Magnetic resonance signal processing method and device, magnetic resonance system and computer equipment

Abstract

The application relates to a magnetic resonance signal processing method and device, a magnetic resonance system and a computer device. The method comprises the following steps: acquiring initial magnetic resonance signals of a plurality of voxel points; for the initial magnetic resonance signal of each voxel point, determining a correction coefficient of an N-order phase according to the initial magnetic resonance signal of the voxel point; correcting the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the N-order phase to obtain a corrected magnetic resonance signal; determining a correction coefficient of a zero-order phase according to the corrected magnetic resonance signal, and correcting the phase of the corrected magnetic resonance signal according to the correction coefficient of the zero-order phase to obtain a target magnetic resonance signal. The magnetic resonance signal processing method can correct the N-order phase and the zero-order phase of the magnetic resonance signal in one or more dimensions, and can more effectively correct the magnetic resonance signal.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical image processing, and in particular to a magnetic resonance signal processing method and device, a magnetic resonance system and a computer device. BACKGROUND

[0002] Magnetic Resonance Imaging (MRI) is the full name of the nuclear magnetic resonance imaging technology. Magnetic resonance imaging is a diagnostic technology that uses the nuclear magnetic resonance phenomenon of certain atomic nuclei, processes the obtained magnetic resonance signals, and reconstructs images. In the actual magnetic resonance imaging process, the phase of the obtained magnetic resonance signal will be incorrect due to the influence of non-ideal factors such as background phase, radio frequency receiving coil, and hardware filtering, so it is necessary to correct the phase of the magnetic resonance signal.

[0003] In the traditional technology, after obtaining the reconstructed image, the image is layered, and the phase of the magnetic resonance signal corresponding to each layer image is corrected. However, the effectiveness of the phase correction using the method of correcting the phase of the magnetic resonance signal in the traditional technology is low. SUMMARY

[0004] Therefore, it is necessary to provide a magnetic resonance signal processing method, device, magnetic resonance system and computer device to solve the above technical problems.

[0005] In a first aspect, an embodiment of the present application provides a magnetic resonance signal processing method, comprising:

[0006] Obtaining initial magnetic resonance signals of a plurality of voxel points, for the initial magnetic resonance signal of each voxel point, determining a correction coefficient of an N-order phase according to the initial magnetic resonance signal of the voxel point; the correction coefficient of the N-order phase includes a correction coefficient of an N-order phase of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1;

[0007] Correcting the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the N-order phase to obtain a corrected magnetic resonance signal;

[0008] Determining a correction coefficient of a zero-order phase according to the corrected magnetic resonance signal, and correcting the phase of the corrected magnetic resonance signal according to the correction coefficient of the zero-order phase to obtain a target magnetic resonance signal.

[0009] In one of the embodiments, the correction coefficient of the N-order phase is determined according to the magnetic resonance signal of the voxel point, comprising:

[0010] The correction coefficient of the N-order phase is determined according to the magnetic resonance signal of the voxel point and the magnetic resonance signal of the adjacent voxel point of the voxel point.

[0011] In one of the embodiments, the method for determining the magnetic resonance signals of the neighboring voxels includes:

[0012] The coordinate value of the voxel is shifted by M steps to determine the neighboring voxels and obtain the magnetic resonance signals of the neighboring voxels; M is an integer greater than 1.

[0013] In one of the embodiments, the method for determining the correction coefficient of the Nth order phase according to the magnetic resonance signals of the voxels includes:

[0014] For each dimension, the correction coefficient of the Nth order phase in the dimension is determined according to the magnetic resonance signals of the initial voxel and the magnetic resonance signals of the neighboring voxels of the initial voxel.

[0015] In one of the embodiments, the method for determining the correction coefficient of the zeroth order phase according to the corrected magnetic resonance signals includes:

[0016] The phase histogram of the corrected magnetic resonance signals is determined.

[0017] The correction coefficient of the zeroth order phase is determined according to the phase corresponding to the peak value in the phase histogram.

[0018] In one of the embodiments, the method for correcting the phase of the magnetic resonance signals of the voxels according to the correction coefficient of the Nth order phase to obtain the corrected magnetic resonance signals includes:

[0019] The corrected phase of the Nth order phase is determined according to the correction coefficient of the Nth order phase.

[0020] The magnetic resonance signals of the voxels are multiplied with the corrected phase of the Nth order phase to obtain the corrected magnetic resonance signals.

[0021] In a second aspect, one of the embodiments of the present application provides a magnetic resonance system, which includes: a radio frequency receiving coil and an image processing device.

[0022] The image processing device is configured to receive the magnetic resonance signals received by the radio frequency receiving coil to perform the steps of the magnetic resonance signal processing method provided by the above-mentioned embodiments.

[0023] In a third aspect, one of the embodiments of the present application provides a magnetic resonance signal processing device, which includes:

[0024] The obtaining module is configured to obtain the initial magnetic resonance signals of a plurality of voxels, and for the initial magnetic resonance signals of each voxel, determine the correction coefficient of the Nth order phase according to the initial magnetic resonance signals of the voxel; the correction coefficient of the Nth order phase includes the correction coefficient of the Nth order phase of the magnetic resonance signals in one or more dimensions, and N is an integer greater than or equal to 1.

[0025] a correction module configured to correct the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the Nth order phase to obtain a corrected magnetic resonance signal;

[0026] a determination module configured to determine the correction coefficient of the zeroth order phase according to the corrected magnetic resonance signal, and correct the phase of the corrected magnetic resonance signal according to the correction coefficient of the zeroth order phase to obtain a target magnetic resonance signal.

[0027] In a fourth aspect, an embodiment of the present application provides a computer device, including a memory and a processor, the memory stores a computer program, and the processor implements the steps of the method provided in the above embodiments when executing the computer program.

[0028] In a fifth aspect, an embodiment of the present application further provides a computer readable storage medium, which stores a computer program, and the computer program is executed by a processor to implement the steps of the method provided in the above embodiments.

[0029] The embodiments of the present application provide a magnetic resonance signal processing method, device, system and computer device. The method includes: obtaining initial magnetic resonance signals of a plurality of voxel points; for each initial magnetic resonance signal of the voxel points, determining a correction coefficient of an Nth order phase according to the initial magnetic resonance signal of the voxel point; correcting the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the Nth order phase to obtain a corrected magnetic resonance signal; determining a correction coefficient of a zeroth order phase according to the corrected magnetic resonance signal, and correcting the phase of the corrected magnetic resonance signal according to the correction coefficient of the zeroth order phase to obtain a target magnetic resonance signal. The magnetic resonance signal processing method provided in the embodiments of the present application corrects the Nth order phase and the zeroth order phase of the magnetic resonance signal in one or more dimensions, compared with the traditional technology, not only can avoid the inconsistency of the inversion of the magnetic resonance signal corresponding to each layer image, but also can correct the phase of the magnetic resonance signal in multiple dimensions, improve the signal-to-noise ratio, so as to more effectively correct the phase of the magnetic resonance signal, and further improve the quality of the reconstructed image determined by using the corrected magnetic resonance signal. BRIEF DESCRIPTION OF DRAWINGS

[0030] In order to more clearly illustrate the technical solutions of the embodiments of the present application or the prior art, the drawings needed in the embodiments or the prior art description will be briefly introduced as follows. Obviously, the drawings in the following description are only some embodiments of the present application, and other drawings can be obtained by those skilled in the art without creative labor.

[0031] Figure 1 The step flowchart of the magnetic resonance signal processing method provided in an embodiment of the present application is shown in the figure;

[0032] Figure 2A step flow diagram of a magnetic resonance signal processing method is provided for an embodiment of the present application.

[0033] Figure 3 A schematic diagram of a phase histogram is provided for an embodiment of the present application.

[0034] Figure 4 A step flow diagram of a magnetic resonance signal processing method is provided for an embodiment of the present application.

[0035] Figure 5 A step flow diagram of a magnetic resonance image reconstruction method is provided for an embodiment of the present application.

[0036] Figure 6 A multi-layer image diagram of a reconstructed image is provided for an embodiment of the present application.

[0037] Figure 7 A structural diagram of a magnetic resonance system device is provided for an embodiment of the present application.

[0038] Figure 8 A structural diagram of a magnetic resonance signal processing device is provided for an embodiment of the present application.

[0039] Figure 9 A structural diagram of a computer device is provided for an embodiment of the present application. DETAILED DESCRIPTION

[0040] In order to make the above objectives, features and advantages of the present application more apparent, specific embodiments of the present application will be described in detail below with reference to the accompanying drawings. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present application. However, the present application can be practiced in a variety of ways beyond the specific embodiments described herein without departing from the scope of the present application, and it is understood that similar improvements can be made by those skilled in the art without departing from the spirit of the present application, and therefore the present application is not limited to the specific embodiments disclosed below.

[0041] The technical solutions of the present application and how the technical solutions solve the technical problems will be described in detail below with specific embodiments. The following specific embodiments can be combined with each other, and the same or similar concepts or processes may not be described again in some embodiments. The embodiments of the present application will be described below with reference to the accompanying drawings.

[0042] First, before specifically introducing the technical solutions of the embodiments of the present disclosure, the technical background or technical evolution context based on which the embodiments of the present disclosure are introduced. Magnetic resonance imaging is a diagnostic technique that uses the nuclear magnetic resonance phenomenon of certain atomic nuclei, processes the obtained nuclear magnetic resonance signals, and reconstructs images. In the actual magnetic resonance imaging process, the phase of the obtained magnetic resonance signal will be incorrect due to the influence of non-ideal factors such as radio frequency receiving coils, hardware filtering, etc., and therefore the phase of the magnetic resonance signal needs to be corrected.

[0043] In the conventional technology, after obtaining the reconstructed image, the image is layered, and the phase of the magnetic resonance signal corresponding to each layer image is corrected. The initial method is to remove the first-order phase and zero-order phase of the magnetic resonance signal corresponding to each layer image in one direction / dimension (X direction). However, simply removing the phase in one direction is far from enough, and the first-order phase and zero-order phase in other directions (such as Y direction) also need to be removed. However, using the phase correction method of the magnetic resonance signal in the conventional technology, the phase of the magnetic resonance signal corresponding to each layer image is corrected, and during reconstruction, there will be a situation that the inversion of the magnetic resonance signal corresponding to each layer image is inconsistent, thereby affecting the quality of the reconstructed image. In view of this, the present application provides a magnetic resonance signal processing method.

[0044] The magnetic resonance signal processing method provided by the present application can be implemented by a computer device. The computer device includes but is not limited to a control chip, a personal computer, a notebook computer, a smart phone, a tablet computer and a portable wearable device. The method provided by the present application can be implemented by JAVA software, and can also be applied to other software.

[0045] Please refer to Figure 1 An embodiment of the present application provides a magnetic resonance signal processing method. The embodiment takes a computer device as the execution subject to describe the magnetic resonance signal processing method in detail, and the steps of the method include:

[0046] Step 100, obtaining initial magnetic resonance signals of a plurality of voxel points, for the initial magnetic resonance signal of each voxel point, determining a correction coefficient of an N-order phase according to the initial magnetic resonance signal of the voxel point; the correction coefficient of the N-order phase includes a correction coefficient of an N-order phase of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1.

[0047] The computer device obtains initial magnetic resonance signals of each voxel point respectively to obtain initial magnetic resonance signals of a plurality of voxel points. A voxel point refers to a coordinate point of the to-be-detected object, and corresponds to a basic or minimum detection unit of the to-be-detected object. When a magnetic resonance device is used for scanning, a corresponding magnetic resonance signal is generated for each coordinate point of the to-be-detected object, that is, the initial magnetic resonance signal of each voxel point. The initial magnetic resonance signals of the plurality of voxel points can be stored in a memory of the computer device, and the computer device can directly obtain the initial magnetic resonance signals in the memory when needed. The embodiment is not limited to the method of obtaining the initial magnetic resonance signals of the plurality of voxel points, as long as the function can be realized.

[0048] The computer device determines, for each initial magnetic resonance signal of the plurality of voxel points, a correction coefficient of an N-order phase of the initial magnetic resonance signal in one or more dimensions according to the initial magnetic resonance signal of the voxel point. Assuming that the correction coefficient of the N-order phase of the initial magnetic resonance signal in three dimensions is determined according to the initial magnetic resonance signal of the voxel point, the three dimensions can refer to three directions, that is, the X direction, the Y direction, and the Z direction. The value of N is related to the order of the phase in the initial magnetic resonance signal. If the order of the phase in the initial magnetic resonance signal includes the first order and the zero order, the value of N is 1. The embodiment is not limited to the method of determining the correction coefficient of the N-order phase according to the initial magnetic resonance signal of the voxel point, as long as the function can be realized.

[0049] In step 110, the phase of the magnetic resonance signal of the voxel point is corrected according to the correction coefficient of the N-order phase to obtain a corrected magnetic resonance signal.

[0050] After the computer device obtains the correction coefficient of the N-order phase of the initial magnetic resonance signal of each voxel point, the N-order phase of the initial magnetic resonance signal of the voxel point is corrected to obtain a corrected magnetic resonance signal of each voxel point, and thus a corrected magnetic resonance signal of a plurality of voxel points can be obtained. The embodiment is not limited to the specific method of correcting the N-order phase of the magnetic resonance signal of the voxel point according to the N-order correction coefficient, as long as the function can be realized.

[0051] After the computer device obtains the corrected magnetic resonance signals of all the voxel points, an intermediate three-dimensional image is determined according to the corrected magnetic resonance signals of all the voxel points. The intermediate three-dimensional image refers to an image determined according to the magnetic resonance signal after the N-order phase of the initial magnetic resonance signal is corrected.

[0052] In an optional embodiment, the computer device performs Fourier transform on the corrected magnetic resonance signals of all the voxel points to obtain the intermediate three-dimensional image.

[0053] In step 120, a correction coefficient of the zero-order phase is determined according to the corrected magnetic resonance signal, and the phase of the corrected magnetic resonance signal is corrected according to the correction coefficient of the zero-order phase to obtain a target magnetic resonance signal.

[0054] After obtaining the corrected magnetic resonance signal, the computer device determines a correction coefficient of the zero-order phase of the corrected magnetic resonance signal according to the corrected magnetic resonance signal. The phase of the initial magnetic resonance signal of the voxel point includes not only the N-order phase but also the zero-order phase. After the N-order phase of the initial magnetic resonance signal is corrected using the N-order phase coefficient to obtain the corrected magnetic resonance signal, the corrected magnetic resonance signal includes the zero-order phase. After the correction coefficient of the zero-order phase is determined, the computer device corrects the zero-order phase of the corrected magnetic resonance signal using the correction coefficient, and a target magnetic resonance signal that removes the N-order phase and the zero-order phase can be obtained. The method of determining the correction coefficient of the zero-order phase according to the corrected magnetic resonance signal and the method of correcting the phase of the corrected magnetic resonance signal according to the correction coefficient of the zero-order phase are not limited in this embodiment, as long as the functions thereof can be implemented.

[0055] The magnetic resonance signal processing method provided in the embodiments of this application obtains the initial magnetic resonance signals of a plurality of voxel points. For the initial magnetic resonance signal of each voxel point, a correction coefficient of an N-order phase is determined according to the initial magnetic resonance signal of the voxel point. The phase of the magnetic resonance signal of the voxel point is corrected according to the correction coefficient of the N-order phase to obtain a corrected magnetic resonance signal. A correction coefficient of a zero-order phase is determined according to the corrected magnetic resonance signal, and the phase of the corrected magnetic resonance signal is corrected according to the correction coefficient of the zero-order phase to obtain a target magnetic resonance signal. The magnetic resonance signal processing method provided in the embodiments of this application corrects the N-order phase and the zero-order phase of the magnetic resonance signal in one or more dimensions. Compared with the traditional technology, the method can not only avoid the inconsistency of the inversion of the magnetic resonance signal corresponding to each layer image, but also correct the phase of the magnetic resonance signal in multiple dimensions, improve the signal-to-noise ratio, and thus can more effectively correct the phase of the magnetic resonance signal, and further improve the quality of the reconstructed image determined using the corrected magnetic resonance signal.

[0056] In one embodiment, a possible implementation of determining the correction coefficient of the N-order phase according to the magnetic resonance signal of the voxel point includes:

[0057] The correction coefficient of the N-order phase is determined according to the magnetic resonance signal of the voxel point and the magnetic resonance signal of the adjacent voxel point of the voxel point.

[0058] For the magnetic resonance signal of each voxel point, the computer device determines the correction coefficient of the N-order phase of the magnetic resonance signal of the voxel point according to the magnetic resonance signal of the voxel point and the magnetic resonance signal of the adjacent voxel point of the voxel point.

[0059] In an optional embodiment, the method for determining the magnetic resonance signals of the neighboring voxels of the voxel point comprises: the computer device determining, as the neighboring voxels, the voxels closest to the voxel point among all the voxels, and acquiring the magnetic resonance signals of the neighboring voxels.

[0060] In an embodiment, a possible implementation of determining the magnetic resonance signals of the neighboring voxels comprises:

[0061] The coordinate value of the voxel point is shifted by M steps to determine the neighboring voxels and acquire the magnetic resonance signals of the neighboring voxels; M is an integer greater than 1.

[0062] When determining the magnetic resonance signals of the neighboring voxels of the voxel point, the computer device needs to first determine the neighboring voxels of the voxel point and then acquire the magnetic resonance signals of the neighboring voxels. The computer device determines the neighboring voxels by shifting the coordinate value of the voxel point by M steps. The value of M can be set by the staff according to the actual situation. Alternatively, the M steps can refer to the distance between two adjacent unit voxels.

[0063] In this embodiment, the computer device determines the neighboring voxels by shifting the coordinate value of the voxel point by M steps, which makes the correction coefficient of the Nth-order phase more accurate, thereby enabling more effective correction of the phase of the magnetic resonance signals.

[0064] In an embodiment, a possible implementation of determining the correction coefficient of the Nth-order phase according to the magnetic resonance signals of the voxel point comprises:

[0065] For each dimension, the correction coefficient of the Nth-order phase in the dimension is determined according to the magnetic resonance signals of the initial voxel point and the magnetic resonance signals of the neighboring voxels of the voxel point. The neighboring voxels refer to the voxels adjacent to the voxel point in any dimension (such as the X-direction dimension, the Y-direction dimension, or the Z-direction dimension).

[0066] The correction coefficient of the Nth-order phase includes the correction coefficient of the Nth-order phase of the initial magnetic resonance signals in three dimensions, that is, the computer device needs to determine the correction coefficient of the Nth-order phase of the magnetic resonance signals in three dimensions according to the magnetic resonance signals of the voxel point. In other words, for each dimension of the magnetic resonance signals, the computer device determines the correction coefficient of the Nth-order phase in the dimension according to the magnetic resonance signals of the initial voxel point and the magnetic resonance signals of the neighboring voxels of the initial voxel point.

[0067] Optionally, the three dimensions of the magnetic resonance signal are X direction, Y direction and Z direction. For the X direction, the computer device determines the correction coefficient of the Nth order phase in the X direction according to the magnetic resonance signal of the initial voxel point and the magnetic resonance signals of the adjacent voxel points of the initial voxel point in the X direction. For the Y direction, the computer device determines the correction coefficient of the Nth order phase in the Y direction according to the magnetic resonance signal of the initial voxel point and the magnetic resonance signals of the adjacent voxel points of the initial voxel point in the Y direction. For the Z direction, the computer device determines the correction coefficient of the Nth order phase in the Z direction according to the magnetic resonance signal of the initial voxel point and the magnetic resonance signals of the adjacent voxel points of the initial voxel point in the Z direction.

[0068] In an optional embodiment, the initial magnetic resonance signal of the voxel point (the signal collected by the magnetic resonance receiving coil) can be represented as wherein x, y and z represent the coordinate values of the three dimensions (directions) of the initial magnetic resonance signal; f(x, y, z) represents the magnetic resonance signal generated by the hydrogen proton nuclear spin of the voxel point, which is affected by the non-uniformity of the main magnetic field, the non-uniformity of the receiving coil sensitivity and the digital-to-analog conversion circuit, so that the initial magnetic resonance signal of the voxel point received by the magnetic resonance receiving coil will have a phase shift relative to the magnetic resonance signal generated by the hydrogen proton nuclear spin of the voxel point. In this embodiment wherein φ0 represents the zeroth order phase of the initial magnetic resonance signal, φ0 represents the correction coefficient of the zeroth order phase, e i(·) represents the first order phase of the magnetic resonance signal, ∈1 represents the correction coefficient of the first order phase in the X direction, ∈2 represents the correction coefficient of the first order phase in the Y direction, and ∈3 represents the correction coefficient of the first order phase in the Z direction. The calculation formula of the correction coefficient of the first order phase in the X direction is represented as:

[0069] wherein n is the step of translation, represents the magnetic resonance signal of the adjacent voxel point of the initial magnetic resonance signal in the X direction, E(·) represents the mean operation, * represents the conjugate operation, arg represents the complex amplitude angle operation / inverse trigonometric function operation, and n is a positive integer. The calculation formula of the correction coefficient of the first order phase in the Y direction is represented as:

[0070] wherein, represents the magnetic resonance signal of the adjacent voxel point of the initial magnetic resonance signal in the Y direction. The calculation formula of the correction coefficient of the first order phase in the Z direction is represented as: wherein, represents the magnetic resonance signal of the adjacent voxel point of the initial magnetic resonance signal in the Z direction.

[0071] Please refer to Figure 2In one embodiment, a possible implementation of the correction coefficient of the zero-order phase determined according to the corrected magnetic resonance signal includes:

[0072] Step 200, determine a phase histogram of the corrected magnetic resonance signal.

[0073] After obtaining the corrected magnetic resonance signal, the computer device arranges the corrected magnetic resonance signal according to coordinate values in space, determines the number of pixel points (coordinate values) corresponding to each phase (considering the periodicity of the signal, the statistical range of the phase is limited to [-π, π]), and obtains a phase histogram. The abscissa of the phase histogram is the phase, and the ordinate is the distribution number of the pixel points corresponding to each phase.

[0074] Step 210, determine the correction coefficient of the zero-order phase according to the phase corresponding to the peak value in the phase histogram.

[0075] After obtaining the phase histogram, the computer device obtains the phase corresponding to the peak value in the phase histogram, and determines the correction coefficient of the zero-order phase according to the phase corresponding to the peak value.

[0076] The method for determining the correction coefficient of the zero-order phase provided in this embodiment is simple in operation and easy to implement.

[0077] In an optional embodiment, the phase histogram of the corrected magnetic resonance signal is as shown in Figure 3 The computer device takes the phase corresponding to the peak value in the phase histogram as the correction coefficient of the zero-order phase.

[0078] Please refer to Figure 4 In one embodiment, the method for correcting the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the N-order phase to obtain the corrected magnetic resonance signal includes:

[0079] Step 400, determine the correction phase of the N-order phase according to the correction coefficient of the N-order phase.

[0080] Step 410, perform multiplication operation processing on the magnetic resonance signal of the voxel point and the correction phase of the N-order phase to obtain the corrected magnetic resonance signal.

[0081] After obtaining the correction coefficient of the N-order phase, the computer device determines the correction phase according to the correction coefficient. Optionally, the correction coefficient of the N-order phase includes the correction coefficient of the N-order phase of the initial magnetic resonance signal in three dimensions, and then the correction phase of the N-order phase in three dimensions can be obtained. After obtaining the correction phase of the N-order phase, the computer device calculates the product of the magnetic resonance signal of the voxel point and the correction phase of the N-order phase, and the corrected magnetic resonance signal can be obtained.

[0082] In an optional embodiment, the correction phase of the first-order phase is represented as The corrected magnetic resonance signal can be represented as wherein, The corrected magnetic resonance signal is represented.

[0083] In an optional embodiment, after determining the correction coefficient of the zeroth order phase, the computer device determines a corrected phase of the zeroth order phase according to the correction coefficient, and performs operation processing on the corrected magnetic resonance signal and the corrected phase of the zeroth order phase to obtain a target magnetic resonance signal. The corrected phase of the zeroth order phase can be represented as The target magnetic resonance signal can be represented as wherein, is a signal obtained by removing the first order phase and the zeroth order phase from the initial magnetic resonance signal, i.e., the target magnetic resonance signal.

[0084] See Figure 5 An embodiment of the present application also provides a magnetic resonance image reconstruction method, comprising:

[0085] Step 500: obtaining initial magnetic resonance signals of a plurality of voxel points, and for each initial magnetic resonance signal of a voxel point, determining a correction coefficient of an Nth order phase according to the initial magnetic resonance signal of the voxel point; the correction coefficient of the Nth order phase includes a correction coefficient of an Nth order phase of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1;

[0086] Step 510: correcting the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the Nth order phase to obtain a corrected magnetic resonance signal;

[0087] Step 520: performing phase statistics on the corrected magnetic resonance signal to obtain a phase histogram;

[0088] Step 530: determining a correction coefficient of a zeroth order phase according to the phase histogram, and correcting the phase of the corrected magnetic resonance signal according to the correction coefficient of the zeroth order phase to obtain a target magnetic resonance signal;

[0089] Step 540: performing real part reconstruction on the target magnetic resonance signal to obtain a target magnetic resonance image.

[0090] In an optional embodiment, in the process of magnetic resonance imaging of the inner ear, the multi-layer image of the reconstructed image obtained by using the magnetic resonance signal processed by the method provided in the present application is as shown in Figure 6The upper image of each layer is determined using the target magnetic resonance signal obtained by the method provided in the embodiments of the present application, and the lower image of each layer is determined using the magnetic resonance signal after phase correction by the conventional technique. Since the T1 (longitudinal relaxation) of fat is short, the signal should be positive, i.e., the outermost circle of the image is a relatively bright area. It can be seen from the outermost bright fat and the middle black area that the signal flip of the upper image of each layer is correct, while the signal flip of the lower image of the 1st layer, the 7th layer, the 8th layer, and the 9th-10th layers is incorrect. Therefore, the method for processing magnetic resonance signal provided in the embodiments of the present application can more effectively correct the phase of the magnetic resonance signal, thereby improving the quality of the reconstructed image obtained.

[0091] It should be understood that, although each step in the flowchart in the figure is shown in sequence according to the arrow, the steps are not necessarily executed in sequence according to the arrow. Unless otherwise specified herein, the execution of the steps is not strictly limited in sequence, and the steps can be executed in other sequences. Moreover, at least part of the steps in the figure can include multiple sub-steps or multiple stages, which are not necessarily executed at the same time, but can be executed at different times, and the execution sequence of the sub-steps or stages is not necessarily sequential, but can be alternately or alternately executed with at least part of other steps or sub-steps or stages of other steps.

[0092] Please refer to Figure 7 An embodiment of the present application provides a magnetic resonance system 10, which comprises a radio frequency receiving coil 11 and an image processing device 12. The image processing device 12 is configured to receive the magnetic resonance signal received by the radio frequency receiving coil 11, to perform the steps of the method for processing magnetic resonance signal provided in the above embodiments. The image processing device 12 is further configured to determine a reconstructed image according to the target magnetic resonance signal after obtaining the target magnetic resonance signal. The present embodiment does not limit the specific structure of the image processing device 12 as long as it can realize the functions thereof.

[0093] The magnetic resonance system 10 provided in the present embodiment performs the steps of the method for processing magnetic resonance signal provided in the above embodiments, and therefore has all the beneficial effects of the method for processing magnetic resonance signal, which will not be described herein again.

[0094] In an alternative embodiment, the magnetic resonance system 10 further comprises a magnet, gradient coils and radio frequency transmit coils. In the strong magnetic field provided by the magnet, hydrogen nuclei are transferred from a state of thermal equilibrium in which they are randomly oriented to a state in which they are partially aligned with the direction of the main magnetic field, the difference between the two forming a net magnetization vector. The hydrogen nuclei precess around the main magnetic field, the precession frequency being proportional to the strength of the magnetic field. The gradient coils generate magnetic fields whose strength varies with spatial position, for spatial encoding of the signal. The radio frequency transmit coils flip the hydrogen nuclei from the direction of the main magnetic field to the transverse plane, and the radio frequency receive coils can induce a current signal, i.e. a magnetic resonance signal, from the radio frequency transmit coils as the hydrogen nuclei precess around the main magnetic field.

[0095] See Figure 8 An embodiment of the present application provides a magnetic resonance signal processing apparatus 20, which comprises an acquisition module 21, a correction module 22 and a determination module 23. Wherein,

[0096] The acquisition module 21 is configured to acquire initial magnetic resonance signals of a plurality of voxel points, and for each initial magnetic resonance signal of a voxel point, determine a correction coefficient of an Nth-order phase according to the initial magnetic resonance signal of the voxel point; the correction coefficient of the Nth-order phase comprises a correction coefficient of an Nth-order phase of the magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1;

[0097] The correction module 22 is configured to correct the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the Nth-order phase, to obtain a corrected magnetic resonance signal;

[0098] The determination module 23 is configured to determine a correction coefficient of a zeroth-order phase according to the corrected magnetic resonance signal, and correct the corrected magnetic resonance signal according to the correction coefficient of the zeroth-order phase, to obtain a target magnetic resonance signal.

[0099] In an embodiment, the determination module 21 is configured to determine the correction coefficient of the Nth-order phase according to the magnetic resonance signal of the voxel point and the magnetic resonance signal of a neighboring voxel point of the voxel point.

[0100] In an embodiment, the acquisition module 21 is specifically configured to translate the coordinate value of the voxel point by M steps, determine a neighboring voxel point, and acquire the magnetic resonance signal of the neighboring voxel point; M is an integer greater than 1.

[0101] In an embodiment, the acquisition module 21 is specifically further configured to, for each dimension, determine a correction coefficient of the Nth-order phase in the dimension according to the magnetic resonance signal of the initial voxel point and the magnetic resonance signal of a neighboring voxel point of the initial voxel point; the neighboring voxel point refers to a voxel point adjacent to the voxel point in the dimension.

[0102] In an embodiment, the determination module 23 is specifically configured to determine a phase histogram of the corrected magnetic resonance signal; and determine the correction coefficient of the zeroth-order phase according to a phase corresponding to a peak value in the phase histogram.

[0103] In one embodiment, the correction module 22 is specifically configured to determine a corrected phase of the Nth order phase according to the correction coefficient of the Nth order phase; and perform multiplication processing on the magnetic resonance signal of the voxel point and the corrected phase of the Nth order phase to obtain a corrected magnetic resonance signal.

[0104] The specific limitations of the magnetic resonance signal processing device 10 described above can refer to the limitations of the magnetic resonance signal processing method described above, and will not be repeated here. Each module in the magnetic resonance signal processing device 10 can be realized by software, hardware and their combinations. Each device, module or unit described above can be embedded in or independent of the processor in the computer device in hardware form, or can be stored in the memory in the computer device in software form, so that the processor calls and executes the corresponding operations of each device or module.

[0105] Please refer to Figure 9 In one embodiment, a computer device is provided, which can be a server, and the internal structure diagram thereof can be as shown in Figure 9 The computer device includes a processor, a memory, a network interface and a database connected through a system bus. The processor of the computer device is used to provide computing and control capabilities. The memory of the computer device includes a non-volatile storage medium and an internal memory. The non-volatile storage medium stores an operating system, a computer program and a database. The internal memory provides an environment for the operating system and the computer program in the non-volatile storage medium to run. The database of the computer device is used to store the magnetic resonance signals of a plurality of voxel points and the like. The network interface of the computer device is used to communicate with the external terminal through the network connection. The computer device is executed by the processor to implement a magnetic resonance signal processing method.

[0106] Those skilled in the art can understand Figure 9 The structure shown in the figure is only a block diagram of part of the structure related to the scheme of the present application, and does not constitute a limitation on the computer device to which the scheme of the present application is applied. The specific computer device can include more or fewer components than those shown in the figure, or combine certain components, or have a different component arrangement.

[0107] In one embodiment, a computer device is provided, which includes a memory and a processor, the memory stores a computer program, and the processor implements the following steps when executing the computer program:

[0108] Obtaining initial magnetic resonance signals of a plurality of voxel points, for each initial magnetic resonance signal of the voxel point, determining a correction coefficient of an Nth order phase of the voxel point according to the initial magnetic resonance signal of the voxel point; the correction coefficient of the Nth order phase includes a correction coefficient of an Nth order phase of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1;

[0109] correct the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the Nth order phase, to obtain a corrected magnetic resonance signal;

[0110] determine the correction coefficient of the zeroth order phase according to the corrected magnetic resonance signal, and correct the phase of the corrected magnetic resonance signal according to the correction coefficient of the zeroth order phase, to obtain a target magnetic resonance signal.

[0111] In one embodiment, the processor further implements the following steps when executing the computer program: determining the correction coefficient of the Nth order phase according to the magnetic resonance signal of the voxel point and the magnetic resonance signal of the neighboring voxel point of the voxel point.

[0112] In one embodiment, the processor further implements the following steps when executing the computer program: translating the coordinate value of the voxel point by M steps to determine the neighboring voxel point and obtain the magnetic resonance signal of the neighboring voxel point; M is an integer greater than 1.

[0113] In one embodiment, the processor further implements the following steps when executing the computer program: for each dimension, determining the correction coefficient of the Nth order phase in the dimension according to the magnetic resonance signal of the initial voxel point and the magnetic resonance signal of the neighboring voxel point of the initial voxel point; the neighboring voxel point refers to the voxel point adjacent to the voxel point in the dimension.

[0114] In one embodiment, the processor further implements the following steps when executing the computer program: determining the phase histogram of the corrected magnetic resonance signal; determining the correction coefficient of the zeroth order phase according to the phase corresponding to the peak value in the phase histogram.

[0115] In one embodiment, the processor further implements the following steps when executing the computer program: determining the correction phase of the Nth order phase according to the correction coefficient of the Nth order phase; performing multiplication processing on the magnetic resonance signal of the voxel point and the correction phase of the Nth order phase, to obtain the corrected magnetic resonance signal.

[0116] In one embodiment, a computer readable storage medium is provided, and the computer readable storage medium stores a computer program. The computer program is executed by a processor to implement the following steps:

[0117] obtaining initial magnetic resonance signals of a plurality of voxel points, and for each initial magnetic resonance signal of a voxel point, determining a correction coefficient of an Nth order phase according to the initial magnetic resonance signal of the voxel point; the correction coefficient of the Nth order phase includes a correction coefficient of the Nth order phase of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1;

[0118] correcting the phase of the magnetic resonance signal of the voxel point according to the correction coefficient of the Nth order phase, to obtain a corrected magnetic resonance signal;

[0119] The correction coefficient of the zero-order phase is determined according to the corrected magnetic resonance signal, and the phase of the corrected magnetic resonance signal is corrected according to the correction coefficient of the zero-order phase, so as to obtain a target magnetic resonance signal.

[0120] In one embodiment, the computer program, when executed by the processor, further implements the following steps: determining the correction coefficient of the N-order phase according to the magnetic resonance signal of the voxel point and the magnetic resonance signal of the adjacent voxel point of the voxel point.

[0121] In one embodiment, the computer program, when executed by the processor, further implements the following steps: translating the coordinate value of the voxel point by M steps to determine the adjacent voxel point and obtain the magnetic resonance signal of the adjacent voxel point; M is an integer greater than 1.

[0122] In one embodiment, the computer program, when executed by the processor, further implements the following steps: for each dimension, determining the correction coefficient of the N-order phase in the dimension according to the magnetic resonance signal of the initial voxel point and the magnetic resonance signal of the adjacent voxel point of the initial voxel point; the adjacent voxel point refers to the voxel point adjacent to the voxel point in the dimension.

[0123] In one embodiment, the computer program, when executed by the processor, further implements the following steps: determining the phase histogram of the corrected magnetic resonance signal; and determining the correction coefficient of the zero-order phase according to the phase corresponding to the peak value in the phase histogram.

[0124] In one embodiment, the computer program, when executed by the processor, further implements the following steps: determining the corrected phase of the N-order phase according to the correction coefficient of the N-order phase; and performing multiplication processing on the magnetic resonance signal of the voxel point and the corrected phase of the N-order phase to obtain the corrected magnetic resonance signal.

[0125] Those skilled in the art can understand that all or part of the processes in the above-mentioned embodiment methods can be completed by instructing the relevant hardware through a computer program. The computer program can be stored in a non-volatile computer readable storage medium, and when the computer program is executed, the processes of the above-mentioned embodiments of the methods can be included. Any reference to memory, storage, databases, or other media in the embodiments provided by the present application can include non-volatile and / or volatile memory. Non-volatile memory can include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM), or flash memory. Volatile memory can include random access memory (RAM) or external cache memory. As an illustration but not limitation, RAM is available in many forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (DDR SDRAM), enhanced SDRAM (ESDRAM), synchronous link (Synchlink) DRAM (SLDRAM), memory bus (Rambus) direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM), etc.

[0126] Any combination of the technical features of the above embodiments can be made, and in order to make the description simple, not all possible combinations of the technical features in the above embodiments are described, however, as long as the combination of the technical features does not exist, it should be considered as the scope of the present application.

[0127] The above embodiments only express several implementation manners of the present application, and the description is more specific and detailed, but it should not be understood as a limitation on the scope of the patent of the present application. It should be pointed out that for ordinary skilled in the art, without departing from the concept of the present application, a number of modifications and improvements can be made, which are all within the protection scope of the present application. Therefore, the protection scope of the patent of the present application should be subject to the appended claims.

Claims

1. A method of magnetic resonance signal processing, characterized by, The method comprises the following steps: acquiring initial magnetic resonance signals of a plurality of voxel points, and determining, for each initial magnetic resonance signal of the voxel points, correction coefficients of N-order phases according to the initial magnetic resonance signal of the voxel point; the correction coefficients of the N-order phases comprise correction coefficients of N-order phases of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1; correcting the phase of the initial magnetic resonance signal of the voxel point according to the correction coefficients of the N-order phases to obtain a corrected magnetic resonance signal; determining correction coefficients of zero-order phases according to the corrected magnetic resonance signal, and correcting the phase of the corrected magnetic resonance signal according to the correction coefficients of the zero-order phases to obtain a target magnetic resonance signal; wherein the step of determining the correction coefficients of the N-order phases according to the initial magnetic resonance signal of the voxel point comprises the step of determining the correction coefficients of the N-order phases according to the initial magnetic resonance signal of the voxel point and initial magnetic resonance signals of adjacent voxel points of the voxel point; the step of determining the correction coefficients of the zero-order phases according to the corrected magnetic resonance signal comprises the steps of determining a phase histogram of the corrected magnetic resonance signal, and determining the correction coefficients of the zero-order phases according to phases corresponding to peak values in the phase histogram.

2. The method of claim 1, wherein, The method for determining the initial magnetic resonance signals of the adjacent voxel points comprises the steps of: translating the coordinate value of the voxel point by M steps to determine the adjacent voxel points and acquire the initial magnetic resonance signals of the adjacent voxel points; M is an integer greater than 1.

3. The method of claim 1, wherein, the step of determining the correction coefficients of the N-order phases according to the initial magnetic resonance signal of the voxel point comprises the step of: for each dimension, determining the correction coefficient of the N-order phase in the dimension according to the initial magnetic resonance signal of the voxel point and initial magnetic resonance signals of adjacent voxel points of the voxel point.

4. The method of claim 1, wherein, the step of correcting the phase of the initial magnetic resonance signal of the voxel point according to the correction coefficients of the N-order phases to obtain a corrected magnetic resonance signal comprises the steps of: determining a corrected phase of the N-order phase according to the correction coefficients of the N-order phases; performing multiplication processing on the initial magnetic resonance signal of the voxel point and the corrected phase of the N-order phase to obtain the corrected magnetic resonance signal.

5. The method of claim 1, wherein, the step of correcting the phase of the corrected magnetic resonance signal according to the correction coefficients of the zero-order phases to obtain a target magnetic resonance signal comprises the steps of: determining a corrected phase of the zero-order phase according to the correction coefficients of the zero-order phases; performing operation processing on the corrected magnetic resonance signal and the corrected phase of the zero-order phase to obtain the target magnetic resonance signal.

6. A method of magnetic resonance image reconstruction, characterized by, The method comprises the following steps: acquiring initial magnetic resonance signals of a plurality of voxel points, and determining, for each initial magnetic resonance signal of the voxel points, correction coefficients of N-order phases according to the initial magnetic resonance signal of the voxel point; the correction coefficients of the N-order phases comprise correction coefficients of N-order phases of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1; correcting the phase of the initial magnetic resonance signal of the voxel point according to the correction coefficients of the N-order phases to obtain a corrected magnetic resonance signal; performing phase statistics on the corrected magnetic resonance signal to obtain a phase histogram; The correction coefficient of the zero-order phase is determined according to the phase histogram, and the phase of the corrected magnetic resonance signal is corrected according to the correction coefficient of the zero-order phase, so as to obtain a target magnetic resonance signal; The real part of the target magnetic resonance signal is reconstructed to obtain a target magnetic resonance image; The correction coefficient of the N-order phase is determined according to the initial magnetic resonance signal of the voxel point and the initial magnetic resonance signal of the adjacent voxel point of the voxel point.

7. A magnetic resonance system characterized in that, Comprise: A radio frequency receiving coil and an image processing device; The image processing device is configured to receive the magnetic resonance signal received by the radio frequency receiving coil, and perform the steps of the magnetic resonance signal processing method according to any one of claims 1-6.

8. A magnetic resonance signal processing apparatus, characterized by Comprise: An acquisition module configured to acquire initial magnetic resonance signals of a plurality of voxel points, and for each initial magnetic resonance signal of the voxel points, determine a correction coefficient of an N-order phase according to the initial magnetic resonance signal of the voxel point; the correction coefficient of the N-order phase comprises a correction coefficient of an N-order phase of the initial magnetic resonance signal in one or more dimensions, and N is an integer greater than or equal to 1; A correction module configured to correct the phase of the initial magnetic resonance signal of the voxel point according to the correction coefficient of the N-order phase, so as to obtain a corrected magnetic resonance signal; A determination module configured to determine a correction coefficient of a zero-order phase according to the corrected magnetic resonance signal, and correct the phase of the corrected magnetic resonance signal according to the correction coefficient of the zero-order phase, so as to obtain a target magnetic resonance signal; The determination module is configured to determine the correction coefficient of the N-order phase according to the initial magnetic resonance signal of the voxel point and the initial magnetic resonance signal of the adjacent voxel point of the voxel point. The determination module is specifically further configured to determine a phase histogram of the corrected magnetic resonance signal, and determine the correction coefficient of the zero-order phase according to the phase corresponding to the peak value in the phase histogram. 9.A computer device, comprising a memory and a processor, wherein the memory stores a computer program, and the computer device is configured to perform the method according to any one of claims 1-8 when the computer program is executed by the processor. The processor executes the computer program to implement the steps of the method according to any one of claims 1-6.

10. 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 steps of the method according to any one of claims 1-6.

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