X-ray CT imaging method and device, electronic equipment and storage medium

Abstract

The invention provides an X-ray CT imaging method and device, electronic equipment and a storage medium. Simulating an intense radiation field in the 4 pi direction in the simulated world, and starting the simulated X-ray CT imaging system to perform first simulation calculation; in the X-ray CT imaging system, X-rays are emitted through an emitter, and a die body is scanned and energy deposition is recorded through a detector; in the first simulation calculation process, the simulation calculation of the current angle is stopped when the X-ray of each angle hits the boundary of the world, and the first simulation calculation process is stopped until the X-ray of the last angle hits the boundary of the world; and obtaining a first CT image of the die body through a three-dimensional reconstruction algorithm based on two-dimensional projection images of different angles output by energy deposition converted and recorded by the detector. According to the method, the problem that systematic evaluation of the influence of a space intense radiation environment on X-ray CT imaging full-link performance can be solved.

Description

Technical Field

[0001] The embodiments of the present disclosure relate to the field of imaging technology, and in particular to an X-ray CT imaging method, apparatus, electronic device, and storage medium. Background Art

[0002] As an important non-destructive testing technology, CT technology is widely used in fields such as spacecraft structure inspection and material analysis. However, radiation particle irradiation in the space radiation environment can cause problems such as increased detector noise and signal attenuation in X-ray CT imaging systems, seriously affecting imaging accuracy and equipment life.

[0003] At present, there is no public full-link simulation system for X-ray CT imaging system simulation in strong radiation environments, such as space and nuclear facilities, which can simultaneously simulate the impact of the radiation environment on the entire process of X-ray source, measured object, detector and image reconstruction. Summary of the Invention

[0004] In view of this, the present application provides an X-ray CT imaging method, device, electronic device and storage medium, which can solve the problem of systematically evaluating the impact of strong radiation environment in space on the full-link performance of X-ray CT imaging.

[0005] To solve the above technical problems, the technical solution of this application is implemented as follows: In one embodiment, an X-ray CT imaging method is provided, the method comprising: A strong radiation field in the 4π direction is simulated in the simulated world, and a simulated X-ray CT imaging system is started to perform a first simulation calculation. In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records energy deposition. During the first simulation calculation process, when the X-ray at each angle hits the boundary of the world, the simulation calculation at the current angle is stopped, and the first simulation calculation process is stopped when the X-ray at the last angle hits the boundary of the world; Based on the two-dimensional projection images at different angles output by the detector through the energy deposition recorded by the conversion, a first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm; wherein, the first CT image is used to analyze the influence of the strong radiation field on the quality of X-ray CT imaging.

[0006] Wherein, the method further comprises: Using a Monte Carlo toolkit to simulate the world, the strong radiation field in the 4π direction, and the X-ray CT imaging system; The simulation of the X-ray imaging system includes simulation of the emitter, phantom and detector; and a preset physical process is added to the X-ray CT imaging system to set scanning parameters; and strong radiation environment model parameters are set for the strong radiation field.

[0007] Wherein, the preset physical process includes: Electromagnetic interaction, hadronic interaction, Compton scattering, Rayleigh scattering and X-ray attenuation.

[0008] The scanning parameters include: The energy range and ray angle emitted by the transmitter; The resolution, material, and size of the detector; as well as the position, source-object distance, and source-screen distance of the phantom to be scanned.

[0009] The strong radiation environment model parameters include: The type, energy and amount of radiation particles required.

[0010] Wherein, the method further comprises: A simulated X-ray CT imaging system is started in the simulated world to perform a second simulation calculation. In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records energy deposition. During the second simulation calculation process, when the X-ray at each angle hits the boundary of the world, the simulation calculation at the current angle is stopped, and the second simulation calculation process is stopped when the X-ray at the last angle hits the boundary of the world; Based on the two-dimensional projection images at different angles outputted by the energy deposition recorded by the detector conversion, a second CT image of the phantom is obtained through a three-dimensional reconstruction algorithm.

[0011] Wherein, the method further comprises: acquiring the first CT image and the second CT image; The first CT image and the second CT image are compared to analyze the influence of the strong radiation field on the X-ray CT imaging quality.

[0012] In another embodiment, an X-ray CT imaging apparatus is provided, comprising: Simulation unit, used to simulate the world, strong radiation field in 4π direction and X-ray CT imaging system; a simulation calculation unit configured to simulate a strong radiation field in a 4π direction in a simulated world, and to activate a simulated X-ray CT imaging system to perform a first simulation calculation; wherein the X-ray CT imaging system emits X-rays via an emitter, and scans a phantom via a detector to record energy deposition; and during the first simulation calculation, when the X-rays at each angle hit the boundary of the world, the simulation calculation is stopped at the current angle, and the first simulation calculation is stopped when the X-rays at the last angle hit the boundary of the world; An acquisition unit is configured to obtain a first CT image of the phantom based on two-dimensional projection images at different angles outputted by the detector based on the energy deposition recorded by the detector conversion, and to obtain the first CT image of the phantom through a three-dimensional reconstruction algorithm; wherein the first CT image is used to analyze the influence of a strong radiation field on the imaging quality of X-ray CT.

[0013] In another embodiment, an electronic device is provided, including a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor implements an X-ray CT imaging method when executing the program.

[0014] In another embodiment, a computer-readable storage medium is provided, on which a computer program is stored. When the program is executed by a processor, an X-ray CT imaging method is implemented.

[0015] As can be seen from the above technical solution, in the above embodiment, a strong radiation field in the 4π direction is simulated in a simulated vacuum world, and after starting the simulated X-ray CT imaging system, the first simulation calculation is performed; during the first simulation calculation, X-rays are emitted at all angles to the phantom, and the detector is used to scan and record the energy deposition; after the first simulation calculation is completed, the two-dimensional projection images at different angles are output based on the energy deposition recorded by the detector conversion, and the first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm. This first CT image can be used to analyze the impact of the strong radiation field on the X-ray CT imaging quality. This method can solve the problem of systematically evaluating the impact of the strong radiation environment in space on the full-link performance of X-ray CT imaging. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the following briefly introduces the drawings required for use in the description of the embodiments. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0017] Figure 1 This is a schematic diagram of an X-ray CT imaging process in an embodiment of the present application; Figure 2Schematic diagram of a CT imaging system under strong radiation in a simulated world in an embodiment of the present application; Figure 3 This is another schematic diagram of an X-ray CT imaging process in an embodiment of the present application; Figure 4 Schematic diagram of a CT imaging system without strong radiation in a simulated world in an embodiment of the present application; Figure 5 This is a schematic diagram of the CT image comparison process in the embodiment of this application; Figure 6 This is a schematic diagram of the X-ray CT imaging device structure in an embodiment of the present application; Figure 7 A schematic diagram of the physical structure of an electronic device provided by an embodiment of the present invention. DETAILED DESCRIPTION

[0018] The following will be combined with the drawings in the embodiments of this application to clearly and completely describe the technical solutions in the embodiments of this application. Obviously, the embodiments described are only part of the embodiments of this application, not all of the embodiments. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0019] The terms "first," "second," "third," "fourth," and so on (if any) in the description and claims of the present invention and in the drawings described above are used to distinguish similar objects and are not necessarily used to describe the order or precedence of objects. It should be understood that the terms used in this way are interchangeable where appropriate, so that the implementation of the invention described herein can, for example, be implemented in an order other than those illustrated or described herein. In addition, the terms "including" and "having," as well as any variations thereof, are intended to cover non-exclusive inclusions. For example, a process, method, system, product, or apparatus that includes a series of steps or units is not necessarily limited to those steps or units expressly listed, but may include other steps or units not expressly listed or inherent to such processes, methods, products, or apparatus.

[0020] The following specific embodiments are used to describe the technical solution of the present invention in detail. The following specific embodiments can be combined with each other, and the same or similar concepts or processes may not be described in detail in some embodiments.

[0021] At present, there is no public full-link simulation system for X-ray CT imaging system simulation in strong radiation environments, such as space and nuclear facilities, which can simultaneously simulate the impact of the radiation environment on the entire process of X-ray source, measured object, detector and image reconstruction.

[0022] Based on the above technical problems, an X-ray CT imaging method is provided in an embodiment of the present application. A strong radiation field in the 4π direction is simulated in a simulated vacuum world. After starting the simulated X-ray CT imaging system, a first simulation calculation is performed. During the first simulation calculation, X-rays are emitted at all angles to the phantom, and a detector is used to scan and record the energy deposition. After the first simulation calculation is completed, two-dimensional projection images at different angles are output based on the energy deposition recorded by the detector conversion, and a first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm. This first CT image can be used to analyze the impact of the strong radiation field on the X-ray CT imaging quality. This solution can solve the problem of systematically evaluating the impact of a strong radiation environment in space on the full-link performance of X-ray CT imaging.

[0023] Before performing X-ray CT imaging, the strong radiation fields in the world and 4π directions, as well as the X-ray CT imaging system, are simulated first; preset physical processes are added to the X-ray CT imaging system, and scanning parameters are set; and strong radiation environment model parameters are set for the strong radiation field.

[0024] The simulated world is a vacuum world, which is used as a simulation environment for the X-ray CT imaging system; The simulated strong radiation field in the 4π direction usually refers to a radiation field that is uniform and has a high intensity within a 4π solid angle (all-directional). The 4π direction refers to the full spatial solid angle (spherical), that is, non-directional (or isotropic) radiation. A strong radiation field means that the radiation power density within a unit solid angle is high, which is suitable for scenarios with high dose rates or high field strength requirements.

[0025] Simulated X-ray CT imaging system, including: emitter, detector and phantom; In practical implementation, the Monte Carlo toolkit can be used to simulate the world, strong radiation fields in the 4π direction, and X-ray CT imaging systems. The Monte Carlo method is a numerical computation technique based on random sampling that approximates complex mathematical, physical, or engineering problems through a large number of random simulations. Its core concept is to use probability and statistics theory to approximate the true solution through random experiments. Written in the object-oriented C++ language, the Monte Carlo toolkit offers excellent flexibility, accuracy, and professionalism. In Geant4, simulations are more realistic.

[0026] Set the scanning parameters of the X-ray CT imaging system: The energy range and beam angle of the transmitter; the energy range of the transmitter can be set to 80-100 keV (electron volt, a unit of energy), but this can be determined based on actual needs during implementation and is not limited to this; the beam angle is determined based on the volume and shape of the phantom to be scanned; The resolution, material, and size of the detector; as well as the position of the phantom to be scanned, the source-object distance, and the source-screen distance.

[0027] The resolution of the detector can be set to 512 512, but there is no restriction on this; the material can be selected as cesium iodide, etc.; the size setting is based on the size of the phantom, the size of the vacuum world, etc.; import the required scanning phantom, that is, specify the object to be scanned, that is, the simulated phantom; The source-object distance is set as the distance between the emitter's X-ray source and the center of the phantom, and the source-screen distance is the vertical distance from the emitter's X-ray source (focus) to the detector (screen / imaging plane).

[0028] Set the strong radiation environment model parameters: The type, energy and quantity of radiation particles required; Types of radiation particles include protons, neutrons, heavy ions, etc.

[0029] The energy of the radiated particles can be set to monoenergetic or spectral; Single energy simulation: 5~6 typical energy points such as 10MeV, 100MeV, 1GeV, 10GeV, 100GeV, etc. Energy spectrum simulation: Use measured or standard energy spectra, such as: Solar proton event (SPE) spectrum; Galactic cosmic ray (GCR) spectrum; The number of radiation particles (or flux) can be set to a fixed number of particles (such as 10 6 Protons) or flux density (in particles / cm² / s), combined with irradiation time to calculate the total number of particles. If simulating cell damage, the number of incident particles per cell can be set, such as 1particle / cell.

[0030] At this point, the simulation preparations for the world and X-ray CT imaging system have been completed and simulation experiments can be carried out.

[0031] The X-ray CT imaging process in the embodiment of the present application is described in detail below with reference to the accompanying drawings.

[0032] See also Figure 1 , Figure 1 This is a schematic diagram of an X-ray CT imaging process in an embodiment of the present application. The specific steps are: Step 101: simulate a strong radiation field in the 4π direction in the simulated world, and start a simulated X-ray CT imaging system to perform the first simulation calculation; in the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records the energy deposition.

[0033] See also Figure 2 , Figure 2 Schematic diagram of a CT imaging system under strong radiation in a simulated world in an embodiment of the present application. After simulating a strong radiation field D in the 4π direction in world E and turning on the X-ray CT imaging system, the emitter A in the X-ray CT imaging system starts emitting X-rays F at the phantom B at the initial position; the initial position here can be any pre-specified position; the simulated strong radiation field D in the 4π direction can randomly generate strong radiation rays at any point in world E, forming a strong radiation field in the 4π direction, i.e. Figure 2 The relatively messy lines outside the X-rays; detector C scans the phantom B and records the energy deposition.

[0034] Step 102, during the first simulation calculation process, when the X-ray at each angle hits the boundary of the simulated world, the simulation calculation of the current angle is stopped, and the first simulation calculation process is stopped when the X-ray at the last angle hits the boundary of the simulated world.

[0035] During the simulation, the phantom is completely scanned, i.e., 360 degrees, so that X-rays are emitted at every angle to scan the phantom. This effect can be achieved by rotating the phantom or by rotating the emitter and detector. For each angle, the simulation calculation of the current angle is stopped when the X-ray hits the boundary of the world; then the angle is switched, and so on, until all angles are scanned.

[0036] Step 103 : Based on the two-dimensional projection images at different angles outputted by the detector through energy deposition conversion and recording, a first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm. The first CT image is used to analyze the effect of the strong radiation field on the quality of X-ray CT imaging.

[0037] The specific implementation of obtaining the first CT image of the phantom through the three-dimensional reconstruction algorithm for the two-dimensional projection images at different angles is as follows: The first step is to obtain a three-dimensional CT model by using a three-dimensional reconstruction algorithm on two-dimensional projection images at different angles.

[0038] The reconstruction can be performed using VGStudio Max3.0 software, and the reconstruction algorithm can be an approximate reconstruction based on circular cone-beam scanning (Feldkamp-Davis-Kress, FDK) algorithm.

[0039] The second step is to slice the three-dimensional CT model to obtain a first CT image.

[0040] The relevant processing of slicing here can be set according to actual needs, and this application does not impose any restrictions on this.

[0041] In this embodiment, a strong radiation field in the 4π direction is simulated in a simulated vacuum world, and after starting the simulated X-ray CT imaging system, the first simulation calculation is performed; during the first simulation calculation, X-rays are emitted to the phantom at all angles, and the detector is used to scan and record the energy deposition; after the first simulation calculation is completed, two-dimensional projection images of different angles are output based on the energy deposition recorded by the detector conversion, and the first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm. This method performs full-link modeling and simulation on the X-ray CT imaging system and the strong radiation field in the 4π direction, and the first CT image of the phantom can be obtained after one simulation calculation, which can be used to analyze the impact of the strong radiation field on the quality of X-ray CT imaging. Therefore, this solution can solve the problem of systematically evaluating the impact of the strong radiation environment in space on the full-link performance of X-ray CT imaging.

[0042] See also Figure 3 , Figure 3 This is another X-ray CT imaging process diagram in the embodiment of this application. The specific steps are: Step 301: Start a simulated X-ray CT imaging system in the simulated world and perform a second simulation calculation. In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records energy deposition.

[0043] See also Figure 4 , Figure 4 Schematic diagram of a CT imaging system without strong radiation in a simulated world in an embodiment of the present application.

[0044] After the X-ray CT imaging system is turned on in world E, emitter A in the X-ray CT imaging system begins to emit X-rays F onto phantom B at an initial position; the initial position here can be any pre-specified position; detector C scans phantom B and records the energy deposition.

[0045] Figure 2 The realization ratio Figure 4 The implementation adds a strong radiation field, and the other implementation processes are the same.

[0046] Step 302: During the second simulation calculation, when the X-ray at each angle hits the boundary of the simulated world, the simulation calculation at the current angle is stopped, and the second simulation calculation process is stopped when the X-ray at the last angle hits the boundary of the simulated world. During the simulation, the phantom is completely scanned, i.e., 360 degrees, so that X-rays are emitted at every angle to scan the phantom. This effect can be achieved by rotating the phantom or by rotating the emitter and detector. For each angle, the simulation calculation of the current angle is stopped when the X-ray hits the boundary of the world; then the angle is switched, and so on, until all angles are scanned.

[0047] Step 303 : Based on the two-dimensional projection images at different angles outputted by the detector through energy deposition conversion and recording, a second CT image of the phantom is obtained through a three-dimensional reconstruction algorithm.

[0048] The specific implementation of obtaining the second CT image of the phantom through the three-dimensional reconstruction algorithm for the two-dimensional projection images at different angles is as follows: The first step is to obtain a three-dimensional CT model by using a three-dimensional reconstruction algorithm on two-dimensional projection images at different angles.

[0049] During the specific reconstruction, VGStudio Max3.0 software can be used for reconstruction, and the reconstruction algorithm can be the FDK algorithm.

[0050] The second step is to slice the three-dimensional CT model to obtain a second CT image.

[0051] The relevant processing of slicing here can be set according to actual needs, and this application does not impose any restrictions on this.

[0052] In this embodiment, after starting the simulated X-ray CT imaging system in the simulated vacuum world, a second simulation calculation is performed; during the second simulation calculation, X-rays are emitted to the phantom at all angles, and the detector is used to scan and record the energy deposition; after the first simulation calculation is completed, the two-dimensional projection images at different angles are output based on the energy deposition recorded by the detector conversion, and the second CT image of the phantom is obtained through a three-dimensional reconstruction algorithm. This method performs full-link modeling and simulation on the X-ray CT imaging system, and the first CT image of the phantom can be obtained after one simulation calculation, which can be used to analyze the impact of X-rays on CT imaging in the absence of strong radiation. Therefore, this solution can simulate the X-ray CT imaging system in an environment without strong radiation and obtain corresponding CT imaging.

[0053] See also Figure 5 , Figure 5 This is a schematic diagram of the CT image comparison process in the embodiment of this application. The specific steps are: Step 501 : simulate a strong radiation field in the 4π direction in the simulated world, start a simulated X-ray CT imaging system, and perform the first simulation calculation.

[0054] In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records the energy deposition.

[0055] Step 502, during the first simulation calculation process, when the X-ray at each angle hits the boundary of the simulated world, the simulation calculation of the current angle is stopped, and the first simulation calculation process is stopped until the X-ray at the last angle hits the boundary of the simulated world.

[0056] In step 503 , based on the two-dimensional projection images at different angles outputted by the detector through energy deposition conversion and recording, a first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm. Execute step 507 .

[0057] The first CT image is used to analyze the influence of X-rays on CT imaging under strong radiation.

[0058] Step 504: Start the simulated X-ray CT imaging system in the simulated world and perform a second simulation calculation.

[0059] In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records energy deposition.

[0060] Step 505, during the second simulation calculation process, the simulation calculation of the current angle is stopped when the X-ray at each angle hits the boundary of the simulated world, and the second simulation calculation process is stopped until the X-ray at the last angle hits the boundary of the simulated world.

[0061] Step 506 : Based on the two-dimensional projection images at different angles outputted by the detector through conversion and recording of the energy deposition, a second CT image of the phantom is obtained through a three-dimensional reconstruction algorithm.

[0062] Step 507: Acquire a first CT image and a second CT image.

[0063] Step 508 : Compare the first CT image and the second CT image to analyze the impact of the strong radiation field on the X-ray CT imaging quality.

[0064] In this embodiment, simulation calculations are performed in strong radiation field scenarios and non-strong radiation field scenarios to obtain a first CT image under a strong radiation field and a second CT image under a non-strong radiation field. Through comparative analysis, the impact of a strong radiation field on the quality of X-ray CT imaging can be better determined.

[0065] Based on the Monte Carlo method to simulate the performance changes of the X-ray CT imaging system in a strong radiation environment, we can evaluate the different radiation effects and the degree of influence of the strong radiation environment on the X-ray CT imaging system, reveal the specific impact mechanism of strong spatial radiation on the image quality of the CT system, and provide theoretical guidance for future device design and optimization of CT imaging algorithms in its environment.

[0066] All the above optional technical solutions can be arbitrarily combined to form optional embodiments of the present disclosure, and will not be described in detail here.

[0067] Based on the same inventive concept, an X-ray CT imaging device is also provided in the embodiment of the present application. Figure 6 , Figure 6 This is a schematic diagram of the X-ray CT imaging device structure in an embodiment of the present application. The device includes: A simulation unit 601 is used to simulate the world, a strong radiation field in the 4π direction, and an X-ray CT imaging system; The simulation calculation unit 602 is configured to simulate a strong radiation field in the 4π direction in the simulated world and activate a simulated X-ray CT imaging system to perform a first simulation calculation. In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records energy deposition. During the first simulation calculation, the simulation calculation for each angle is stopped when the X-rays at the current angle hit the boundary of the world, and the first simulation calculation process is stopped when the X-rays at the last angle hit the boundary of the world. The acquisition unit 603 is used to output two-dimensional projection images at different angles based on the energy deposition recorded by the detector conversion, and obtain a first CT image of the phantom through a three-dimensional reconstruction algorithm; wherein the first CT image is used to analyze the impact of the strong radiation field on the X-ray CT imaging quality.

[0068] In another embodiment, The simulation unit 601 specifically uses a Monte Carlo toolkit to simulate the world, a strong radiation field in the 4π direction, and an X-ray CT imaging system; wherein the simulation of the X-ray imaging system includes the simulation of the emitter, the phantom, and the detector; and adds preset physical processes to the X-ray CT imaging system and sets scanning parameters; and sets strong radiation environment model parameters for the strong radiation field.

[0069] In another embodiment, the preset physical process includes: Electromagnetic interaction, hadronic interaction, Compton scattering, Rayleigh scattering and X-ray attenuation.

[0070] In another embodiment, the scanning parameters include: The energy range and ray angle emitted by the transmitter; The resolution, material, and size of the detector; as well as the position of the phantom to be scanned, the source-object distance, and the source-screen distance.

[0071] In another embodiment, the strong radiation environment model parameters include: The type, energy and amount of radiation particles required.

[0072] In another embodiment, The simulation calculation unit is further configured to start a simulated X-ray CT imaging system in the simulated world and perform a second simulation calculation; wherein the X-ray CT imaging system emits X-rays through an emitter, and scans the phantom through a detector to record energy deposition; during the second simulation calculation, when the X-rays at each angle hit the boundary of the world, the simulation calculation at the current angle is stopped, and the second simulation calculation process is stopped when the X-rays at the last angle hit the boundary of the world; The acquisition unit 603 is further configured to obtain a second CT image of the phantom through a three-dimensional reconstruction algorithm based on the two-dimensional projection images at different angles outputted by the detector based on the energy deposition recorded by the detector conversion.

[0073] In another embodiment, An acquisition unit 603 is further configured to acquire a first CT image and a second CT image; The analyzing unit 604 is further configured to compare the first CT image and the second CT image, and analyze the influence of the strong radiation field on the X-ray CT imaging quality.

[0074] The units in the above embodiments may be integrated into one body or deployed separately; they may be combined into one unit or further divided into multiple sub-units.

[0075] In another embodiment, an electronic device is provided, including a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor implements the X-ray CT imaging method when executing the program.

[0076] In another embodiment, a computer-readable storage medium is provided, on which computer instructions are stored. When the instructions are executed by a processor, an X-ray CT imaging method is implemented.

[0077] Figure 7 Schematic diagram of the physical structure of the electronic device provided by the embodiment of the present invention. Figure 7 As shown, the electronic device may include: a processor (Processor) 710, a communication interface (Communications Interface) 720, a memory (Memory) 730 and a communication bus 740, wherein the processor 710, the communication interface 720, and the memory 730 communicate with each other via the communication bus 740. The processor 710 may call the logic instructions in the memory 730 to execute the following method: In the simulated world, a strong radiation field in the 4π direction is simulated, and a simulated X-ray CT imaging system is started to perform the first simulation calculation. In the X-ray CT imaging system, the emitter emits X-rays, and the detector scans the phantom and records the energy deposition. During the first simulation calculation, when the X-ray at each angle hits the boundary of the world, the simulation calculation of the current angle is stopped, and the first simulation calculation process is stopped when the X-ray at the last angle hits the boundary of the world; Based on the two-dimensional projection images at different angles output by the detector's recorded energy deposition, a first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm. The first CT image is used to analyze the impact of strong radiation fields on the quality of X-ray CT imaging.

[0078] In addition, the logic instructions in the aforementioned memory 730 can be implemented in the form of a software functional unit and, when sold or used as an independent product, can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the present invention, or the portion that contributes to the prior art, or the portion of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions for causing a computer device (which can be a personal computer, a server, or a network device, etc.) to execute all or part of the steps of the various embodiments of the method of the present invention. The aforementioned storage medium includes various media that can store program code, such as a USB flash drive, a mobile hard drive, a read-only memory (ROM), a random access memory (RAM), a magnetic disk, or an optical disk.

[0079] The device embodiments described above are merely illustrative. The units described as separate components may or may not be physically separate, and the components shown as units may or may not be physical units, i.e., they may be located in one location or distributed across multiple network units. Some or all of the modules may be selected based on actual needs to achieve the objectives of the present embodiment. Persons of ordinary skill in the art will be able to understand and implement the present invention without inventive effort.

[0080] Through the description of the above embodiments, those skilled in the art will clearly understand that each embodiment can be implemented using software plus a necessary general-purpose hardware platform, or of course, hardware. Based on this understanding, the essence of the above technical solution, or the portion that contributes to the prior art, can be embodied in the form of a software product. This computer software product can be stored in a computer-readable storage medium, such as ROM / RAM, a magnetic disk, or an optical disk, and includes a number of instructions for causing a computer device (which can be a personal computer, a server, or a network device, etc.) to execute the methods described in each embodiment or certain portions of the embodiments.

[0081] The flowcharts and block diagrams in the accompanying drawings of the present application show the possible implementation architecture, functions and operations of the systems, methods and computer program products according to the various embodiments disclosed in the present application. In this regard, each box in the flowchart or block diagram can represent a module, program segment, or a part of code, and the above-mentioned module, program segment, or a part of code contains one or more executable instructions for realizing the specified logical function. It should also be noted that in some alternative implementations, the functions marked in the box can also occur in the order of the standards in different figures. For example, the boxes represented by two connections can actually be executed substantially in parallel, and they can sometimes be executed in the opposite order, depending on the functions involved. It should also be noted that each box in the block diagram or flowchart, and the combination of the boxes in the block diagram or flowchart, can be implemented by a dedicated hardware-based system that performs the specified function or operation, or can be implemented by a combination of dedicated hardware and computer instructions.

[0082] Those skilled in the art will appreciate that the features described in the various embodiments and / or claims disclosed in this application may be combined and / or coupled in various ways, even if such combinations and / or couplings are not explicitly disclosed in this application. In particular, without departing from the spirit and teachings of this application, the features described in the various embodiments and / or claims of this application may be combined and / or coupled in various ways, and all such combinations and / or couplings fall within the scope disclosed in this application.

[0083] The principles and implementation methods of the present invention are described herein using specific embodiments. The description of the above embodiments is only used to help understand the method of the present invention and its core ideas, and is not intended to limit this application. For those skilled in the art, changes can be made in the specific implementation methods and application scope based on the ideas, spirit and principles of the present invention. Any modifications, equivalent replacements, improvements, etc. made therein should be included within the scope of protection of this application.

Claims

1. An X-ray CT imaging method, characterized in that: The method comprises: A strong radiation field in the 4π direction is simulated in the simulated world, and a simulated X-ray CT imaging system is started to perform a first simulation calculation. In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records energy deposition. During the first simulation calculation process, when the X-ray at each angle hits the boundary of the world, the simulation calculation at the current angle is stopped, and the first simulation calculation process is stopped when the X-ray at the last angle hits the boundary of the world; Based on the two-dimensional projection images at different angles output by the detector through the energy deposition recorded by the conversion, a first CT image of the phantom is obtained through a three-dimensional reconstruction algorithm; wherein, the first CT image is used to analyze the influence of the strong radiation field on the quality of X-ray CT imaging.

2. The method according to claim 1, characterized in that The method further comprises: Using a Monte Carlo toolkit to simulate the world, the strong radiation field in the 4π direction, and the X-ray CT imaging system; The simulation of the X-ray imaging system includes simulation of the emitter, phantom and detector; and a preset physical process is added to the X-ray CT imaging system to set scanning parameters; and strong radiation environment model parameters are set for the strong radiation field.

3. The method according to claim 2, characterized in that The preset physical process includes: Electromagnetic interaction, hadronic interaction, Compton scattering, Rayleigh scattering and X-ray attenuation.

4. The method according to claim 2, characterized in that The scanning parameters include: The energy range and ray angle emitted by the transmitter; The resolution, material, and size of the detector; as well as the position, source-object distance, and source-screen distance of the phantom to be scanned.

5. The method according to claim 2, characterized in that The strong radiation environment model parameters include: The type, energy and quantity of radiation particles required.

6. The method according to any one of claims 1 to 5, characterized in that The method further comprises: A simulated X-ray CT imaging system is started in the simulated world to perform a second simulation calculation. In the X-ray CT imaging system, an emitter emits X-rays, and a detector scans the phantom and records energy deposition. During the second simulation calculation process, when the X-ray at each angle hits the boundary of the world, the simulation calculation at the current angle is stopped, and the second simulation calculation process is stopped when the X-ray at the last angle hits the boundary of the world; Based on the two-dimensional projection images at different angles outputted by the energy deposition recorded by the detector conversion, a second CT image of the phantom is obtained through a three-dimensional reconstruction algorithm.

7. The method according to claim 6, characterized in that The method further comprises: acquiring the first CT image and the second CT image; The first CT image and the second CT image are compared to analyze the influence of the strong radiation field on the X-ray CT imaging quality.

8. An X-ray CT imaging device, characterized in that: The device comprises: Simulation unit, used to simulate the world, strong radiation field in 4π direction and X-ray CT imaging system; a simulation calculation unit configured to simulate a strong radiation field in a 4π direction in a simulated world, and to activate a simulated X-ray CT imaging system to perform a first simulation calculation; wherein the X-ray CT imaging system emits X-rays via an emitter, and scans a phantom via a detector to record energy deposition; and during the first simulation calculation, when the X-rays at each angle hit the boundary of the world, the simulation calculation is stopped at the current angle, and the first simulation calculation is stopped when the X-rays at the last angle hit the boundary of the world; An acquisition unit is configured to obtain a first CT image of the phantom based on two-dimensional projection images at different angles outputted by the detector based on the energy deposition recorded by the detector conversion, and to obtain the first CT image of the phantom through a three-dimensional reconstruction algorithm; wherein the first CT image is used to analyze the influence of a strong radiation field on the imaging quality of X-ray CT.

9. An electronic device comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein: When the processor executes the program, the method according to any one of claims 1 to 7 is implemented.

10. A computer-readable storage medium having a computer program stored thereon, characterized in that: When the program is executed by a processor, the method according to any one of claims 1 to 7 is implemented.

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