tube in the three-segment X-ray source array to achieve multi-energy spectrum scanning.

[0035] The detector collects projection data of X-rays after passing through the object to be measured; and simultaneously completes data collection of different energy levels in sequence.

[0036] The data acquisition and processing unit acquires the projection data, then performs an interpolation enhancement operation, processes the projection data by filling in information between adjacent projection points through an algorithm, performs image reconstruction in real time to obtain image data, and then saves the image data to the data storage unit.

[0037] The present invention provides a multi-segment linear array X-ray source static real-time CT imaging system and imaging method, wherein the multi-segment linear array X-ray source static real-time CT imaging system is provided with: a scanning device - which generates projection data by emitting X-rays so that the X-rays pass through the object to be measured; a ray source control unit - which controls the scanning device to emit X-rays in a timed sequence through a timed exposure mode to control the exposure sequence and exposure range, and can also control the energy of the X-rays; the scanning device is provided with a multi-segment X-ray source array and a detector, the emission end of the multi-segment X-ray source array is facing the detector, and the multi-segment X-ray source array is connected to the ray source control unit; the multi-segment X-ray source array is composed of more than three linear ray source segments, and all the linear ray source segments are connected end to end from front to back. The beneficial effects of the present invention are as follows: 1. The multi-segment X-ray source array of the present invention can freely adjust the entire length and angle of the entire segment to achieve a larger lateral range than a circular array, which is suitable for large-sized objects to be measured. The present invention can improve the coverage and quality of wide-field imaging through a multi-segment X-ray tube array; 2. The circular array of the prior art requires more X-ray sources to achieve a certain field of view, while the multi-segment X-ray source array of the present invention can use fewer X-ray sources to achieve the same wide field of view; and circular arrays are limited by radius and find it difficult to achieve a relatively wider range. The multi-segment X-ray source array of the present invention has a more flexible design and is easier to expand; 3. The ray source distribution of the multi-segment X-ray source array can be relatively dispersed, with less intersection of ray paths, and significantly reduced interference from scattered signals; 4. The exposure strategy of the scanning device can be controlled by the ray source control unit, and the emission of X-rays from different areas of the multi-segment X-ray source array can be flexibly controlled to control the exposure order, range, and energy of the X-rays, thereby optimizing the radiation dose utilization rate and reducing radiation exposure to non-target areas. It is particularly suitable for high-precision medical imaging scenarios such as stroke. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] The present invention is further described with reference to the accompanying drawings, but the contents in the accompanying drawings do not constitute any limitation to the present invention.

[0039] Figure 1 This is a structural diagram of a multi-segment linear array X-ray source static real-time CT imaging system.

[0040] Figure 2 Schematic diagram of data transmission of a multi-segment linear array X-ray source static real-time CT imaging system.

[0041] Figure 3 A schematic diagram of the structure of the scanning device.

[0042] Figure 4 Schematic diagram of the structure of a multi-segment X-ray source array and detector.

[0043] Figure 5Schematic diagram of an isosceles trapezoid formed by a multi-segment X-ray source array in Example 1.

[0044] Figure 6 This is a schematic diagram of the middle linear ray source segment at work.

[0045] Figure 7 This is a schematic diagram of the linear ray source segment on the left at work.

[0046] Figure 8 This is a schematic diagram of the linear ray source segment on the right side at work.

[0047] Figure 9 This is a structural diagram of the X-ray tube, tube bracket, filter and high-voltage switch module.

[0048] Figure 10 Schematic diagram of a ray tube emitting X-rays to a detector.

[0049] Figure 11 It is the data processing flow degree of the three-segment linear ray source segment when it is working.

[0050] exist Figures 1 to 11 Including:

[0051] Scanning device 100,

[0052] Multi-segment X-ray source array 110, linear ray source segment 111, ray tube 112, tube holder 113, filter 114,

[0053] Detector 120,

[0054] Radiation source control unit 200, high voltage switch module 210,

[0055] Data acquisition and processing unit 300 , scanning bed 400 , data storage unit 500 , carrier 600 , user interaction unit 700 , and system main control unit 800 . DETAILED DESCRIPTION

[0056] The technical solution of the present invention is further described with reference to the following examples.

[0057] Example 1

[0058] A multi-segment linear array X-ray source static real-time CT imaging system, such as Figure 1 and Figure 2 , the settings are:

[0059] Scanning device 100 - generates projection data by emitting X-rays that pass through the object to be measured. The scanning device 100 is provided with a multi-segment X-ray source array 110 and a detector 120. The emission end of the multi-segment X-ray source array 110 faces the detector 120. The multi-segment X-ray source array 110 is connected to a radiation source control unit 200.

[0060] The X-ray source control unit 200 controls the scanning device 100 to emit X-rays in a timed sequence to control the exposure order and exposure range, and also controls the energy of the X-rays through a timed exposure mode. The timed exposure mode can be a segmented contact mode or a synchronous pulse mode.

[0061] The data acquisition and processing unit 300 collects projection data from the detection modules in the detector 120; then performs interpolation and enhancement operations on the projection data, using an algorithm to fill in the information between adjacent projection points, optimize the data sampling density, and obtain image data;

[0062] Data storage unit 500 - stores image data from the data acquisition and processing unit 300;

[0063] Carrier 600 - used to fix the scanning device 100;

[0064] User interaction unit 700 - used to input clinical parameters;

[0065] System main control unit 800 - generates the corresponding coding scheme according to the built-in algorithm and transmits the coding instructions to the high-voltage switch controller.

[0066] The multi-segment X-ray source array 110 of the present invention is composed of three or more linear X-ray source segments 111, all of which are connected end-to-end from front to back. Each linear X-ray source segment 111 is equipped with multiple independent X-ray tubes 112, which are arranged linearly within the same linear X-ray source segment 111. The X-ray source control unit 200 is equipped with a high-voltage switch controller for independently controlling the switching of each X-ray tube 112. The high-voltage switch controller is equipped with multiple high-voltage switch modules 210, and each X-ray tube 112 is connected to a high-voltage switch module 210.

[0067] The number of the linear ray source segments 111 of the present invention can be determined according to actual conditions, such as three, four, six, ten, etc. The present invention is described with three segments as an example. Figure 3 and Figure 4. The present invention defines three linear ray source segments 111 as a left linear ray source segment 111, a middle linear ray source segment 111 and a right linear ray source segment 111 respectively; the rear end of the left linear ray source segment 111 is connected to the front end of the middle linear ray source segment 111, the rear end of the middle linear ray source segment 111 is connected to the front end of the right linear ray source segment 111, the front end of the left linear ray source segment 111 is connected to the detector 120, and the rear end of the right linear ray source segment 111 is connected to the detector 120. A virtual straight line is connected between the front end of the left linear ray source segment 111 and the rear end of the right linear ray source segment 111, and the left linear ray source segment 111, the middle linear ray source segment 111, the right linear ray source segment 111 and the virtual straight line form an isosceles trapezoid, and the base angle of the isosceles trapezoid is 60°, as shown in FIG. Figure 5 .

[0068] It should be noted that the radiation source control unit 200 of the present invention controls the emission of the X-ray tube 112 through a sequential exposure mechanism. Specifically, the sequential exposure mode is a segmented trigger mode or a synchronized pulse mode to improve imaging efficiency. Furthermore, the radiation source control unit 200 of the present invention can control the order and range of exposure of the X-ray tube 112 based on the patient's affected area through specific coding, thereby reducing radiation exposure. The sequential exposure mode of the present invention supports dynamic adjustment of the emission sequence, optimizing the exposure time of the center and edge radiation sources, and improving the integrity of the projection data. The base angle of the isosceles trapezoid in this embodiment can be 30°, 45°, 60°, 70°, 80°, etc. When the base angle of the isosceles trapezoid is 60°, the X-ray tubes 112 at the front end of the left linear radiation source segment 111 and the rear end of the right linear radiation source segment 111 are relatively easy to arrange. Furthermore, the horizontal and vertical distances between the multi-segment X-ray source array 110 are relatively moderate, and the three linear radiation source segments 111 are all of the same length, resulting in a more regular geometric distribution.

[0069] In the static real-time CT imaging system of the present invention, the X-ray tubes 112 of the multi-segment X-ray source array 110 achieve precise timing control and switching operation through a high-voltage switch controller. This control method is based on the high-voltage switch controller, which adopts a compact electronic module design and integrates high-performance solid-state switches (such as IGBT transistors) or high-voltage relays. The high-voltage switch controller can turn individual X-ray tubes 112 on and off by quickly switching the on and off state of the high-voltage power supply. Compared with the traditional deflected electron beam transmission target method, this control method provides greater control flexibility and reliability, is particularly suitable for high-frequency switching scenarios, and significantly improves the operating efficiency and stability of X-ray tubes 112. To achieve the above functions, the multi-segment X-ray source array 110 is composed of multiple linear X-ray source segments 111, which in turn are composed of multiple X-ray tubes 112. The high-voltage switch controller coordinates the independent emission timing of each tube.

[0070] The static, real-time CT imaging system of the present invention utilizes a multi-segment X-ray source array 110 to emit cone-beam X-rays. This system, coupled with a non-inverted geometric imaging system between the X-ray tube 112 and the detector 120, can meet the requirements of a wide field of view and high resolution. Both the multi-segment X-ray source array 110 and the detector 120 are mounted on a carrier 600, with the multi-segment X-ray source array 110 and the detector 120 lying in the same plane, defined as the XY plane. The direction of motion of the scanning table 400 of the static, real-time CT imaging system is defined as the Z-axis.

[0071] In the layout of the multi-segment X-ray source array 110 of the present invention, the scanning device 100 is a multi-segment linear frame structure with multiple mounting slots on the inner wall for evenly accommodating the X-ray tubes 112. The X-ray tubes 112 within each linear X-ray source segment 111 are arranged along a linear path, with their focal points evenly distributed in the XY plane to ensure uniform projection density. X-ray beams are emitted from each X-ray tube 112 and converge toward the scanning center, forming a continuous projection coverage. The outer wall of the scanning device 100 of the present invention is designed as a multi-layer structure, with the inner layer being a heat dissipation material and the outer layer being a shielding layer to prevent X-ray leakage. The overall layout of the multi-segment X-ray source array 110 is achieved through geometric symmetry, wherein the number of tubes in each X-ray source array segment can be dynamically configured according to imaging requirements.

[0072] The multi-segment X-ray source array 110 of the present invention is composed of multiple independent ray tubes 112, which cover a 180° projection range. Figure 5 In the present invention, each X-ray tube 112 is driven by an independent high-voltage switch controller, supporting a variety of flexible exposure modes to meet different clinical needs, which can be achieved by the following steps:

[0073] First, the operator inputs clinically required parameters (e.g., imaging of a left-side brain lesion) through the user interface unit 700. The system's main control unit 800 generates a corresponding encoding scheme based on a built-in algorithm and transmits the encoding instructions to the high-voltage switch controller. The high-voltage switch controller integrates multiple high-voltage switch modules 210, each of which independently controls the power supply to a single X-ray tube 112. The system supports multiple sequential emission modes, including emission from the left linear X-ray source segment 111 to the right linear X-ray source segment 111, from the right linear X-ray source segment 111 to the left linear X-ray source segment 111, and from the middle linear X-ray source segment 111 to the left and right linear X-ray source segments 111. Taking the sequential emission from the left linear ray source segment 111 to the right linear ray source segment 111 as an example, the high-voltage switch controller sequentially closes the high-voltage switches of the left linear ray source segment 111, the middle linear ray source segment 111, and the right linear ray source segment 111 according to a preset timing, triggering X-ray emission segment by segment; it can be used for full-range brain scanning in neurology to obtain continuous projection data to assist comprehensive diagnosis.

[0074] Second, when implementing the synchronous exposure mode, the high-voltage switch controller simultaneously closes all high-voltage switch modules 210, causing all ray tubes 112 to emit X-rays synchronously; this can be used for rapid stroke imaging in the emergency department, where high-density data needs to be acquired in a short time.

[0075] Third, to achieve a local exposure mode, for example, for imaging a lesion on the left side of the brain, the operator inputs lesion location information through the user interaction unit 700, and the system main control unit 800 generates a code to activate only the left linear radiation source segment 111. After receiving the command, the high-voltage switch controller turns on the radiation tube 112 of the left linear radiation source segment 111, keeps the radiation tubes 112 of the right linear radiation source segment 111 and the middle linear radiation source segment 111 turned off, and cuts off their power to prevent X-ray emission. At the same time, the exposure dose or frequency is increased by adjusting the power supply voltage or pulse width of the radiation tube 112 of the left linear radiation source segment 111. This can be used for high-precision imaging of local lesions in oncology.

[0076] Fourth, in addition to the above-mentioned specific coding scheme for achieving sequential exposure, in complex lesion scenarios, the high-voltage switch controller of the present invention can set the X-ray tube 112 of the middle linear X-ray source segment 111 in the multi-segment X-ray source array 110 to operate at high voltage through coding, while the other X-ray tubes 112 operate at low voltage or are turned off. Specifically, high-dose focused exposure is achieved by adjusting the power supply parameters. This is suitable for coronary artery imaging in the cardiovascular department, where the fine structure of the target area needs to be highlighted.

[0077] The implementation of the above-mentioned exposure strategy of the present invention is that after the lesion information is input through the user interaction unit 700, the system main control unit 800 automatically generates the code, or calls it through a pre-stored template. After generation, the system main control unit 800 transmits it to the high-voltage switch controller for execution, ensuring the efficiency and accuracy of the operation.

[0078] The X-rays emitted by the multi-segment X-ray source array 110 of the present invention pass through the object to be measured and are then projected onto the corresponding detection modules on the detector 120. The data acquisition and processing unit 300 utilizes a high-performance computing module design, integrating a multi-core processor to accelerate data processing. The data acquisition and processing unit 300 collects projection data in real time from the X-ray signals received by the detection modules. The data processing unit then reconstructs the image. The reconstructed image data is directly transmitted to the data storage unit 500 for storage and to the user interaction unit 700 for visual display and operation.

[0079] The detector 120 of the present invention is an arc-shaped detector 120; the detector 120 is composed of multiple detachable detection modules, which are sequentially assembled from front to back to form the arc-shaped detector 120. The detection modules are at least one of a photon counting detector 120 and an integrating detector 120. The detection modules of the present invention are detachable from the carrier 600. The type of detection module in the detector 120 can be replaced according to actual conditions to meet different imaging accuracy requirements. The configuration of the detection modules can be specifically achieved through the following steps:

[0080] First, all detection modules are replaced with an integrating detector 120. Detector 120 is a single integrating detector 120. Specifically, during installation, integrating detector 120 is fixed to the curved bracket of carrier frame 600 and connected to data acquisition and processing unit 300 via a standard data interface to ensure rapid signal acquisition. During implementation, the operator selects this mode via user interface unit 700 based on clinical needs. The high-voltage switch controller triggers X-ray tube 112, and integrating detector 120 captures projection data in real time. This is particularly suitable for emergency scenarios, such as stroke screening in hospital emergency departments to quickly detect hemorrhage or infarction and provide preliminary diagnostic support.

[0081] Second, all detection modules are replaced with photon-counting detectors 120. During installation, the module's energy resolution circuitry is adjusted to match the data acquisition and processing unit 300, and multi-energy spectrum signals are transmitted via a fiber optic channel. In actual implementation, the system's main control unit 800 coordinates the high-voltage switch controller to switch X-ray emission at preset energy levels. This mode is commonly used for tumor classification examinations in oncology hospitals. Tumor tissue characteristics are identified by energy segmentation, and a dedicated calibration procedure is required to optimize energy segmentation performance.

[0082] Third and finally, a hybrid configuration of photon-counting and integrating detectors 120 is employed. The operator divides the detection modules into segments or regions. For example, the detection module in the left segment of the detector 120 is replaced with an integrating detector 120, and the detection modules in the middle and right segments are replaced with photon-counting detectors 120. After installation, the flexible connector on the carrier 600 ensures data synchronization between the detection modules. During implementation, the system triggers the detection modules in different segments based on the examination requirements. The integrating detector 120 rapidly collects initial data, while the photon-counting detector 120 further analyzes energy characteristics. This system is suitable for combined stroke diagnosis in neurology departments of general hospitals, allowing for rapid localization of bleeding areas and analysis of lesion energy characteristics. The data is then integrated and processed by the data acquisition and processing unit 300.

[0083] In addition to the above three detector 120 configuration schemes, the present invention can also support the introduction of other types of detectors 120, such as scintillation detectors 120. During implementation, the detection module needs to be replaced and the gain setting of the photoelectric conversion module needs to be adjusted. It is installed on the reserved interface of the carrier 600 and connected to the processing unit through a multi-channel data cable. This mode is often used in intraoperative real-time imaging applications, such as providing dynamic image support in neurosurgery. An additional shielding layer is required to enhance signal stability and anti-interference capabilities. All configuration changes are completed through the modular interface of the carrier 600. The data connection between the detection module and the data acquisition and processing unit 300 adopts a standardized plug-in method to ensure fast switching and the reliability of real-time data acquisition.

[0084] It should also be noted that the number of X-ray tubes 112 directly determines the projection density during static scanning. In high-precision medical imaging scenarios, this projection density sometimes fails to meet the requirements for full coverage. Therefore, the data acquisition and processing unit 300 of the static real-time CT imaging system of the present invention optimizes projection data through data processing. Specifically, an interpolation algorithm module is integrated within the data acquisition and processing unit 300. By mathematically interpolating the collected projection data, virtual projection points are generated to enhance data density.

[0085] Taking the three linear ray source segments 111 of this embodiment as an example, including the left linear ray source segment 111, the middle linear ray source segment 111, and the right linear ray source segment 111, the X-rays from the middle linear ray source segment 111 completely cover the object to be measured. However, due to geometric limitations, the left and right linear ray source segments 111 only cover a portion of the object to be measured, resulting in gaps in the projection data. Therefore, the data acquisition and processing unit 300 of the present invention uses an interpolation algorithm to fill in missing information between adjacent projection points, compensating for the limitations of the arrays on both sides and generating virtual projection points to enhance data density, support spectral imaging, and improve scanning efficiency. Compared to traditional methods, the present invention does not require an increase in the number of X-ray tubes 112, but instead achieves higher-density projection acquisition at the data level, effectively improving imaging quality.

[0086] The static real-time CT imaging system of the present invention can also realize a variety of multi-energy spectrum scanning modes, which can be achieved by the following steps, taking the three-segment X-ray source array of this embodiment as an example:

[0087] Each X-ray tube 112 in the first and third linear X-ray source segments 111 can dynamically adjust its output energy via a high-voltage switch controller, enabling rapid energy spectrum switching. The high-voltage switch controller of the present invention supports instantaneous switching between multiple preset energy levels, the number of which can be flexibly configured based on imaging requirements. After the X-ray tube 112 in the left linear X-ray source segment 111 completes a single energy spectrum scan under the control of the high-voltage switch controller, the high-voltage switch controller sequentially activates the X-ray tubes 112 in the middle linear X-ray source segment 111, sequentially switching to the same energy spectrum until the entire three-segment X-ray source array scan is complete.

[0088] The second and third linear ray source segments 111 both support a segmented energy rotation mode, that is, after all ray tubes 112 complete a full scan at the same energy level, the high-voltage switch controller uniformly adjusts the output energy of all ray tubes 112 to the next energy level, and repeats this process until all required energy levels are covered.

[0089] Third, the three linear ray source segments 111 can adopt a grouped multi-energy spectrum mode, and the ray tubes 112 in each linear ray source segment 111 are divided into different energy level groups. The high-voltage switch controller coordinates the simultaneous emission of each ray tube 112. After completing a scan, the high-voltage switch controller adjusts the energy level of each group to the next preset value, and the cycle is executed until all energy level scans are completed.

[0090] like Figure 9 and Figure 10As shown, the multi-segment X-ray source array 110 of the present invention is equipped with multiple tube holders 113 and multiple filters 114 for adjusting the X-ray spectrum. The X-ray tubes 112 are mounted on the carrier 600 via the tube holders 113. The high-voltage switch module 210 is fixed to the surface of the X-ray tubes 112, and the filters 114 are fixed to the X-ray tubes 112. The number of tube holders 113 and filters 114 corresponds to the number of X-ray tubes 112. The X-ray tubes 112 have a cylindrical housing that encapsulates the X-ray generating assembly. The tube holders 113 are fixed to the bottom of the housing to ensure stable installation and precise alignment of the tubes with the carrier 600. A high-voltage switch controller is mounted above the housing of the X-ray tubes 112 and connected to the high-voltage input port of the X-ray tubes 112 via a cable. It is responsible for real-time control of the tube power status. The focal points of all X-ray tubes 112 of the present invention are uniformly arranged in the same XY plane to achieve multi-angle projection of the object under test. Furthermore, the X-ray tube 112 of the present invention is constructed from a high-strength metal housing, and its inner wall is equipped with heat dissipation channels to ensure thermal stability during long-term operation. The high-voltage switch controller comprises a compact housing that integrates a microcontroller and solid-state switch module, capable of performing switching operations with millisecond response times. A status indicator light is located on the top of the controller for real-time monitoring. The tube bracket 113 is connected to the carrier 600 via a multi-point fixture. Fine-tuning screws are provided on the bracket 113, allowing for precise adjustment of the tube's tilt angle and spacing during installation.

[0091] It should be noted that the scanning device 100 of the present invention integrates multiple linear X-ray source segments 111 and detectors 120. The multi-segment X-ray source array 110 is distributed along the inner wall of the carrier 600 to achieve multi-angle projection coverage. Multiple X-ray tubes 112 are fixed within the scanning device 100 and securely mounted by tube holders 113. Furthermore, the focal points of the multi-segment X-ray source array 110 of the present invention are located at the center of the base of an isosceles trapezoid with a base angle of 60° relative to the scanning center, providing a total coverage of 180°. The X-ray beams generated by the tubes 112 are projected toward the center from the tubes 112 of each linear X-ray source segment 111. Through coordinated control by a high-voltage switch controller, each tube 112 emits X-ray beams sequentially or synchronously, achieving efficient multi-directional projection acquisition during static scanning. Furthermore, the scanning device 100 of the present invention employs a modular structure, supporting independent adjustment and optimization of the multi-segment X-ray source array 110 and the detection modules in the detector 120.

[0092] To optimize projection performance, the distributed design of the multi-segment X-ray source array 110 in this invention prioritizes inter-segment connectivity and overall coverage. The X-ray tubes 112 within each linear X-ray source segment 111 are secured by a tube holder 113, which is also equipped with an adjustable clamping device, enabling fine-tuning of the spacing between the tubes 112 to accommodate varying field of view requirements. Flexible interfaces are used to connect the scanning device 100, ensuring seamless transitions within the multi-segment X-ray source array 110 within a 180° range. A high-voltage switch controller connects to the tubes 112 via a cable, controlling their emission timing and supporting either segmented sequential or synchronous modes, enabling flexible scanning strategies. The entire system eliminates the need for circular splicing; the linear distribution of the segmented X-ray source array can meet wide field of view imaging requirements. In practical applications, the configuration of the multi-segment X-ray source array 110 is highly adaptable. The scanning device 100 supports modular expansion, allowing the number of tubes 112 within each linear X-ray source segment 111 to be increased or decreased based on imaging accuracy. The centrally focused X-ray beam design, combined with the precise timing control of the high-voltage switch controller, ensures the integrity and consistency of projection data. It is particularly suitable for high-resolution medical imaging and industrial inspection scenarios, significantly improving the performance of static CT systems.

[0093] like Figures 6 to 8 In the static real-time CT imaging system of the present invention, a multi-segment X-ray source array 110 achieves efficient data acquisition through independent projection acquisition in collaboration with the curved detector 120 modules. In this embodiment, the detection modules in the detector 120 are divided into three groups, each corresponding to a linear X-ray source segment 111. Projection data corresponding to each linear X-ray source segment 111 is captured and temporarily stored by an independent set of detector 120 modules. The number of modules can be configured as needed. The three detection groups contain multiple detection modules, collectively covering a 180° scanning range. After acquisition by the data acquisition and processing unit 300, the stored data is uniformly transmitted via parallel data readout channels for subsequent reconstruction processing.

[0094] like Figure 11 , the data acquisition and processing unit 300 first performs interpolation operations on the three sets of projection data to enhance the uniformity of projection density and make up for the sampling gap. The interpolation process uses an algorithm to fill in the information between adjacent projection points, optimize data integrity, and lay the foundation for subsequent reconstruction. The processed data then enters the FBP reconstruction module, which uses filtered back projection technology to generate three-dimensional block data. This module is equipped with high-performance computing resources (such as multi-core CPU or GPU) to ensure that the reconstruction process is fast and efficient and meets the display requirements of real-time imaging. The reconstruction results are transmitted to the data storage unit 500 via a high-speed interface for storage and visualization.

[0095] The data acquisition process is coordinated by the system's main control unit 800. The high-voltage switch controller triggers the emission of the X-ray tube array 112 of the multi-segment X-ray source array 110 according to a preset timing, synchronously driving the three groups of detection modules for projection capture. Each detection group temporarily stores data in an independent buffer to ensure the synchronization and consistency of acquisition. During the data readout phase, the stored contents of the three detection groups are centrally transmitted to the data acquisition and processing unit 300 via a multi-channel fiber optic link to avoid data loss or delay. Before interpolation processing, the system will perform preliminary corrections on each set of data, including brightness balancing and geometric alignment, to improve reconstruction accuracy. To adapt to different imaging tasks, the data processing flow supports flexible configuration. The interpolation algorithm can adjust parameters according to the projection density requirements, and the FBP reconstruction module allows the optimization of the filter function to balance resolution and noise. This strategy of segmented acquisition and centralized reconstruction is particularly suitable for large-field static imaging, significantly improving image quality and processing efficiency. Compared to traditional multi-slice spiral CT systems that rely on the high-speed rotation of the X-ray tube 112 and transmit data via slip rings or wirelessly, the static real-time CT imaging system of the present invention adopts a fixed design, with a stable structure achieved through the main bearing and CT scanning assembly, eliminating the need for any mechanical movement. Data transmission relies on a high-speed fiber optic network for parallel transmission, significantly improving data throughput and transmission stability. Thanks to the characteristics of static scanning, the system eliminates artifacts caused by motion, and the overall architecture is more simple and reliable, ensuring the efficiency and data consistency of the subsequent three-dimensional reconstruction process. The system of the present invention collects three parts of projection data and first integrates them into a complete data set within the processing unit. Then, an interpolation algorithm is used to optimize the projection point density to ensure the continuity and accuracy of the data distribution. After interpolation, the data enters the reconstruction core module, which uses filtered back projection (FBP) technology to generate three-dimensional stereoscopic microscopic images. The reconstructed stereoscopic data is transmitted to the display system, supporting multi-dimensional image presentation and meeting the dynamic observation requirements of various clinical or industrial scenarios. The entire reconstruction process is efficient and smooth, and the image generation speed can support real-time interactive analysis, significantly enhancing the practical value of the system in high-precision detection.

[0096] The beneficial effects of the multi-segment linear array X-ray source static real-time CT imaging system are as follows: 1. The multi-segment X-ray source array 110 of the present invention can freely adjust the entire length and angle of the segment to achieve a larger lateral range than the circular array, which is suitable for large-sized objects to be measured. The present invention can improve the coverage and quality of large-field imaging through the multi-segment X-ray tube 112 array; 2. The circular array of the prior art requires more X-ray sources to achieve a certain field of view, while the multi-segment X-ray source array 110 of the present invention can use fewer X-ray sources to achieve the same wide field of view; and the circular array is limited by the radius, making it difficult to achieve a relatively wider field of view. range, the multi-segment X-ray source array 110 of the present invention is more flexible in design and easier to expand; 3. The ray source distribution of the multi-segment X-ray source array 110 can be relatively dispersed, with less intersection of ray paths, and the interference of scattered signals will be significantly reduced; 4. The ray source control unit 200 can control the exposure strategy of the scanning device 100, flexibly control the emission of X-rays from different areas in the multi-segment X-ray source array 110, control the exposure order, range, and energy of X-rays, thereby optimizing the radiation dose utilization rate and reducing radiation exposure in non-target areas, which is particularly suitable for high-precision medical imaging scenarios such as stroke. 5. The integrating detector 120 in the detection module of the present invention meets the needs of rapid routine inspections, and the photon counting detector 120 supports multi-energy spectrum analysis, so the present invention has strong flexibility.

[0097] Example 2

[0098] An imaging method is performed using the multi-segment linear array X-ray source static real-time CT imaging system of Example 1.

[0099] The high-voltage switch controller controls the three-segment X-ray source array to emit X-rays in a time-sequential exposure manner, and dynamically adjusts the output energy of each ray tube 112 in the three-segment X-ray source array to achieve multi-energy spectrum scanning.

[0100] The detector 120 collects projection data of X-rays after passing through the object to be measured; and simultaneously completes data collection at different energy levels step by step.

[0101] The data acquisition and processing unit 300 acquires projection data, then performs interpolation enhancement operations, processes the projection data by filling in information between adjacent projection points through an algorithm, performs image reconstruction in real time to obtain image data, and then saves the image data to the data storage unit 500.

[0102] The imaging method has the following beneficial effects: 1. The multi-segment X-ray source array 110 of the present invention can freely adjust the length and angle of the entire segment, achieving a larger lateral range than a circular array, and is suitable for large-sized objects to be measured. The present invention can improve the coverage and quality of large-field imaging through the multi-segment X-ray tube 112 array; 2. The circular array of the prior art requires more X-ray sources to achieve a certain field of view, while the multi-segment X-ray source array 110 of the present invention can use fewer X-ray sources to achieve the same wide field of view; and the circular array is limited by the radius and it is difficult to achieve a relatively wider range. The present invention 1. The multi-segment X-ray source array 110 is more flexible in design and easier to expand; 2. The ray source distribution of the multi-segment X-ray source array 110 can be relatively dispersed, with less intersection of ray paths, and the interference of scattered signals will be significantly reduced; 3. The ray source control unit 200 can control the exposure strategy of the scanning device 100, flexibly control the emission of X-rays from different areas in the multi-segment X-ray source array 110, control the exposure order, range, and energy of X-rays, thereby optimizing the utilization rate of radiation dose and reducing radiation exposure in non-target areas, which is particularly suitable for high-precision medical imaging scenarios such as stroke. 4. The integral detector 120 in the detection module of the present invention meets the needs of rapid routine inspections, and the photon counting detector 120 supports multi-energy spectrum analysis, so the present invention has strong flexibility.

[0103] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit the scope of protection of the present invention. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that the technical solutions of the present invention may be modified or replaced by equivalents without departing from the essence and scope of the technical solutions of the present invention.

Claims

1. A multi-segment linear array X-ray source static real-time CT imaging system, characterized by: The settings are: Scanning device - generates projection data by emitting X-rays so that the X-rays pass through the object to be measured; A ray source control unit controls the scanning device to emit X-rays in a timed sequence through a timed exposure mode to control the exposure sequence and exposure range, and can also control the energy of the X-rays; The scanning device is provided with a multi-segment X-ray source array and a detector, the emission end of the multi-segment X-ray source array is directed toward the detector, and the multi-segment X-ray source array is connected to the ray source control unit; The multi-segment X-ray source array is composed of more than three linear ray source segments, and all the linear ray source segments are connected end to end from front to back.

2. The multi-segment linear array X-ray source static real-time CT imaging system according to claim 1, characterized in that: Each linear ray source section is provided with a plurality of mutually independent ray tubes, and the ray tubes in the same linear ray source section are arranged linearly; The ray source control unit is provided with a high-voltage switch controller for independently controlling each ray tube switch. The high-voltage switch controller is provided with multiple high-voltage switch modules, and each ray tube is connected to one high-voltage switch module.

3. The multi-segment linear array X-ray source static real-time CT imaging system according to claim 2, characterized in that: Also provided are: Data acquisition and processing unit - collects projection data from the detection module in the detector; then performs interpolation and enhancement operations on the projection data, fills in the information between adjacent projection points through an algorithm, optimizes data sampling density, and obtains image data; Data storage unit - storing the image data of the data acquisition and processing unit; Carrier: used to fix the scanning device; User interaction unit - for inputting clinical parameters; System main control unit - generates a corresponding coding scheme based on the clinical parameters input by the user interaction unit and according to the built-in algorithm, transmits the coding instructions to the high-voltage switch controller, and controls the data acquisition and processing unit to work; The multi-segment X-ray source array is provided with a plurality of tube holders and a plurality of filters for adjusting the X-ray spectrum. The X-ray tubes are assembled on the carrier frame through the tube holders. The high-voltage switch module is fixed to the surface of the X-ray tubes. The filters are fixed to the X-ray tubes. The number of the tube supports and the number of the filters correspond to the number of the ray tubes.

4. The multi-segment linear array X-ray source static real-time CT imaging system according to claim 2, characterized in that: The linear ray source segment is provided with three segments, and the three linear ray source segments are respectively defined as a left linear ray source segment, a middle linear ray source segment and a right linear ray source segment; The rear end of the left linear ray source segment is connected to the front end of the middle linear ray source segment, the rear end of the middle linear ray source segment is connected to the front end of the right linear ray source segment, the front end of the left linear ray source segment is connected to the detector, and the rear end of the right linear ray source segment is connected to the detector.

5. The multi-segment linear array X-ray source static real-time CT imaging system according to claim 4, characterized in that: A front end of the left linear ray source segment and a rear end of the right linear ray source segment are connected by a virtual straight line, and the left linear ray source segment, the middle linear ray source segment, the right linear ray source segment and the virtual straight line form an isosceles trapezoid.

6. The multi-segment linear array X-ray source static real-time CT imaging system according to claim 5, characterized in that: The base angle of the isosceles trapezoid is 60°.

7. The multi-segment linear array X-ray source static real-time CT imaging system according to claim 1, characterized in that: The detector is an arc-shaped detector; The detector is composed of a plurality of detachable detection modules, and the plurality of detection modules are sequentially spliced from front to back to form the arc-shaped detector.

8. The multi-segment linear array X-ray source static real-time CT imaging system according to claim 7, characterized in that: The detection module is at least one of a photon counting detector and an integrating detector; The sequential exposure mode is a segmented exposure mode or a synchronous pulse mode.

9. An imaging method, characterized in that: The method is carried out using the multi-segment linear array X-ray source static real-time CT imaging system as described in any one of claims 3 to 8.

10. The imaging method according to claim 9, wherein: The high-voltage switch controller controls the three-segment X-ray source array to emit X-rays in a time-sequential exposure manner, and dynamically adjusts the output energy of each ray tube in the three-segment X-ray source array to achieve multi-energy spectrum scanning; The detector collects projection data of X-rays after passing through the object to be measured; and simultaneously and sequentially completes data collection at different energy levels; The data acquisition and processing unit acquires the projection data, then performs an interpolation enhancement operation, processes the projection data by filling in information between adjacent projection points through an algorithm, performs image reconstruction in real time to obtain image data, and then saves the image data to the data storage unit.

Images