CT scanning system and CT scanning data processing method

Abstract

The application relates to the technical field of CT scanning, and particularly discloses a CT scanning system and a CT scanning data processing method. The system comprises a first ray generating device, a second ray generating device and a shared detection device. The first ray generating device is used for generating a first ray beam, and the first ray beam has a first energy. The second ray generating device is used for generating a second ray beam, and the second ray beam has a second energy. The second energy is greater than the first energy. The shared detection device is arranged in the ray beam emission direction of the first ray generating device and the second ray generating device, used for receiving the first ray beam and the second ray beam, and generating first projection data of the first ray beam and second projection data of the second ray beam. A scanning area is arranged between the first ray generating device, the second ray generating device and the shared detection device, and the first ray generating device and the second ray generating device are arranged at intervals along the direction of longitudinally penetrating the scanning area. The cost is low, and the method is easy to implement.

Description

Technical Field

[0001] The present invention relates to the technical field of CT scanning, and in particular to a CT scanning system and a CT scanning data processing method. Background Art

[0002] Compared to single-energy CT imaging, dual-energy CT can achieve higher material detection accuracy. With the development of CT scanning technology, a variety of methods have emerged to achieve dual-energy CT scanning imaging, such as single-source CT systems that perform two consecutive scans at different energy states, or single-source CT systems that are configured with two independent detection systems, or single-source CT systems that can rapidly switch between high-energy and low-energy states.

[0003] However, each of these implementations presents challenges, such as high system configuration requirements, the high cost of two independent detection systems, the extensive and complex calibration required before scanning to ensure the two detection systems are configured identically, and the subsequent complexity of processing the projection data. Therefore, reducing the cost of dual-energy CT scanning and simplifying its implementation are pressing technical challenges in this field. Summary of the Invention

[0004] Based on this, it is necessary to provide a CT scanning system and a CT scanning data processing method to solve the problem of how to reduce the cost of dual-energy CT scanning imaging and simplify the implementation of dual-energy CT scanning imaging.

[0005] A CT scanning system, comprising:

[0006] A first ray generating device, configured to generate a first ray beam, wherein the first ray beam has a first energy;

[0007] A second ray generating device is used to generate a second ray beam, wherein the second ray beam has a second energy, and the second energy is greater than the first energy;

[0008] a common detection device, disposed in an emission direction of the ray beams of the first ray generating device and the second ray generating device, for receiving the first ray beam and the second ray beam, and generating first projection data of the first ray beam and second projection data of the second ray beam;

[0009] A scanning area is provided between the first ray generating device, the second ray generating device and the common detection device, and the first ray generating device and the second ray generating device are spaced apart along a direction vertically passing through the scanning area.

[0010] In one embodiment, a first projection area of ​​the first ray beam on the common detection device and a second projection area of ​​the second ray beam on the common detection device have an overlapping area.

[0011] In one embodiment, the area of ​​the overlapping region is greater than or equal to one half of the area of ​​the first projection region and smaller than the area of ​​the first projection region;

[0012] Or the area of ​​the overlapping region is greater than or equal to half of the area of ​​the second projection region, and smaller than the area of ​​the second projection region.

[0013] In one embodiment, a first projection area of ​​the first ray beam on the common detection device is close to but does not overlap with a second projection area of ​​the second ray beam on the common detection device.

[0014] In one embodiment, the shared detection device includes an array detector panel, and the array detector panel is a single-layer structure or a double-layer structure.

[0015] In one embodiment, the distance between the first ray generating device and the second ray generating device is:

[0016] L=nd

[0017] Wherein, L represents the distance between the first ray generating device and the second ray generating device, d represents the distance between two adjacent detectors in the direction of the longitudinal scanning area, and n represents a positive integer.

[0018] In one embodiment, the CT scanning system further includes a rotating mechanism, the first ray generating device and the second ray generating device are arranged in a first position area of ​​the rotating mechanism, the common detection device is arranged in a second position area of ​​the rotating mechanism, the second position area is opposite to the first position area, and a hollow scanning area is arranged between the first position area and the second position area.

[0019] In one embodiment, the CT scanning system further includes a transport mechanism, which is used to transport the object to be scanned into and out of the scanning area along a direction longitudinal to the scanning area.

[0020] In one embodiment, the CT scanning system further includes a data processing device, which is connected to the common detection device and is configured to process the first projection data and the second projection data to obtain a scanning result.

[0021] A CT scan data processing method is applied to the above-mentioned CT scanning system; the CT scan data processing method comprises:

[0022] determining a relative position difference between the first ray generating device and the second ray generating device in a direction longitudinally across the scanning area;

[0023] acquiring the first projection data and the second projection data;

[0024] performing alignment adjustment on the first projection data and the second projection data based on the relative position difference to obtain equivalent projection data;

[0025] Material detection is performed based on the equivalent projection data.

[0026] A computer-readable storage medium stores computer instructions, which, when executed by a processor, implement the above-mentioned CT scan data processing method.

[0027] The CT scanning system comprises two radiation generating devices and a shared detection device. The two radiation generating devices are respectively configured to generate radiation beams of different energy states (a first radiation beam and a second radiation beam). The shared detection device is configured to simultaneously receive the first and second radiation beams and generate first projection data corresponding to the first radiation beam and second projection data corresponding to the second radiation beam for subsequent processing to achieve material identification. The two radiation generating devices are spaced apart along a direction longitudinally extending across the scanning area between the radiation generating devices and the shared detection device.

[0028] The two ray generating devices share a single detection device, saving costs compared to using two independent detection systems. This eliminates the need for extensive and complex configuration and calibration work, thus avoiding the problem of low detection accuracy due to calibration errors. Furthermore, because the positional difference between the first and second ray generating devices exists only in the direction longitudinally across the scanning area, the deviation between the first and second projection data primarily occurs in the direction longitudinally across the scanning area. Therefore, subsequent data processing only requires alignment of the first and second projection data based on the positional difference between the first and second ray generating devices. This effectively simplifies the data alignment process, facilitating implementation while maintaining the accuracy of subsequent data processing. BRIEF DESCRIPTION OF THE DRAWINGS

[0029] Figure 1 This is a schematic structural diagram of an implementation of a CT scanning system provided in Example 1 of the present application;

[0030] Figure 2 This is a schematic structural diagram of another embodiment of the CT scanning system provided in Example 1 of the present application;

[0031] Figure 3This is a schematic structural diagram of a specific example of the CT scanning system provided in Example 1 of the present application;

[0032] Figure 4 This is a flowchart of the CT scan data processing method provided in Example 2 of the present application;

[0033] Figure 5 This is a flowchart of step S300 in the CT scan data processing method provided in Example 2 of the present application;

[0034] Figure 6 This is a schematic diagram of the structure of the electronic device provided in Example 3 of the present application.

[0035] Explanation of the reference numerals: 10, first ray generating device; 20, second ray generating device; 30, shared detection device; 40, scanning area; 100, memory; 200, processor. DETAILED DESCRIPTION

[0036] To facilitate understanding of the present invention, the present invention will be described more fully below with reference to the accompanying drawings. Preferred embodiments of the present invention are shown in the accompanying drawings. However, the present invention may be implemented in many different forms and is not limited to the embodiments described herein. Rather, these embodiments are provided to provide a more thorough and comprehensive understanding of the present disclosure.

[0037] In the present invention, unless otherwise specified or limited, the terms "installed," "connected," "connect," "fixed," etc. should be understood in a broad sense. For example, they can refer to fixed connection, detachable connection, or integration; mechanical connection, electrical connection; direct connection, or indirect connection through an intermediate medium; internal communication between two components, or interaction between two components, unless otherwise specified. Those skilled in the art will understand the specific meanings of the above terms in the present invention based on specific circumstances.

[0038] The terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of the technical features being referred to. Thus, a feature specified as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present invention, "plurality" means at least two, for example, two, three, etc., unless otherwise specifically defined.

[0039] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by those skilled in the art to which this invention pertains. The terms used in this specification of the present invention are for the purpose of describing specific embodiments only and are not intended to limit the present invention. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0040] CT (Computed Tomography), also known as electronic computer tomography, uses a precisely collimated beam of radiation and a highly sensitive detector to perform cross-sectional scanning and imaging around the object to be scanned. CT scanning can be divided into single-energy and dual-energy. Single-energy CT scanning uses a beam of radiation of one energy to scan and image the object to be scanned. It can only reconstruct the effective linear attenuation coefficient of the fault, while dual-energy CT scanning uses two beams of radiation of different energies to scan and image the object to be scanned. It can reconstruct the atomic number and electron density of the material, obtain the composition ratio of the material, and achieve the effect of material identification. Therefore, dual-energy CT scanning technology has been widely used in various fields of CT scanning and imaging technology (such as security inspection and medical fields).

[0041] Currently, there are many methods for achieving dual-energy CT scanning imaging. These include configuring two independent detection systems for separate scanning; and using a single-source CT scanning method to quickly switch between high-energy and low-energy states to achieve dual-energy CT scanning. For the first method, due to the use of two independent detection systems (each detection system includes a radiation source and a detector), the cost is relatively high, and the two detection systems need to be calibrated separately before scanning to ensure that their physical properties remain consistent, which is conducive to subsequent data processing. The preparation work for the calibration is relatively complicated. Once an error occurs in the calibration, it will inevitably affect the subsequent data processing results. In addition, the difficulty of subsequent data processing is also relatively high. For the second method, in order to achieve rapid switching between high and low energy, the requirements for the internal configuration of the radiation source are high, there are certain technical bottlenecks, and it is relatively difficult.

[0042] In response to the above problems, the present application provides a CT scanning system and a CT scanning data processing method.

[0043] Example 1

[0044] This embodiment provides a CT scanning system for use in security inspection, medical and other fields.

[0045] Reference Figure 1 and Figure 2 The CT scanning system provided in this embodiment includes a first ray generating device 10 , a second ray generating device 20 and a shared detection device 30 .

[0046] The first ray generating device 10 is used to generate a first ray beam, and the first ray beam has a first energy;

[0047] The second ray generating device 20 is used to generate a second ray beam, the second ray beam has a second energy, and the second energy is greater than the first energy;

[0048] The common detection device 30 is arranged in the ray beam emission direction of the first ray generating device 10 and the second ray generating device 20, and is used to receive the first ray beam and the second ray beam, and generate first projection data of the first ray beam and second projection data of the second ray beam;

[0049] A scanning area 40 is provided between the first ray generating device 10 , the second ray generating device 20 and the common detection device 30 . The first ray generating device 10 and the second ray generating device 20 are spaced apart along a direction vertically passing through the scanning area 40 .

[0050] The CT scanning system comprises two radiation generating devices (a first radiation generating device 10 and a second radiation generating device 20) and a shared detection device 30. The two radiation generating devices are respectively configured to generate radiation beams of different energy states (a first radiation beam and a second radiation beam). The shared detection device 30 receives both the first and second radiation beams and generates first projection data corresponding to the first radiation beam and second projection data corresponding to the second radiation beam for subsequent processing to achieve material identification. The two radiation generating devices are spaced apart along a direction extending longitudinally across a scanning area 40 between the radiation generating devices and the shared detection device 30.

[0051] Because the two ray generating devices share a detection device, compared to using two independent detection systems, the structure is simplified, costs are saved, the utilization rate of the detection panel is improved, and a large amount of complex configuration and calibration work is not required, thereby avoiding the problem of low detection accuracy due to calibration errors. At the same time, because the position difference between the first ray generating device 10 and the second ray generating device 20 only exists in the direction longitudinally extending the scanning area 40, that is, the first projection data and the second projection data mainly have deviations in the direction longitudinally extending the scanning area 40, in the subsequent data processing process, it is only necessary to align the first projection data and the second projection data based on the position difference between the first ray generating device 10 and the second ray generating device 20. This effectively simplifies the data alignment process, facilitates implementation, and does not affect the accuracy of subsequent data processing.

[0052] The first ray generating device 10 and the second ray generating device 20 may be any one of an X-ray accelerator, an X-ray machine, an isotope source, and the like.

[0053] In this embodiment, the second energy is greater than the first energy. The first energy can be defined as low energy and the second energy as high energy. For example, the first energy of the first beam is 80 KeV, and the second energy of the second beam is 160 KeV. In practical applications, the first energy and the second energy can be set according to actual needs to meet different scanning requirements. The first beam and the second beam are generally conical beams, and the cone angles of the two beams can be consistent or inconsistent. In this embodiment, the cone angles of the first beam and the second beam are preferably set to be consistent.

[0054] The shared detection device 30 should be able to receive all of the first and second beams, that is, all of the first and second beams should be projected onto the shared detection device 30, and generate first projection data of the first beam on the shared detection device 30, and second projection data of the second beam on the shared detection device 30. By processing and analyzing the first and second projection data, the substance can be identified.

[0055] As a preferred manner, in actual application, the projection point of the center position of the line connecting the first ray generating device 10 and the second ray generating device 20 on the common detection device 30 coincides with the center point of the common detection device 30 .

[0056] There is a common scanning area 40 between the first ray generating device 10 and the common detection device 30, and between the second ray generating device 20 and the common detection device 30. The scanning area 40 is used to place the object to be scanned. The first ray beam and the second ray beam penetrate the object to be scanned and then are projected onto the common detection device 30. The object to be scanned can be translated within the scanning area 40, thereby enabling scanning of any position of the object to be scanned.

[0057] In this embodiment, the direction of the longitudinal scanning area 40 is the translation direction of the object to be scanned. When the first ray generating device 10 and the second ray generating device 20 are spaced apart along the direction of the longitudinal scanning area 40, assuming that the direction of the longitudinal scanning area 40 is the Z axis, then the first ray generating device 10 and the second ray generating device 20 are in a parallel position relationship on the XY plane, and the relative position difference between the two is only on the Z axis. In other words, the first ray beam and the second ray beam only have an optical path deviation on the Z axis. When the first ray beam and the second ray beam that penetrate the object to be scanned are projected onto the shared detection device 30, the generated first projection data and the second projection data also only have a deviation in the Z axis direction. Therefore, when processing the projection data, only simple internal calculations are required to achieve data alignment. During subsequent data reconstruction, the reconstruction area range is stable and unrestricted, which is conducive to equivalently producing the maximum reconstruction area. Even in actual applications, even if there is a slight deviation in the X and Y axis directions due to errors, it is not necessary to consume a large amount of internal calculations, and the overall data processing process is relatively simple.

[0058] In one embodiment, referring to Figure 1 , the first projection area of ​​the first beam of rays on the common detection device 30 and the second projection area of ​​the second beam of rays on the common detection device 30 have an overlapping area. That is to say, there is a certain cross-overlap between the first beam of rays and the second beam of rays, so that there is an overlapping area in the projection areas of the two on the common detection device 30. In practical applications, the first projection area and the second projection area can be overlapped by reducing the spacing distance between the first ray generating device 10 and the second ray generating device 20, or by adjusting the projection direction of the first ray generating device 10 and the second ray generating device 20 or the cone angle of the beam, etc. In this embodiment, it is preferred to overlap the first projection area and the second projection area by reducing the spacing distance between the first ray generating device 10 and the second ray generating device 20. When setting the spacing distance between the first ray generating device 10 and the second ray generating device 20, it should not be too close to cause interference and other adverse problems.

[0059] Since the first projection area and the second projection area have an overlapping area, the demand for the shared detection panel area can be appropriately reduced. A smaller detection panel can meet the demand of receiving all the first and second ray beams, which can effectively reduce the cost of the CT scanning system.

[0060] As a preferred embodiment, the area of ​​the overlapping region is greater than or equal to half of the area of ​​the first projection region and smaller than the area of ​​the first projection region; or the area of ​​the overlapping region is greater than or equal to half of the area of ​​the second projection region and smaller than the area of ​​the second projection region.

[0061] Specifically, the overlapping area can be one-half, two-thirds, or four-fifths of the area of ​​the first projection area, or one-half, two-thirds, or four-fifths of the area of ​​the second projection area. The larger the overlapping area, the smaller the area required for the shared detection panel, and the greater the cost savings of the detection panel.

[0062] As an alternative embodiment, refer to Figure 2 , the first projection area of ​​the first ray beam on the shared detection device 30 and the second projection area of ​​the second ray beam on the shared detection device 30 are close to each other but do not overlap. That is, the first projection area and the second projection area may not overlap, and the edges of the first projection area and the second projection area may be close to each other. In this configuration, the distance between the first ray generating device 10 and the second ray generating device 20 is relatively far. This configuration can also achieve the objectives of this application and falls within the scope of protection of this application.

[0063] In one embodiment, the shared detection device 30 includes an array detector panel, which can be a single-layer or double-layer structure. The array detector panel is composed of detectors arranged in an array. In practical applications, a single-layer array detector panel can be used to implement dual-energy CT scanning, while a double-layer array detector panel can be used to implement quad-energy CT scanning. The double-layer array detector panel is also known in the art as a sandwich detector panel.

[0064] In one embodiment, the distance between the first ray generating device 10 and the second ray generating device 20 is:

[0065] L=nd

[0066] Wherein, L represents the spacing between the first ray generating device 10 and the second ray generating device 20 , d represents the spacing between two adjacent detectors in the direction of the longitudinal scanning area 40 , and n represents a positive integer.

[0067] In this embodiment, the spacing distance between the first ray generating device 10 and the second ray generating device 20 is set to an integer multiple of the spacing distance between two adjacent detectors in the direction of the longitudinal scanning area 40. If the physical structure is precise enough, the alignment of the projection data only needs to be achieved by data translation, which is convenient and fast, and does not require additional interpolation calculations to waste computing power. The data itself is still the original data, so that the subsequent data alignment of the first projection data and the second projection data can be faster and more accurate.

[0068] In one embodiment, the CT scanning system further includes a rotating mechanism, wherein the first ray generating device 10 and the second ray generating device 20 are disposed in a first position region of the rotating mechanism, and the shared detection device 30 is disposed in a second position region of the rotating mechanism, the second position region being opposite the first position region, and a hollow scanning region 40 is disposed between the first and second position regions. In actual application, the object to be scanned is placed in the hollow scanning region 40, and the rotation of the rotating mechanism can drive the rotation of the first ray generating device 10, the second ray generating device 20, and the shared detection device 30, thereby achieving multi-angle scanning of the object to be scanned.

[0069] Among them, reference Figure 3 The rotating mechanism can be a hollow cylindrical structure. The first ray generating device 10 and the second ray generating device 20 are disposed in an area on one side of the cylindrical structure, and the shared detection device 30 is disposed in an area on the other side of the cylindrical structure. The first ray generating device 10 and the second ray generating device 20 are opposite to the shared detection device 30. The hollow area of ​​the cylindrical structure is the scanning area 40 that accommodates the object to be scanned. The axial direction of the cylindrical structure is the direction that runs longitudinally through the scanning area 40. That is, the first ray generating device 10 and the second ray generating device 20 are spaced apart along the axial direction of the cylindrical structure.

[0070] In one embodiment, the CT scanning system further includes a conveying mechanism for conveying the object to be scanned into and out of the scanning region 40 in a direction longitudinally extending through the scanning region 40. The conveying mechanism may include a conveyor belt and a drive motor. Under the driving force of the drive motor, the conveyor belt conveys the object to be scanned into and out of the scanning region 40 in a direction longitudinally extending through the scanning region 40.

[0071] In one embodiment, the CT scanning system further includes a data processing device, which is connected to the shared detection device 30 and is used to process the first projection data and the second projection data to obtain a scanning result. In this embodiment, before obtaining the first projection data and the second projection data, the data processing module first determines the relative position difference between the first ray generating device 10 and the second ray generating device 20 in the direction of the longitudinal scanning area 40 through a calibration template and a geometric correction algorithm. After obtaining the first projection data and the second projection data, the first projection data and the second projection data are aligned and adjusted according to the relative position difference, thereby obtaining equivalent projection data. Finally, material detection is performed based on the equivalent projection data. The material detection process is to perform double-effect decomposition and three-dimensional reconstruction on the equivalent projection data, thereby calculating the atomic number and electron cloud density, determining the material composition ratio of the object to be scanned, and realizing material identification.

[0072] It should also be noted that, in this embodiment, the number of the first ray generating device 10 and the second ray generating device 20 can both be set to one. When one of the ray generating devices is damaged, it can be downgraded and switched to single-source use, that is, the switching between the first energy and the second energy can be achieved through one ray generating device. This can be achieved by simply setting the ray generating device, which helps to ensure the continuous and stable operation of the CT scanning system.

[0073] Of course, the number of the first ray generating device 10 and the second ray generating device 20 may be more than one, which can be set according to actual needs and is not an absolute limitation here.

[0074] Example 2

[0075] This embodiment provides a CT scan data processing method, which is applied to the CT scanning system provided in Example 1. For details about the CT scanning system, please refer to the corresponding description in Example 1 and will not be repeated here.

[0076] Reference Figure 4 The CT scan data processing method provided in this embodiment includes the following steps:

[0077] Step S100 : determining the relative position difference between the first ray generating device 10 and the second ray generating device 20 in a direction vertically crossing the scanning area 40 .

[0078] Step S200: Acquire first projection data and second projection data.

[0079] Step S300 : aligning and adjusting the first projection data and the second projection data based on the relative position difference to obtain equivalent projection data.

[0080] Step S400: Perform material detection based on equivalent projection data.

[0081] Since the first ray generating device 10 and the second ray generating device 20 only have a relative position difference in the direction longitudinally crossing the scanning area 40, the first ray beam emitted by the first ray generating device 10 and the second ray beam emitted by the second ray generating device 20 also only have a position deviation in the direction longitudinally crossing the scanning area 40 on the optical path. When the first ray beam and the second ray beam that penetrate the object to be scanned are projected onto the common detection device 30, the generated first projection data and the second projection data also only have a deviation in the direction longitudinally crossing the scanning area 40. When processing the projection data, it is only necessary to first determine the relative position difference between the first ray generating device 10 and the second ray generating device 20 in the direction longitudinally crossing the scanning area 40, and then align and adjust the first projection data and the second projection data based on the relative position difference to obtain equivalent projection data, and then perform material identification based on the equivalent projection data. This effectively simplifies the data alignment process and the entire data processing process, eliminates the need for complex internal calculations, facilitates implementation, and also ensures the accuracy of material identification.

[0082] In step S100, the first ray generating device 10 and the second ray generating device 20 can be exposed separately using a calibration template and a geometric correction algorithm, thereby determining the relative position difference between the first ray generating device 10 and the second ray generating device 20 in the direction longitudinally across the scanning area 40. Assume that the determined relative position difference is (α, β, γ), where α, β, and γ are position deviations in the X-axis, Y-axis, and Z-axis directions, respectively. Assume that the direction longitudinally across the scanning area 40 is the Z-axis direction. Since the first ray generating device 10 and the second ray generating device 20 only have a position difference in the Z-axis direction, that is, the two are in a parallel positional relationship in the X-axis-Y-axis plane, that is, both α and β are 0. Of course, errors in actual applications are not ruled out, and α and β may not be 0, but the errors are small.

[0083] When there is no overlapping area between the first projection area and the second projection area, there is no need to consider the response interval of the common detection device 30, that is, in actual application, the first ray generating device 10 and the second ray generating device 20 can be controlled to emit ray beams at the same time, thereby obtaining the first projection data of the first ray beam on the common detection device 30 and the second projection data of the second ray beam on the common detection device 30.

[0084] When an overlapping area is set between the first projection area and the second projection area, since the projection areas are shared, the response interval of the shared detection device 30 needs to be considered. In practical applications, the first ray generating device 10 and the second ray generating device 20 need to be controlled to emit ray beams in sequence to avoid interference.

[0085] In one embodiment, referring to Figure 5 , step S300 may further include:

[0086] Step S310: rearrange the first projection data and the second projection data to form a pseudo-parallel beam;

[0087] Step S320 : performing alignment adjustment on the pseudo-parallel beam based on the relative position difference.

[0088] Specifically, the pseudo-parallel beams can be translated or aligned by interpolation according to the relative position difference, thereby generating equivalent projection data required for subsequent material identification, namely, equivalent projection data.

[0089] The following formula is the position correspondence between the first projection data and the second projection data:

[0090] I(x1,y1,z1)=I(x2+α,y2+β,z2+γ)

[0091] Wherein, I represents projection data, (x1, y1, z1) represents the position of the first projection data, (x2, y2, z2) represents the position of the second projection data, and (α, β, γ) represents the relative position difference.

[0092] In one embodiment, step S400 may further include performing double-effect decomposition and 3D reconstruction based on the equivalent projection data, thereby calculating the atomic number and electron cloud density, and then identifying the material of the scanned object based on the atomic number and electron cloud density. The 3D reconstruction may utilize a filtered back-projection algorithm.

[0093] Example 3

[0094] This embodiment provides an electronic device, such as Figure 6 As shown, the electronic device includes a memory 100 and a processor 200. The memory 100 and the processor 200 are connected to each other in a communication manner and can be connected via a bus or other means. Figure 6 The bus connection is taken as an example.

[0095] The processor 200 may be a central processing unit (CPU). The processor 200 may also be other general-purpose processors, digital signal processors (DSP), application-specific integrated circuits (ASIC), field-programmable gate arrays (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, or a combination of the above chips.

[0096] Memory 100, as a non-transitory computer-readable storage medium, can be used to store non-transitory software programs, non-transitory computer-executable programs, and modules, such as program instructions corresponding to the CT scan data processing method in the embodiments of the present invention. Processor 200 executes the non-transitory software programs, instructions, and modules stored in memory 100 to perform various functional applications and data processing of processor 200, thereby implementing the CT scan data processing method.

[0097] The memory 100 may include a program storage area and a data storage area, wherein the program storage area may store an operating system, an application required for at least one function; the data storage area may store data created by the processor 200, etc. In addition, the memory 100 may include a high-speed random access memory, and may also include a non-volatile memory, such as at least one disk storage device, a flash memory device, or other non-volatile solid-state storage device. In some embodiments, the memory 100 may optionally include a memory remotely located relative to the processor 200, and these remote memories may be connected to the processor via a network. Examples of the above-mentioned network include, but are not limited to, the Internet, an intranet, a local area network, a mobile communication network, and combinations thereof.

[0098] Those skilled in the art will appreciate that all or part of the processes in the above-mentioned embodiments can be implemented by instructing the relevant hardware through a computer program. The program can be stored in a computer-readable storage medium. When the program is executed, it can include the processes of the embodiments of the above-mentioned methods. The storage medium can be a magnetic disk, an optical disk, a read-only memory (ROM), a random access memory (RAM), a flash memory, a hard disk drive (HDD), or a solid-state drive (SSD). The storage medium can also include a combination of the above-mentioned types of memory.

[0099] The technical features of the above-mentioned embodiments can be combined arbitrarily. In order to make the description concise, not all possible combinations of the technical features in the above-mentioned embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0100] The above-described embodiments merely illustrate several implementations of the present invention, and while their descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the patent. It should be noted that a person skilled in the art would be able to make numerous variations and improvements without departing from the spirit of the present invention, all of which fall within the scope of protection of the present invention. Therefore, the scope of protection of the patent for this invention shall be determined by the appended claims.

Claims

1. A CT scanning system, characterized in that: The CT scanning system includes: A first ray generating device, configured to generate a first ray beam, wherein the first ray beam has a first energy; A second ray generating device is used to generate a second ray beam, wherein the second ray beam has a second energy, and the second energy is greater than the first energy; a shared detection device, disposed in the direction of ray beam emission from the first ray generating device and the second ray generating device, for receiving the first ray beam and the second ray beam and generating first projection data of the first ray beam and second projection data of the second ray beam; the shared detection device comprises an array detector panel, and the array detector panel has a single-layer structure or a double-layer structure; A scanning area is provided between the first ray generating device, the second ray generating device, and the common detection device, and the first ray generating device and the second ray generating device are spaced apart in a direction perpendicular to the scanning area; the scanning area is used to place an object to be scanned, and the translation direction of the object to be scanned includes a direction perpendicular to the scanning area; the first projection data and the second projection data are used to perform alignment adjustment based on a relative position difference between the first ray generating device and the second ray generating device in a direction perpendicular to the scanning area; wherein a first projection area of ​​the first ray beam on the common detection device and a second projection area of ​​the second ray beam on the common detection device have an overlapping area; Alternatively, a first projection area of ​​the first ray beam on the common detection device is close to but does not overlap with a second projection area of ​​the second ray beam on the common detection device; The CT scanning system also includes a rotating mechanism, the first ray generating device and the second ray generating device are arranged in a first position area of ​​the rotating mechanism, the common detection device is arranged in a second position area of ​​the rotating mechanism, the second position area is opposite to the first position area, and a hollow scanning area is arranged between the first position area and the second position area.

2. The CT scanning system according to claim 1, wherein: The area of ​​the overlapping region is greater than or equal to one half of the area of ​​the first projection region and smaller than the area of ​​the first projection region; Or the area of ​​the overlapping region is greater than or equal to half of the area of ​​the second projection region, and smaller than the area of ​​the second projection region.

3. The CT scanning system according to claim 1, wherein: The distance between the first ray generating device and the second ray generating device is: L=nd Wherein, L represents the distance between the first ray generating device and the second ray generating device, d represents the distance between two adjacent detectors in the direction of the longitudinal scanning area, and n represents a positive integer.

4. The CT scanning system according to claim 1, wherein: The CT scanning system further includes a transport mechanism for transporting the object to be scanned into and out of the scanning area along a direction running vertically through the scanning area.

5. The CT scanning system according to claim 1, wherein: The CT scanning system further includes a data processing device, which is connected to the common detection device and is used to process the first projection data and the second projection data to obtain a scanning result.

6. A CT scan data processing method, characterized in that: Applicable to the CT scanning system according to any one of claims 1 to 5; the CT scanning data processing method comprises: determining a relative position difference between the first ray generating device and the second ray generating device in a direction longitudinally across the scanning area; acquiring the first projection data and the second projection data; performing alignment adjustment on the first projection data and the second projection data based on the relative position difference to obtain equivalent projection data; Material detection is performed based on the equivalent projection data.

7. A computer-readable storage medium, characterized in that The computer-readable storage medium stores computer instructions, which, when executed by a processor, implement the CT scan data processing method according to claim 6.

Images