Image de-artifacting methods, systems, electronic devices, and storage media

Abstract

The application discloses an image artifact removal method and system, an electronic device and a storage medium. The image artifact removal method comprises the following steps: obtaining original scanning data of a detector in a process of performing computer tomography on a target object; and performing artifact correction on the original scanning data containing a scattering signal by using a scattering reference signal, wherein the scattering reference signal is obtained according to energy data of the detector in a non-slit area and energy data of the detector in a slit area in the process of performing computer tomography. The scattering reference signal obtained according to the energy data of the detector in the non-slit area and the energy data of the detector in the slit area is used to perform artifact correction on the original scanning data containing the scattering signal, so that annular artifacts of a medical image are removed, and better imaging effect is achieved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of computer tomography, in particular to an image artifact removal method and system, an electronic device and a storage medium. BACKGROUND

[0002] The current computer tomography device constructs an image by transmitting rays (ray bundles), and the transmitting rays are generated by X-rays. However, after the X-rays pass through a human body or an object, transmitting rays and scattered rays are generated. The scattered rays are harmful to the reconstructed image and need to be removed. The detector can convert the X-rays irradiated thereon into an electrical signal and is the most important part of the device. The detector directs the X-ray bundle emitted by the ray tube to the corresponding pixel point of the detector module. The detector is assembled in the form of a module, and therefore, some gaps exist between the detector modules, as shown in FIG. 1. When some X-rays pass through the gap and enter the pixel point at the edge of the detector (i.e., the dark square in FIG. 1), the scattering phenomenon occurs, which causes the pixel point at the edge of the detector to receive more X-ray receiving signals than the actual value. On the finally reconstructed image, the pixel point at the edge of the detector is prone to produce artifacts, which affects the finally reconstructed image. In the prior art, in order to remove the artifacts, the hardware device is usually improved, for example, a grid can be added above the gap in FIG. 1 to reduce the scattering signals of the X-rays. However, this method increases the complexity of the hardware and the manufacturing cost of the product, and cannot fundamentally solve the problem that the image scanned by the computer tomography device produces artifacts. Figure 1 Figure 1 Figure 1 SUMMARY

[0003] The technical problem to be solved by the present application is to overcome the problem that in the prior art, due to the gap between the detector modules, when the X-rays are scattered at the edge of the detector, the detector receives more X-rays than the actual value, which causes the finally reconstructed image to produce artifact defects. The present application provides an image artifact removal method, system, electronic device and storage medium.

[0004] The present application solves the above technical problems by the following technical solutions:

[0005] In a first aspect, the present application provides an image artifact removal method, which comprises:

[0006] obtaining the original scanning data of the detector in the process of computer tomography of the target object;

[0007] ​​​The original scan data containing scatter signals is corrected for artifacts by using a scatter reference signal; wherein the scatter reference signal is obtained according to energy data of the detector in a non-slit region and energy data of the detector in a slit region during a computer tomography process.

[0008] Preferably, the energy data of the detector in the non-slit region includes energy intensity values of the detector in a non-phantom non-slit region and energy intensity values of the detector in a phantom non-slit region.

[0009] The energy data of the detector in the slit region includes energy intensity values of the detector in a non-phantom slit region and energy intensity values of the detector in a phantom slit region.

[0010] The phantom is a phantom simulating the target object during a computer tomography process.

[0011] Preferably, the step of correcting the original scan data containing scatter signals for artifacts by using a scatter reference signal includes:

[0012] The original scan data is evaluated for scatter intensity to obtain an original scatter signal.

[0013] The original scatter signal is input into a polynomial fitting result to obtain a scatter signal; wherein coefficients of the polynomial fitting result are determined according to the scatter reference signal.

[0014] The original scan data is removed of the scatter signal to obtain original scan data corrected for artifacts.

[0015] Preferably, the coefficients of the polynomial fitting result are a difference between a first ratio and a second ratio.

[0016] The first ratio is a ratio of the energy intensity values of the detector in the phantom non-slit region to the energy intensity values of the detector in the non-phantom non-slit region.

[0017] The second ratio is a ratio of the energy intensity values of the detector in the phantom slit region to the energy intensity values of the detector in the non-phantom slit region.

[0018] Or,

[0019] The coefficients of the polynomial result are a smoothed difference of a difference between the first ratio and the second ratio; the smoothed difference is a difference obtained after smoothing the difference between the first ratio and the second ratio.

[0020] Preferably, the image artifact correction method further includes:

[0021] The original scan data containing the projection signal is corrected for artifacts by using a projection reference signal;

[0022] The projection reference signal is obtained according to the energy intensity value of the detector in the no phantom and no slit area and the energy intensity value of the detector in the no phantom and slit area during the computer tomography.

[0023] Preferably, the step of correcting the original scan data containing the projection signal for artifacts by using a projection reference signal comprises:

[0024] The original scan data is converted into projection data;

[0025] The projection data is input into a polynomial fitting result to obtain projection correction data; wherein the coefficients of the polynomial fitting result are determined according to the projection reference signal.

[0026] Preferably, the coefficients of the polynomial fitting result are the logarithmic values of a third ratio, wherein the third ratio is the ratio of the energy intensity value of the detector in the no phantom and no slit area to the energy intensity value of the detector in the no phantom and slit area.

[0027] Or,

[0028] The coefficients of the polynomial fitting result are the logarithmic values of a third ratio and a smoothed logarithmic value; the smoothed logarithmic value is a logarithmic value obtained by smoothing the logarithmic values of the third ratio.

[0029] In a second aspect, the present application provides an image artifact removal system, which comprises:

[0030] An acquisition module is configured to acquire original scan data of a detector during a computer tomography of a target object;

[0031] A correction module is configured to correct the original scan data containing the scatter signal for artifacts by using a scatter reference signal; wherein the scatter reference signal is obtained according to the energy data of the detector in the no slit area and the energy data of the detector in the slit area during the computer tomography.

[0032] In a third aspect, the present application provides an electronic device, which comprises a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the computer program to implement the image artifact removal method.

[0033] In a fourth aspect, the present application provides a computer readable storage medium, which stores a computer program, wherein the computer program is executable on a processor to implement the image artifact removal method.

[0034] The positive progress effect of the present application is that:

[0035] The present application adopts the scatter reference signal obtained from the energy data of the non-slit area detector and the energy data of the slit area detector to perform artifact correction on the original scanning data containing the scatter signal, in practice, the image can be reconstructed through the original scanning data after artifact correction, and then the medical image without artifacts is obtained, so that better imaging effect is achieved. BRIEF DESCRIPTION OF DRAWINGS

[0036] Figure 1 A schematic diagram of the principle of the artifact caused by the X-ray passing through the gap between the detector modules;

[0037] Figure 2 A first flowchart of an image artifact removal method provided for embodiment 1 of the present application;

[0038] Figure 3 A second flowchart of an image artifact removal method provided for embodiment 1 of the present application;

[0039] Figure 4 A third flowchart of an image artifact removal method provided for embodiment 1 of the present application;

[0040] Figure 5 A schematic diagram of the original scatter signal intensity of an image artifact removal method provided for embodiment 1 of the present application;

[0041] Figure 6 A schematic diagram of the fitted scatter signal intensity of an image artifact removal method provided for embodiment 1 of the present application;

[0042] Figure 7 A comparison diagram of the original scatter signal intensity and the fitted scatter signal intensity of an image artifact removal method provided for embodiment 1 of the present application;

[0043] Figure 8 A first structural diagram of an image artifact removal system provided for embodiment 2 of the present application;

[0044] Figure 9 A second structural diagram of an image artifact removal system provided for embodiment 2 of the present application;

[0045] Figure 10 A structural schematic diagram of an electronic device provided for embodiment 3 of the present application. DETAILED DESCRIPTION

[0046] The present application will be further described below by way of examples, but the present application is not limited in the scope of the examples.

[0047] Embodiment 1

[0048] The embodiment provides an image artifact removal method which can be applied to images constructed by a computed tomography image device such as a CT (Computed Tomography) device and a PET (Positron Emission Computed Tomography) device. Figure 2 The image artifact removal method comprises the following steps.

[0049] S1, obtaining original scanning data of a detector in a process of performing computed tomography on a target object. The target object is a biological tissue, for example, the head of a person can be subjected to computed tomography by a CT device or a PET device, and the target object is the head of the person.

[0050] S2, performing artifact correction on the original scanning data containing a scatter signal by using a scatter reference signal.

[0051] The scatter reference signal is obtained according to energy data of the detector without a slit region and energy data of the detector with a slit region in the process of performing computed tomography. The energy data includes energy data such as a scatter signal and a projection signal.

[0052] When the energy data of the detector with a slit region is obtained, other regions of the detector except the slit region are shielded so that the content of the scatter signal contained in the original scanning data of the slit region is less than a content threshold. The slit region is arranged on a baffle, the slit region is composed of a slit with a fixed preset width and a narrow and long slit, and the baffle with the slit region is placed on the detector to receive a fixed content of the scatter signal of the original scanning data. The content threshold is determined according to the slit width and the total content of the scatter signal contained in the original scanning data. For example, the slit region only allows the scatter signal of 20 pixel points (the pixel points are pixel points of the detector for receiving X-rays and outputting response data) to be irradiated. In actual operation, the slit region needs to be moved so that all the pixel points of the detector can be irradiated by X-rays.

[0053] In an optional embodiment, the energy data of the detector without a slit region includes an energy intensity value of a detector without a phantom without a slit region and an energy intensity value of a detector with a phantom without a slit region.

[0054] The energy data of the detector with a slit region includes an energy intensity value of a detector without a phantom with a slit region and an energy intensity value of a detector with a phantom with a slit region.

[0055] The phantom is a phantom for simulating the target object in the process of computer tomography. The phantom can be made of Teflon, water or other materials, and the thickness of the phantom is greater than or equal to 3 mm to simulate the thickness of human tissue.

[0056] The original scanning data after the artifact correction is used for image reconstruction, and thus the de-artifact medical image of the target object can be obtained.

[0057] In an optional embodiment, the filtered back projection (FBP) method can be used to reconstruct the image of the original scanning data after the artifact correction, so as to obtain the de-artifact medical image of the target object.

[0058] In the embodiment, the scatter reference signal obtained from the energy data of the detector in the non-slit region and the energy data of the detector in the slit region is used to correct the original scanning data containing the scatter signal, so as to remove the ring artifact of the medical image and achieve a better imaging effect.

[0059] In an optional embodiment, referring to Figure 3 , the step S2 includes:

[0060] S21, the original scatter signal is obtained by evaluating the scatter intensity of the original scanning data.

[0061] The scatter intensity evaluation is to analyze the original scanning data signal by using an algorithm, a model, a neural network or the like, so as to obtain the scatter signal in the original scanning data, i.e., the original scatter signal. The scatter intensity evaluation method includes convolution, Monte Carlo algorithm and deep learning or the like.

[0062] S22, the scatter signal is obtained by inputting the original scatter signal into the polynomial fitting result.

[0063] The polynomial fitting is to fit the entire original scatter signal by using a polynomial expansion, so as to obtain the objective scatter signal. The scatter signal after the polynomial fitting is closer to the scatter signal actually contained in the original scanning data.

[0064] The coefficients of the polynomial fitting result are determined according to the scatter reference signal.

[0065] In an optional embodiment, the coefficients of the polynomial fitting result are the difference between the first ratio and the second ratio. The first ratio is the ratio of the energy intensity value of the detector in the phantom and non-slit region to the energy intensity value of the detector in the non-phantom and non-slit region. The second ratio is the ratio of the energy intensity value of the detector in the phantom and slit region to the energy intensity value of the detector in the non-phantom and slit region.

[0066] The phantom can be made of Teflon, water or other materials, and the thickness of the phantom is greater than or equal to 3 mm to simulate the thickness of human tissue.

[0067] In an optional embodiment, the coefficient of the polynomial result is a smoothed difference value of the first ratio and the second ratio; and the smoothed difference value is a difference value obtained by smoothing the difference between the first ratio and the second ratio.

[0068] The smoothing processing mode includes a first-order exponential smoothing processing mode, a second-order exponential smoothing processing mode, and a third-order exponential smoothing processing mode, etc.

[0069] S23, remove the scattering signal from the original scanning data to obtain the original scanning data after artifact correction.

[0070] In the embodiment, through the scattering intensity evaluation and the polynomial fitting algorithm, the effect of removing the scattering signal from the original scanning data is finally achieved, the original scanning data is artifact corrected, the artifact correction mode is simplified, the operation cost is reduced, and a better imaging effect is achieved.

[0071] In an optional embodiment, the image artifact correction method further includes:

[0072] S3, using the projection reference signal to perform artifact correction on the original scanning data containing the projection signal.

[0073] The projection reference signal is obtained according to the energy intensity value of the detector in the slit region without the phantom and the energy intensity value of the detector in the slit region with the phantom during the computer tomography. The phantom is a phantom simulating the target object during the computer tomography. The phantom can be made of Teflon, water or other materials, and the thickness of the phantom is greater than or equal to 3 mm to simulate the thickness of human tissue.

[0074] In an optional embodiment, referring to Figure 4 , step S3 includes:

[0075] S31, converting the original scanning data into projection data.

[0076] The original scanning data collected from the detector is usually converted into projection data by using log operation (logarithmic operation). The projection data is the original data collected by the detector arranged into a two-dimensional matrix with the detector channel as the horizontal axis and the scanning field of view as the vertical axis, which is essentially a curve formed by each point in medical imaging.

[0077] S32, inputting the projection data into the polynomial fitting result to obtain the projection correction data.

[0078] The coefficient of the polynomial fitting result is determined according to the projection reference signal.

[0079] In an optional embodiment, the coefficient of the polynomial fitting result is a logarithmic value of a third ratio, wherein the third ratio is a ratio of the energy intensity value of the detector in the region without the phantom and the energy intensity value of the detector in the region with the phantom.

[0080] In an optional embodiment, the coefficient of the polynomial fitting result is a logarithmic value of a third ratio and a smoothed logarithmic value; the smoothed logarithmic value is a logarithmic value obtained by smoothing the logarithmic value of the third ratio.

[0081] The smoothing processing mode includes a first-order exponential smoothing processing mode, a second-order exponential smoothing processing mode, and a third-order exponential smoothing processing mode, etc.

[0082] In the embodiment, the projection reference signal is used to further correct the projection signal of the original scanning data, so that the imaging effect of the medical image is further optimized.

[0083] The following describes specific steps of an example of the image artifact removal method:

[0084] S41, air correction is performed on the original scanning data.

[0085] The air correction is a set of data obtained by performing a series of scanning without placing any object in the scanning range of the scanning device, and then subtracting a reference value obtained by only scanning the air from the original scanning data to obtain more accurate original scanning data.

[0086] S42, log operation (logarithmic operation) is performed on the original scanning data after the air correction to obtain projection data.

[0087] S43, the projection data is input into a polynomial fitting result A to obtain projection correction data.

[0088] The coefficient of the polynomial fitting result A is determined according to the projection reference signal. In the example, the coefficient of the polynomial fitting result A is a smoothed logarithmic value of a logarithmic value, and the smoothed logarithmic value is a logarithmic value obtained by smoothing the logarithmic value of a third ratio. The third ratio is a ratio of the energy intensity value of the detector in the region without the phantom and the energy intensity value of the detector in the region with the phantom. The phantom can be a phantom made of Teflon, water, or the like, and the thickness of the phantom is greater than or equal to 3 mm to simulate the thickness of human tissue.

[0089] S44, the log operation (anti-log operation) is performed on the projection correction data to obtain the original scanning data after projection artifact correction, and the scatter intensity evaluation is performed on the original scanning data after projection artifact correction to obtain the original scatter signal. The scatter evaluation mode includes convolution, Monte Carlo algorithm and deep learning. Figure 5 After the scatter intensity evaluation, the original scatter signal curve is obtained. Figure 5 The abscissa of the scatter signal curve represents the number of detector channels; Figure 5 The ordinate of the scatter signal curve represents the intensity value of the scatter signal.

[0090] S45, the original scatter signal is input into the polynomial fitting result B to obtain the scatter signal.

[0091] Figure 6 The curve part in the scatter signal curve represents the original scatter signal (the same as Figure 5 ), and the highlighted part of the curve represents the fitted scatter signal, Figure 6 The abscissa of the scatter signal curve represents the number of detector channels; Figure 6 The ordinate of the scatter signal curve represents the intensity value of the scatter signal. Figure 6 The scatter signal curve is closer to the actual acquired scatter signal intensity value, Figure 5 The highlighted part of the curve is produced because some X-rays may pass through the gap into the edge pixel points of the detector (i.e. Figure 1 The dark block in the scatter signal curve) when the scatter phenomenon occurs, which will cause the edge pixel points of the detector to receive more X-ray receiving signals than the actual ones, so multiple sharp peaks will be generated on the originally smooth curve. This is also the reason for the generation of artifacts in the pixel points of the edge of the detector in the finally reconstructed image.

[0092] Figure 7 The scatter signal curve is closer to the actual acquired scatter signal intensity value, Figure 7 The abscissa of the scatter signal curve represents the number of detector channels; Figure 7 The ordinate of the scatter signal curve represents the intensity value of the scatter signal.

[0093] In the present example, the coefficient of the polynomial fitting result B is the smoothed difference value of the difference between the first ratio and the second ratio. The first ratio is the ratio of the energy intensity value of the detector in the region with the phantom and without the slit to the energy intensity value of the detector in the region without the phantom and without the slit; the second ratio is the ratio of the energy intensity value of the detector in the region with the phantom and with the slit to the energy intensity value of the detector in the region without the phantom and with the slit. The smoothed difference value is the difference value obtained by smoothing the difference between the first ratio and the second ratio. The phantom can be a Teflon, water or other material phantom with a thickness greater than or equal to 3 mm to simulate the thickness of human tissue.

[0094] S46, the original scanning data is removed from the scatter signal, and further artifact correction is performed.

[0095] S47, reconstructing the original scanning data after the artifact correction operation by using a filtered back projection method (FBP) to obtain a de-artifact medical image of the target object.

[0096] Embodiment 2

[0097] The embodiment provides an image de-artifact system, referring to Figure 8 , the image de-artifact system comprises:

[0098] The acquisition module 1 is configured to acquire original scanning data of a detector in a process of performing computer tomography on a target object.

[0099] The correction module 2 is configured to correct the original scanning data containing a scattering signal by using a scattering reference signal, wherein the scattering reference signal is obtained according to energy data of the detector in a non-slit area and energy data of the detector in a slit area in the process of performing computer tomography.

[0100] In an optional implementation, the energy data of the detector in the non-slit area comprises an energy intensity value of the detector in a non-slit area without a phantom and an energy intensity value of the detector in a non-slit area with a phantom.

[0101] The energy data of the detector in the slit area comprises an energy intensity value of the detector in a slit area without a phantom and an energy intensity value of the detector in a slit area with a phantom.

[0102] The phantom is a phantom simulating the target object in the process of performing computer tomography. The phantom can be a Teflon, water or other material phantom, and the thickness of the phantom is greater than or equal to 3 mm to simulate the thickness of human tissue.

[0103] In an optional implementation, referring to Figure 9 , the image de-artifact system further comprises:

[0104] The reconstruction module 3 is configured to reconstruct the original scanning data after the artifact correction by using a filtered back projection method (FBP) to obtain a de-artifact medical image of the target object.

[0105] In the embodiment, the image de-artifact system corrects the original scanning data containing a scattering signal by using a scattering reference signal obtained according to the energy data of the detector in the non-slit area and the energy data of the detector in the slit area, and then removes the ring-shaped artifact of the medical image, so that a better imaging effect is achieved.

[0106] In an optional implementation, referring to Figure 9 , the image de-artifact system further comprises:

[0107] The fitting module 4 is configured to evaluate the original scanning data to obtain an original scatter signal, and configured to input the original scatter signal into the polynomial fitting result to obtain a scatter signal.

[0108] The coefficients of the polynomial fitting result are determined according to the scatter reference signal.

[0109] In an optional embodiment, the coefficients of the polynomial fitting result are a difference between a first ratio and a second ratio. The first ratio is a ratio of an energy intensity value of the detector in the region without the phantom and the slit to an energy intensity value of the detector in the region without the phantom and the slit. The second ratio is a ratio of an energy intensity value of the detector in the region with the phantom and the slit to an energy intensity value of the detector in the region without the phantom and the slit. The phantom can be made of Teflon, water or other materials, and the thickness of the phantom is greater than or equal to 3 mm to simulate the thickness of human tissue.

[0110] In an optional embodiment, the coefficients of the polynomial fitting result are a smoothed difference between the first ratio and the second ratio. The smoothed difference is a difference obtained by smoothing the difference between the first ratio and the second ratio.

[0111] The smoothing processing mode includes a first-order exponential smoothing processing mode, a second-order exponential smoothing processing mode, a third-order exponential smoothing processing mode, and the like.

[0112] The correction module 2 is further configured to remove the scatter signal from the original scanning data to obtain original scanning data after artifact correction.

[0113] In the embodiment, the image artifact correction system achieves the effect of removing the scatter signal from the original scanning data through the scatter intensity evaluation and the polynomial fitting algorithm, realizes the artifact correction of the original scanning data, simplifies the artifact correction mode, reduces the operation cost, and achieves a better imaging effect.

[0114] In an optional embodiment, the correction module 2 is further configured to use a projection reference signal to correct the original scanning data containing a projection signal.

[0115] The projection reference signal is obtained according to the energy intensity value of the detector in the region without the phantom and the slit and the energy intensity value of the detector in the region with the phantom and the slit in the process of computer tomography. The phantom is a phantom simulating a target object in the process of computer tomography. The phantom can be made of Teflon, water or other materials, and the thickness of the phantom is greater than or equal to 3 mm to simulate the thickness of human tissue.

[0116] In an optional embodiment, the fitting module 4 is further configured to convert the original scanning data into projection data, and configured to input the projection data into the polynomial fitting result to obtain projection correction data.

[0117] wherein the coefficients of the polynomial fitting result are determined according to the projection reference signal.

[0118] In an optional embodiment, the coefficients of the polynomial fitting result are logarithmic values of a third ratio, wherein the third ratio is a ratio of the energy intensity value of the detector in the region without the phantom and the energy intensity value of the detector in the region with the phantom.

[0119] In an optional embodiment, the coefficients of the polynomial fitting result are logarithmic values of a third ratio and smoothed logarithmic values; the smoothed logarithmic values are logarithmic values obtained by smoothing the logarithmic values of the third ratio.

[0120] The smoothing processing mode includes a first-order exponential smoothing processing mode, a second-order exponential smoothing processing mode, a third-order exponential smoothing processing mode, and the like.

[0121] In the embodiment, the image artifact removal system further corrects the projection signal of the original scanning data by using the projection reference signal, thereby optimizing the imaging effect of the medical image.

[0122] Embodiment 3

[0123] The embodiment provides an electronic device, Figure 10 A schematic diagram of a module of the electronic device is shown. The electronic device includes a memory, a processor, and a computer program stored in the memory and executable on the processor, and the processor implements the image artifact removal method of the embodiment 1 when executing the program. Figure 10 The electronic device 30 shown is merely an example and should not impose any limitation on the functions and use range of the embodiments of the present application.

[0124] As shown in Figure 10 The electronic device 30 can be in the form of a general computing device, for example, it can be a server device. The components of the electronic device 30 can include but are not limited to the above-mentioned at least one processor 31, the above-mentioned at least one memory 32, and a bus 33 connecting different system components including the memory 32 and the processor 31.

[0125] The bus 33 includes a data bus, an address bus, and a control bus.

[0126] The memory 32 can include a volatile memory, for example, a random access memory (RAM) 321 and / or a cache memory 322, and can further include a read-only memory (ROM) 323.

[0127] The memory 32 can also include a program / utility 325 having a set (at least one) of program modules 324, including but not limited to an operating system, one or more application programs, other program modules, and program data, each of which or a combination thereof, can include implementation of a network environment as in each of these examples or some combination thereof.

[0128] The processor 31 performs a variety of functions, including executing computer program instructions stored in the memory 32, by operating in accordance with the instructions, to perform various functions and data processing, such as the image artifact removal method of embodiment 1.

[0129] The electronic device 30 can also communicate with one or more external devices 34 such as a keyboard or a pointing device, by way of Input / Output (I / O) interface 35. Further, the model generation device 30 can communicate with one or more networks, such as a local area network (LAN), a wide area network (WAN), and / or a public network, such as the Internet, by way of the network adapter 36. As Figure 10 illustrated, the network adapter 36 communicates with the other modules of the model generation device 30 by way of the bus 33. It should be appreciated that the model generation device 30 can be a part of another device or that the model generation device 30 can be a stand-alone device. Further, it should be appreciated that the model generation device 30 might not need the bus 33, and be functionally coupled to the other modules by way of the network adapter 36.

[0130] It should be noted that although several units / modules or sub-units / modules of an electronic device are mentioned in the foregoing detailed description, such a division is merely exemplary and not mandatory. Indeed, according to an embodiment of the application, the features and functionalities of two or more units / modules described above can be embodied in one unit / module. Conversely, the features and functionalities of one unit / module described above can be further divided into a plurality of units / modules.

[0131] Embodiment 4

[0132] The present embodiment provides a computer readable storage medium having stored thereon a computer program, which, when executed by a processor, implements the image artifact removal method of embodiment 1.

[0133] More specifically, the computer readable storage medium can include, but is not limited to, portable discs, hard disks, random access memories, read-only memories, erasable programmable read-only memories, optical storage devices, magnetic storage devices, or any suitable combination of the foregoing.

[0134] In a possible implementation, the present application can also be implemented in the form of a program product, which comprises program codes for causing the terminal device to execute the image de-artifact method of embodiment 1 when the program product is run on the terminal device.

[0135] Wherein the program codes for executing the present application can be written in any combination of one or more programming languages, and can be executed completely on the user device, partially on the user device, as a stand-alone software package, partially on the user device and partially on a remote device, or completely on a remote device.

[0136] Although the specific embodiments of the present application are described above, those skilled in the art should understand that this is only an illustration, and the protection scope of the present application is defined by the appended claims. Those skilled in the art can make various changes or modifications to these embodiments without departing from the principles and essence of the present application, and these changes and modifications all fall within the protection scope of the present application.

Claims

1. A method of image de-artifacting, characterized in that, The image de-artifact method comprises: obtaining original scanning data of a detector during computer tomography of a target object; using a scatter reference signal to perform artifact correction on the original scanning data containing scatter signals; wherein the scatter reference signal is obtained according to energy data of the detector in a non-slit area during computer tomography and energy data of the detector in a slit area; the step of using the scatter reference signal to perform artifact correction on the original scanning data containing scatter signals comprises: performing scatter intensity evaluation on the original scanning data to obtain original scatter signals; inputting the original scatter signals into a polynomial fitting result to obtain scatter signals; wherein coefficients of the polynomial fitting result are determined according to the scatter reference signal; removing the scatter signals from the original scanning data to obtain artifact-corrected original scanning data.

2. The image deartifacting method of claim 1, wherein, The energy data of the detector in the non-slit area comprises energy intensity values of the detector in a non-phantom non-slit area and energy intensity values of the detector in a phantom non-slit area; The energy data of the detector in the slit area comprises energy intensity values of the detector in a non-phantom slit area and energy intensity values of the detector in a phantom slit area; The phantom is a phantom simulating the target object during computer tomography.

3. The image deartifacting method of claim 2, wherein, The coefficients of the polynomial fitting result are a difference between a first ratio and a second ratio; wherein the first ratio is a ratio of the energy intensity values of the detector in the phantom non-slit area to the energy intensity values of the detector in the non-phantom non-slit area; the second ratio is a ratio of the energy intensity values of the detector in the phantom slit area to the energy intensity values of the detector in the non-phantom slit area; or, The coefficients of the polynomial fitting result are a smoothed difference of a difference between a first ratio and a second ratio; the smoothed difference is a difference obtained by smoothing the difference between the first ratio and the second ratio.

4. The image de-artifacting method of any one of claims 1-3, wherein, The image de-artifact method further comprises: using a projection reference signal to perform artifact correction on the original scanning data containing projection signals; wherein the projection reference signal is obtained according to energy intensity values of the detector in a non-phantom slit area and energy intensity values of the detector in a phantom slit area during computer tomography.

5. The image deartifacting method of claim 4, wherein, The step of using the projection reference signal to perform artifact correction on the original scanning data containing projection signals comprises: converting the original scanning data into projection data; inputting the projection data into a polynomial fitting result to obtain projection correction data; wherein coefficients of the polynomial fitting result are determined according to the projection reference signal.

6. The image deartifacting method of claim 5, wherein, The coefficients of the polynomial fitting result are a logarithmic value of a third ratio, wherein the third ratio is a ratio of the energy intensity values of the detector in the non-phantom slit area to the energy intensity values of the detector in the phantom slit area; or, The coefficients of the polynomial fitting result are a smoothed logarithmic value of a logarithmic value of a third ratio; the smoothed logarithmic value is a logarithmic value obtained by smoothing the logarithmic value of the third ratio.

7. An image deartifacting system characterized by, The image artifact removal system comprises: An acquisition module configured to acquire original scan data of a detector during a computed tomography scan of a target object; A correction module configured to perform artifact correction on the original scan data containing scatter signals using a scatter reference signal, wherein the scatter reference signal is derived from energy data of the detector in a non-slit region and energy data of the detector in a slit region during the computed tomography scan; A fitting module configured to perform scatter intensity evaluation on the original scan data to obtain original scatter signals, and configured to input the original scatter signals into a polynomial fitting result to obtain scatter signals, wherein coefficients of the polynomial fitting result are determined according to the scatter reference signal; The correction module is further configured to remove the scatter signals from the original scan data to obtain artifact-corrected original scan data.

8. An electronic device comprising a memory, a processor, and a computer program stored on the memory and executable on the processor, characterized in that, The processor executes the computer program to implement the image artifact removal method of any one of claims 1-6.

9. A computer-readable storage medium having stored thereon a computer program, characterized in that, The computer program is executed by the processor to implement the image artifact removal method of any one of claims 1-6.

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