Magnetic resonance imaging methods, devices and computer equipment

Abstract

This application relates to a magnetic resonance imaging method, apparatus, and computer device. The method includes determining a preset acceleration factor; based on the preset acceleration factor, determining target K-space filling regions corresponding to multiple phases of the object to be detected; filling the target K-space filling regions with magnetic resonance data acquired from the object in each phase to obtain multiple sets of K-space data; for each phase, determining synthetic K-space data using the K-space data corresponding to the phase and the data of the undersampled filling regions in the K-space data of other phases; reconstructing the synthetic K-space data to generate a magnetic resonance image of the object. The magnetic resonance imaging method of this application can improve the quality of magnetic resonance images.

Description

Technical Field

[0001] This application relates to the field of medical imaging technology, and in particular to a magnetic resonance imaging method, apparatus, computer equipment, storage medium, and computer program product. Background Technology

[0002] Magnetic resonance imaging (MRI), a multi-parameter, multi-contrast imaging technique, is one of the main imaging methods in modern medical imaging. The basic principle of MRI is to utilize the magnetic resonance phenomenon. Radio frequency excitation is used to excite hydrogen atoms in the human body, gradient fields are used for position encoding, and radio frequency receiving coils induce magnetic resonance data. This data is then filled into the K-space, and a magnetic resonance image is reconstructed using Fourier transform. To improve the widespread adoption and application of MRI technology, it is necessary to reduce the time required to acquire magnetic resonance data.

[0003] With the development of phased array coils, traditional techniques have adopted parallel sampling to reduce the acquisition time of magnetic resonance data and improve the speed of magnetic resonance imaging by combining the spatial distribution of coils.

[0004] However, traditional methods for reducing the acquisition time of magnetic resonance data reduce the amount of magnetic resonance data acquired, thus affecting the quality of magnetic resonance imaging. Summary of the Invention

[0005] Therefore, it is necessary to provide a magnetic resonance imaging method, apparatus, computer equipment, computer-readable storage medium, and computer program product that can provide magnetic resonance imaging quality in response to the above-mentioned technical problems.

[0006] In a first aspect, this application provides a magnetic resonance imaging method, the method comprising:

[0007] Based on a preset acceleration factor, the target K-space filling regions corresponding to multiple phases of the detection object are determined respectively. The target K-space filling regions include the filling regions corresponding to undersampling.

[0008] The magnetic resonance data collected from the target object in each period are filled into the target K-space filling region to obtain multiple sets of K-space data;

[0009] For each phase, the composite K-space data is determined by using the K-space data corresponding to the phase and the data of the undersampled filling region in the K-space data corresponding to other phases.

[0010] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0011] In one embodiment, based on a preset acceleration factor, the target K-space filling regions corresponding to multiple phases of the detection object are determined, including:

[0012] Based on the preset acceleration multiplier, determine the first acceleration multiplier, the second acceleration multiplier, and the third acceleration multiplier;

[0013] Obtain the initial K-space filling region. Based on the symmetry of the initial K-space filling region and the first acceleration factor, perform trajectory planning on the initial K-space filling region to obtain the first K-space filling region.

[0014] Based on the second acceleration factor, trajectory planning is performed on the first K space filling region to obtain the second K space filling region;

[0015] Based on the third acceleration factor, trajectory planning is performed on the second K-space filling region to obtain the target K-space filling region.

[0016] In one embodiment, trajectory planning is performed on the second K-space filling region based on the third acceleration factor to obtain the target K-space filling region, including:

[0017] The acceleration parameters are determined based on the third acceleration factor. Based on the acceleration parameters, the trajectory is planned in the second K space using the compressed sensing algorithm to obtain the target K space filling region.

[0018] In one embodiment, reconstructing synthetic K-space data to generate a magnetic resonance image of the detected object includes:

[0019] The synthesized K-space data is reconstructed and restored to obtain the K-space data corresponding to the initial K-space filling region;

[0020] Fourier transform is performed on the K-space data corresponding to the initial K-space filling region to determine the magnetic resonance image.

[0021] In one embodiment, the synthesized K-space data is reconstructed and restored to obtain the K-space data corresponding to the initial K-space filling region, including:

[0022] Based on the third acceleration factor, the synthesized K-space data is reconstructed and restored to obtain the K-space data corresponding to the second K-space filling region;

[0023] Based on the second acceleration factor, the K-space data corresponding to the second K-space filling region is reconstructed and restored to obtain the K-space data corresponding to the first K-space filling region.

[0024] Based on the symmetry of the first acceleration factor and the initial K-space filling region, the K-space data corresponding to the first K-space filling region is reconstructed to obtain the K-space data corresponding to the initial K-space filling region.

[0025] Secondly, one embodiment of this application provides a magnetic resonance imaging method, the method comprising:

[0026] Acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes undersampled data.

[0027] For each phase, the synthesized K-space data is determined by using the K-space data corresponding to the phase and the undersampled data corresponding to the phases other than the phase itself.

[0028] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0029] In one embodiment, multiple sets of K-space data of the detected object are acquired, including:

[0030] Based on the preset acceleration factor, determine the target K-space filling regions corresponding to the multiple phases of the object being detected;

[0031] The magnetic resonance data collected from the target object in each period are filled into the target K-space filling region to obtain multiple sets of K-space data.

[0032] Thirdly, one embodiment of this application provides a magnetic resonance imaging apparatus, the apparatus comprising:

[0033] The first determining module is used to determine a preset acceleration factor and, based on the preset acceleration factor, determine the target K-space filling regions corresponding to multiple phases of the detection object, including the filling regions corresponding to undersampling.

[0034] The filling module is used to fill the target K-space filling region with the magnetic resonance data collected from the relative detection object in each period, so as to obtain multiple sets of K-space data;

[0035] The second determining module is used to determine the synthesized K-space data for each period by using the K-space data corresponding to the period and the data of the undersampled filling region in the K-space data corresponding to other periods.

[0036] The first reconstruction module is used to reconstruct the synthetic K-space data and generate a magnetic resonance image of the detected object.

[0037] Thirdly, one embodiment of this application provides a magnetic resonance imaging apparatus, the apparatus comprising:

[0038] The acquisition module is used to acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes undersampled data.

[0039] The third determining module is used to determine the synthesized K-space data for each period using the K-space data corresponding to the period and the undersampled data corresponding to the period other than the period itself.

[0040] The second reconstruction module is used to reconstruct the synthetic K-space data and generate magnetic resonance images of the detected object.

[0041] Fourthly, one embodiment of this application provides a computer device including a memory and a processor. The memory stores a computer program, and the processor executes the computer program to implement the steps of the method provided in the above embodiments.

[0042] Fifthly, one embodiment of this application provides a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the steps of the method provided in the above embodiments.

[0043] Sixthly, one embodiment of this application also provides a computer program product, including a computer program that, when executed by a processor, implements the steps of the method provided in the above embodiments.

[0044] The aforementioned magnetic resonance imaging method, apparatus, computer equipment, storage medium, and computer program product, in this method, determine a preset acceleration factor, and based on this preset acceleration factor, determine the target K-space filling regions corresponding to multiple phases of the object being detected. The method then fills the target K-space filling regions with the magnetic resonance data acquired from each phase of the object being detected, obtaining multiple sets of K-space data. For each phase, it uses the K-space data corresponding to that phase and the data from the undersampled filling regions in the K-space data of other phases to determine synthetic K-space data. The synthetic K-space data is then reconstructed to generate a magnetic resonance image of the object being detected. The magnetic resonance imaging method provided in this embodiment, for each phase, synthesizes the data from the undersampled filling regions in the K-space data of other phases with the K-space data corresponding to that phase, and then reconstructs the synthetic K-space data to generate a magnetic resonance image of the object being detected. This eliminates the need to spend a significant amount of sampling time acquiring magnetic resonance data for each phase, as the initial K-space filling region corresponding to that phase is fully filled, thus shortening the sampling time. Meanwhile, the K-space data corresponding to each period are very similar. By reconstructing the synthetic K-space data, the quality of the generated magnetic resonance image is not affected by the small amount of sampled data acquired. In other words, the magnetic resonance imaging method provided in this application can ensure the quality of magnetic resonance images while reducing the amount of magnetic resonance data acquired. Attached Figure Description

[0045] Figure 1 This is a diagram illustrating the application environment of a magnetic resonance imaging method in one embodiment.

[0046] Figure 2 This is a schematic flowchart of a magnetic resonance imaging method in one embodiment;

[0047] Figure 3This is a flowchart illustrating the steps of a magnetic resonance imaging method in another embodiment;

[0048] Figure 4 This is a schematic diagram of the initial K-space filling region in one embodiment;

[0049] Figure 5 This is a schematic diagram of the first K-space filling region in one embodiment;

[0050] Figure 6 This is a schematic diagram of the second K-space filling region in one embodiment;

[0051] Figure 7 This is a schematic diagram of the third K-space filling region in one embodiment;

[0052] Figure 8 This is a schematic diagram illustrating the division of the third K-space filling region in one embodiment;

[0053] Figure 9 This is a schematic diagram of the K-space data synthesis corresponding to the middle stage of an embodiment;

[0054] Figure 10 This is a flowchart illustrating the steps of a magnetic resonance imaging method in another embodiment;

[0055] Figure 11 This is a flowchart illustrating the steps of a magnetic resonance imaging method in another embodiment;

[0056] Figure 12 This is a flowchart illustrating the steps of a magnetic resonance imaging method in another embodiment;

[0057] Figure 13 This is a flowchart illustrating the steps of a magnetic resonance imaging method in another embodiment;

[0058] Figure 14 A magnetic resonance image in one embodiment;

[0059] Figure 15 For another embodiment, a magnetic resonance image;

[0060] Figure 16 This is a schematic diagram of the structure of a magnetic resonance imaging device in one embodiment;

[0061] Figure 17 This is a schematic diagram of the structure of a magnetic resonance imaging device in one embodiment;

[0062] Figure 18 This is an internal structural diagram of a computer device in one embodiment. Detailed Implementation

[0063] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0064] The magnetic resonance imaging method provided in this application embodiment can be applied to, for example... Figure 1 In the application scenario shown, the application environment includes a terminal 102 and a magnetic resonance imaging (MRI) device 104, wherein the terminal 102 can communicate with the MRI device 104 via a network. The terminal 102 can be, but is not limited to, various personal computers, laptops, and tablets. This embodiment does not limit the specific structure of the MRI device 104.

[0065] The technical solution of this application and how it solves the technical problems will be described in detail below with specific embodiments. These 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 this application will be described below with reference to the accompanying drawings.

[0066] Please see Figure 2 One embodiment of this application provides a magnetic resonance imaging method, which is applied to... Figure 1 Taking the terminal in the example, the explanation includes the following steps:

[0067] Step 200: Based on the preset acceleration factor, determine the target K-space filling regions corresponding to the multiple phases of the detection object. The target K-space filling regions include a first region and a second region. The first region corresponds to the full sampling region, and the second region corresponds to the undersampling region.

[0068] The preset acceleration factor is related to the acquisition time; the shorter the acquisition time, the higher the preset acceleration factor. The preset acceleration factor can be determined in advance by the staff based on actual needs and stored in the terminal's memory. Multiple phases of the detected object are determined based on the object's physiological movements. For example, when scanning the heart region of the detected object using an MRI scanner, diastole is one phase, systole is another phase, and multiple diastolic and systolic phases constitute multiple phases of the detected object. After scanning the detected object in one phase, an image corresponding to that phase can be obtained. Reconstructing multiple images corresponding to different phases yields the MRI image of the detected object. This embodiment does not limit the number of phases of the detected object.

[0069] After setting a preset acceleration factor, the terminal determines the target K-space filling region corresponding to each phase of the detected object when that preset acceleration factor can be achieved. The target K-space filling region for each phase refers to the K-space region that needs to be filled by the acquired magnetic resonance data relative to the detected object in that phase. The target K-space filling region includes a first region and a second region. The first region corresponds to the full sampling region and is located in the center of the target K-space filling region. The second region corresponds to the undersampling region and is located around the first region. The second region is the filling region corresponding to undersampling. A full sampling region means that the acquired magnetic resonance data needs to fill the entire region; an undersampling region means that the acquired magnetic resonance data can be intermittently filled within this region. The position of the first region of the target K-space is the same for each phase, but the position of the second region of the target K-space can be different for each phase.

[0070] Step 210: Fill the target K-space filling region with the magnetic resonance data collected from the relative detection object in each period to obtain multiple sets of K-space data.

[0071] After determining the target K-space filling region corresponding to each phase, the terminal fills the target K-space filling region corresponding to the acquired magnetic resonance data of the target object in that phase with the acquired data for each phase, thereby obtaining the K-space data of that phase. In this way, multiple sets of K-space data corresponding to multiple phases can be obtained.

[0072] Step 220: For each period phase, use the K-space data corresponding to the period phase and the data of the second region in the K-space data corresponding to other periods to determine the composite K-space data;

[0073] After determining the K-space data corresponding to each period, the terminal synthesizes the K-space data corresponding to each period with the data in the second region of the target K-space filling area from the K-space data of other periods to obtain the synthetic K-space data corresponding to that period. Thus, multiple synthetic K-space data corresponding to each period can be obtained.

[0074] Step 230: Reconstruct the synthetic K-space data to generate a magnetic resonance image of the detected object.

[0075] After determining the synthetic K-space data, the terminal reconstructs it to generate a magnetic resonance image of the detected object. In other words, after obtaining the synthetic K-space data corresponding to each phase, the terminal can reconstruct an image of the detected object in that phase. By performing three-dimensional reconstruction on the images corresponding to each phase, a magnetic resonance image of the detected object can be obtained. This embodiment does not limit the specific method for reconstructing the synthetic K-space data, as long as the function can be achieved.

[0076] The magnetic resonance imaging method provided in this application determines the target K-space filling regions corresponding to multiple phases of the detection by determining a preset acceleration factor; fills the target K-space filling regions with magnetic resonance data acquired from the detection object in each phase, obtaining multiple sets of K-space data; for each phase, uses the K-space data corresponding to that phase and the data of the second region in the K-space data of phases other than that phase to determine the synthetic K-space data; reconstructs the synthetic K-space to generate the magnetic resonance image of the detection object. The magnetic resonance imaging method provided in this application, for each phase, synthesizes the data of the second region in the K-space data corresponding to phases other than that phase with the K-space data corresponding to that phase, and then reconstructs the synthetic K-space data to generate the magnetic resonance image of the detection object. In this way, it is not necessary to spend a lot of sampling time acquiring magnetic resonance data in each phase, and the initial K-space filling region corresponding to that phase is fully filled, i.e., the sampling time can be shortened. At the same time, the K-space data corresponding to each phase are very similar, and by reconstructing the synthetic K-space data, the quality of the generated magnetic resonance image is not affected by the small amount of sampled data. In other words, the magnetic resonance imaging method provided in this application can reduce the amount of magnetic resonance data collected while ensuring the quality of the magnetic resonance images.

[0077] In one embodiment, such as Figure 3 As shown, this relates to a possible implementation method for determining the target K-space filling region corresponding to multiple phases of a detection object based on a preset acceleration factor. The steps include:

[0078] Step 300: Determine the first acceleration multiple, the second acceleration multiple, and the third acceleration multiple according to the preset acceleration multiple.

[0079] After determining the preset acceleration factor, the terminal divides it into a first acceleration factor, a second acceleration factor, and a third acceleration factor. That is, the sum of the first, second, and third acceleration factors equals the preset acceleration factor. Specifically, the first, second, and third acceleration factors can be the same, meaning the preset acceleration factor is divided into three equal parts; alternatively, the first, second, and third acceleration factors can be different. This embodiment does not limit the first, second, and third acceleration factors, as long as the function can be achieved.

[0080] Step 310: Obtain the initial K-space filling region. Based on the symmetry of the initial K-space filling region and the first acceleration factor, perform trajectory planning on the initial K-space filling region to obtain the first K-space filling region.

[0081] The initial K-space filling region refers to the complete K-space corresponding to each phase during magnetic resonance imaging of the object being examined. The initial K-space filling region exhibits symmetry, and... (The initial K-space filling region is shown in the image.) Figure 4 As shown in the figure, the black squares represent the regions that need to be filled with magnetic resonance data. The initial K-space filling region is centrally symmetric. Figure 4 In this context, Ky represents phase coding, and Kz represents layer orientation coding during scanning.

[0082] After acquiring the initial K-space filling region for each phase of the detected object, the terminal performs trajectory planning on the initial K-space filling region based on its symmetry and a determined first acceleration factor. Specifically, it plans the area to be filled within the initial K-space filling region to obtain the first K-space filling region. Specifically, when planning the trajectory for the initial K-space filling region, the terminal first determines the acceleration parameters based on the first acceleration factor, and then plans the trajectory based on these acceleration parameters. The first acceleration factor and the first K-space filling region are inversely proportional; that is, the larger the first acceleration factor, the smaller the first K-space filling region. The first K-space filling region is as follows: Figure 5 As shown, from Figure 5 It can be seen that the first K-space filling region is the region to the right of the initial K-space filling region.

[0083] Step 320: Based on the second acceleration factor and the parallel acquisition method, perform trajectory planning on the first K-space filling region to obtain the second K-space filling region.

[0084] The parallel acquisition method improves the scanning speed by using a multi-channel coil to perform regular undersampling in the K-space.

[0085] Specifically, after obtaining the second acceleration factor, the terminal can determine the density of the first K-space reduced by using a parallel acquisition method when the scanning speed of the detected object needs to reach the second acceleration factor. Based on this density, trajectory planning can be performed on the first K-space filling region to obtain the second K-space filling region. The second K-space filling region is as follows: Figure 6 As shown, from Figure 6 It can be seen that the second K-space filling region is obtained by reducing the density of the first K-space filling region.

[0086] Step 330: Perform trajectory planning on the second K-space filling region based on the third acceleration factor to obtain the third K-space filling region; determine the target K-space filling region based on the third K-space filling region.

[0087] After obtaining the third acceleration factor, the terminal performs trajectory planning on the obtained second K-space filling region based on the third acceleration factor to ensure that the scanning speed of the detected object reaches the third acceleration factor. This embodiment does not limit the specific method of trajectory planning for the second K-space filling region based on the third acceleration factor, as long as the function is achieved. The third K-space filling region is as follows: Figure 7 As shown, comparison Figure 6 and Figure 7 It can be seen from this that Figure 7 The black square area (filled area) in the middle is relative to Figure 6 The area of ​​black squares in the image has been reduced.

[0088] After obtaining the third K-space filling region, the terminal determines the target K-space filling region based on it. Specifically, the terminal can divide the third K-space filling region according to the number of phases during the scanning process of the detection object to obtain the target K-space filling region corresponding to each phase. This embodiment does not limit the specific method of dividing the third K-space filling region, as long as it can achieve its function.

[0089] In an optional embodiment, the terminal may divide the third K-space filling region according to the number of phases by distributing it evenly, such as... Figure 8 As shown, there are 8 phases, dividing the second region of the third K-space filling region into 9 parts. Figure 8 The central region is the first region of the target K-space filling region. Figure 8 At least one part of the outer region can be a second region that fills the target K space corresponding to a period.

[0090] In a specific embodiment, such as Figure 9 As shown, by combining the K-space data corresponding to phase 1 and the K-space data corresponding to phase 2, we can obtain the composite data corresponding to phase 1 and the composite data corresponding to phase 2.

[0091] In this embodiment, to achieve a preset acceleration factor for scanning the target object, the preset acceleration factor is divided into a first acceleration factor, a second acceleration factor, and a third acceleration factor. For each acceleration factor, a trajectory is planned for the initial K-space filling region of each phase of the target object using a different method to obtain a third K-space filling region. The target K-space filling region is then determined based on the third K-space filling region. This reduces the final target K-space filling region, thus requiring less magnetic resonance data to be acquired, thereby shortening the scanning time.

[0092] In one embodiment, a possible implementation method for obtaining a target K-space filling region by trajectory planning of a second K-space filling region based on a third acceleration factor includes the following steps:

[0093] The acceleration parameters are determined based on the third acceleration factor. Based on the acceleration parameters, the trajectory is planned in the second K space using the compressed sensing algorithm to obtain the target K space filling region.

[0094] Compressed sensing is a new sampling theory that uses the sparsity of the sampled signal to obtain discrete samples of the signal by random sampling at a rate lower than the Nyquist sampling rate.

[0095] After determining the third acceleration factor, the terminal determines the acceleration parameters required for trajectory planning of the second K-space filling region using the compressed sensing algorithm, based on this third acceleration factor, to achieve the second acceleration factor when scanning the target object. The terminal then uses the compressed sensing algorithm to plan the trajectory of the second K-space according to the determined acceleration parameters, thus obtaining the target K-space filling region.

[0096] In an optional embodiment, when the compressed sensing algorithm is used to reduce the first K-space filling region, random sampling is performed, and the terminal can perform trajectory planning for the second K-space filling region in a regular manner through methods such as variable density or Latin hypercube.

[0097] In one embodiment, such as Figure 10 As shown, a possible implementation method for reconstructing synthetic K-space data and generating magnetic resonance images of the detected object includes the following steps:

[0098] Step 101: Reconstruct and restore the synthesized K-space data to obtain the K-space data corresponding to the initial K-space filling region.

[0099] After obtaining the synthetic K-space data corresponding to each phase, the terminal reconstructs and restores the synthetic K-space data to obtain the K-space data corresponding to the initial K-space filled region for each phase. The K-space data corresponding to the initial K-space filled region refers to the K-space data after the initial K-space filled region is completely filled with magnetic resonance data. By reconstructing and restoring the synthetic K-space data (i.e., fitting and restoring the data of the unfilled data regions in the initial K-space filled region), the terminal can obtain the magnetic resonance data of the regions in the initial K-space filled region other than the target K-space filled region, thereby obtaining the K-space data corresponding to the initial K-space filled region. The method of reconstructing and restoring the synthetic K-space data by the terminal in this embodiment is not limited, as long as its function can be achieved.

[0100] Step 102: Perform Fourier transform on the K-space data corresponding to the initial K-space filling region to determine the magnetic resonance image.

[0101] After obtaining the K-space data corresponding to the initial K-space filling region of each phase of the detected object, the terminal performs a Fourier transform on the K-space data corresponding to the initial K-space filling region of each phase to obtain the corresponding image of that phase. By performing three-dimensional reconstruction on the images corresponding to multiple phases, the magnetic resonance image of the detected object can be obtained.

[0102] In this embodiment, by reconstructing and restoring the synthesized K-space data, magnetic resonance data of the region outside the target K-space filling region in the initial K-space filling region can be obtained. In this way, the quality of the magnetic resonance image generated from the K-space data corresponding to the initial K-space filling region obtained from the reconstructed magnetic resonance data will not be affected by the short scanning time (less magnetic resonance data acquired).

[0103] In one embodiment, such as Figure 11 As shown, the synthesized K-space data is reconstructed and restored to obtain the K-space data corresponding to the initial K-space filling region, including:

[0104] Step 111: Based on the third acceleration factor, reconstruct and restore the synthesized K-space data to obtain the K-space data corresponding to the second K-space filling region.

[0105] The K-space filled region (third K-space filled region) corresponding to the synthesized K-space data is obtained by the terminal performing trajectory planning on the second K-space filled region based on the third acceleration factor. Therefore, the terminal can determine other regions within the second K-space filled region besides the target K-space filled region based on the third acceleration factor, denoted as the first unfilled region. The terminal reconstructs and restores the synthesized K-space data; specifically, it fills the first unfilled region with data from regions adjacent to the first unfilled region to obtain the K-space data corresponding to the second K-space filled region.

[0106] In an optional embodiment, the method by which the terminal fills the first unfilled area with data from the area adjacent to the first unfilled area may be to directly fill the first unfilled area with data from the area adjacent to the first unfilled area.

[0107] Step 112: Reconstruct and restore the K-space data corresponding to the second K-space filling region according to the second acceleration factor and parallel acquisition method to obtain the K-space data corresponding to the first K-space filling region.

[0108] The second K-space filling region is obtained by the terminal through trajectory planning of the first K-space filling region based on the second acceleration factor and parallel acquisition method. Then, the terminal can determine other regions within the first K-space filling region besides the second K-space filling region based on the second acceleration factor and parallel acquisition method, denoted as the second unfilled region. The terminal reconstructs and recovers the K-space data corresponding to the second K-space filling region. Specifically, by filling the second unfilled region with data from regions adjacent to it, the terminal can obtain the K-space data corresponding to the first K-space filling region. This embodiment does not limit the specific method for filling the second unfilled region with data from regions adjacent to it, as long as the function can be achieved.

[0109] Step 113: Reconstruct and restore the K-space data corresponding to the first K-space filling region based on the symmetry of the first acceleration factor and the initial K-space filling region to obtain the K-space data corresponding to the initial K-space filling region.

[0110] The first K-space filling region is determined by the terminal based on the symmetry between the first acceleration factor and the initial K-space filling region. Then, based on the symmetry between the first acceleration factor and the initial K-space filling region, the terminal can determine other regions within the initial K-space filling region besides the first K-space filling region, denoted as the third unfilled region. The terminal reconstructs and restores the data using the K-space data corresponding to the first K-space filling region. Specifically, by filling the third unfilled region with data from regions adjacent to the third unfilled region, the K-space data corresponding to the initial K-space filling region can be obtained. This embodiment does not limit the specific method for filling the third unfilled region with data from regions adjacent to the third filling region, as long as the function can be achieved.

[0111] In this embodiment, the method for determining the K-space data corresponding to the initial K-space filling region is based on the reverse thinking approach of determining the target K-space filling regions corresponding to multiple phases of the detection object based on a preset acceleration factor, which is simple and easy to understand.

[0112] Please see Figure 12 One embodiment of this application proposes a magnetic resonance imaging method, which is applied to... Figure 1 Taking the terminal in the example, the explanation includes the following steps:

[0113] Step 121: Obtain multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes full-sampled data and undersampled data.

[0114] The description of the phase parameters can be found in the above embodiments and will not be repeated here. Full sampling data refers to data obtained by fully sampling the object being detected, while undersampling refers to data obtained by undersampling the object being detected.

[0115] For each phase, after the terminal scans the target object in that phase and collects the magnetic resonance data, it fills the corresponding target K-space filling region to obtain the K-space data for that phase. This allows for the acquisition of K-space data for each phase, i.e., multiple sets of K-space data for the target object. This embodiment does not limit the specific method for obtaining multiple sets of K-space data for the target object, as long as the function can be achieved.

[0116] Step 122: For each period phase, use the corresponding K-space data and the undersampled data of other periods to determine the synthesized K-space data.

[0117] After obtaining multiple sets of K-space data corresponding to multiple periods, the terminal synthesizes the K-space data corresponding to each period with the undersampled data in the K-space data corresponding to other periods to obtain the synthesized K-space data corresponding to that period.

[0118] Step 123: Reconstruct the synthetic K-space data to generate a magnetic resonance image of the detected object.

[0119] After obtaining the synthetic K-space data for each phase, the terminal reconstructs it to detect the image of the object in that phase. By performing three-dimensional reconstruction on the image of the detected object in each phase, a magnetic resonance image of the object can be obtained. The specific method for generating the magnetic resonance image of the detected object from the reconstructed synthetic K-space data can be found in the detailed description in the above embodiments, and will not be repeated here.

[0120] The magnetic resonance imaging (MRI) method provided in this application acquires multiple sets of K-space data of the target object, with each set corresponding to data collected from the target object in one phase. For each phase, synthetic K-space data is determined using the K-space data corresponding to that phase and undersampled data corresponding to phases other than that phase. The synthetic K-space data is then reconstructed to generate an MRI image of the target object. In this MRI method, for each phase, synthetic K-space data is determined by synthesizing the K-space data corresponding to that phase and undersampled data corresponding to phases other than that phase, and then the synthetic K-space data is reconstructed to generate an MRI image of the target object. This eliminates the need for extensive sampling time to acquire MRI data in each phase; the MRI data collected in each phase is directly synthesized, shortening the sampling time. Furthermore, since the K-space data corresponding to each phase are very similar, the quality of the generated MRI image is not affected by the limited amount of sampled data acquired. In other words, the MRI method provided in this application can reduce the amount of MRI data acquired while maintaining the quality of the MRI image.

[0121] In one embodiment, such as Figure 13 As shown, a possible implementation method for acquiring multiple sets of K-space data of the detection object includes the following steps:

[0122] Step 131: Determine the target K-space filling regions corresponding to the multiple phases of the detection object according to the preset acceleration factor.

[0123] Step 132: Fill the target K-space filling region with the magnetic resonance data collected from the relative detection object in each period to obtain multiple sets of K-space data.

[0124] After acquiring a preset acceleration factor, the terminal fills in the target K-space region corresponding to each phase of the detected object when the preset acceleration factor is reached. The target K-space region for each phase includes a first region and a second region. The first region corresponds to the full-sampling region and is located in the center of the target K-space region; data filling the first region is full-sampling data. The second region corresponds to the undersampled region and is located around the first region; data filling the second region is undersampled data. After filling the magnetic resonance data collected from the detected object for each phase into the corresponding target K-space region, the terminal can obtain multiple sets of K-space data corresponding to multiple phases. A detailed description of the target K-space region corresponding to the multiple phases of the detected object can be found in the description in the above embodiments, and will not be repeated here.

[0125] In one embodiment, the fully sampled data is low-frequency data, and the undersampled data is high-frequency data. The first region is the central region of the initial K-space filling region; using low-frequency data for the fully sampled data corresponding to the central region can improve the contrast of the magnetic resonance image. The second region is the outer region of the initial K-space filling region; sampling high-frequency data for the undersampled data corresponding to the outer region can clearly display the anatomical details of the image in the magnetic resonance image.

[0126] In one embodiment, if the preset acceleration factor is 3, and a conventional acceleration method, namely parallel acquisition method, is used, and based on the symmetry of the K-space filling region, the generated magnetic resonance image is as follows: Figure 14 As shown. With a preset acceleration factor of 5, a parallel acquisition method was used, and based on the symmetry of the K-space filling region, a compressed sensing method was employed to generate the magnetic resonance image, as shown. Figure 15 As shown. Comparison Figure 14 and Figure 15 It can be seen that increasing the acceleration factor by using compressed sensing results in less magnetic resonance data acquired at the periphery of K-space, leading to blurry and unsharp images. The magnetic resonance imaging method provided in this application distributes the acceleration factor across magnetic resonance data acquired at different phases. For example, if the sampling time is doubled, distributing the acceleration across 10 phases only increases the total sampling time by 1 / 10. Compared to conventional acceleration methods, this method only doubles the sampling time while maintaining the same image quality. Therefore, the magnetic resonance imaging method provided in this application can reduce sampling time while ensuring image quality.

[0127] It should be understood that although the steps in the flowcharts of the embodiments described above are shown sequentially according to the arrows, these steps are not necessarily executed in the order indicated by the arrows. Unless explicitly stated herein, there is no strict order restriction on the execution of these steps, and they can be executed in other orders. Moreover, at least some steps in the flowcharts of the embodiments described above may include multiple steps or multiple stages. These steps or stages are not necessarily completed at the same time, but can be executed at different times. The execution order of these steps or stages is not necessarily sequential, but can be performed alternately or in turn with other steps or at least some of the steps or stages of other steps.

[0128] Based on the same inventive concept, this application also provides a magnetic resonance imaging apparatus for implementing the magnetic resonance imaging method described above. The solution provided by this apparatus is similar to the implementation described in the above method; therefore, the specific limitations in one or more magnetic resonance imaging apparatus embodiments provided below can be found in the limitations of the magnetic resonance imaging method described above, and will not be repeated here.

[0129] In one embodiment, such as Figure 16 As shown, a magnetic resonance imaging device 10 is provided, including: a first determining module 11, a filling module 12, a second determining module 13, and a first reconstruction module 14, wherein:

[0130] The first determining module 11 is used to determine a preset acceleration factor. Based on the preset acceleration factor, it determines the target K-space filling regions corresponding to multiple phases of the detection object. The target K-space filling regions include a first region and a second region. The first region corresponds to the full sampling region, and the second region corresponds to the undersampling region.

[0131] The filling module 12 is used to fill the target K-space filling region with the magnetic resonance data collected from the relative detection object in each period to obtain multiple sets of K-space data.

[0132] The second determining module 13 is used to determine the synthesized K-space data for each period by using the K-space data corresponding to the period and the data of the second region in the K-space data corresponding to other periods.

[0133] The first reconstruction module 14 is used to reconstruct the synthetic K-space data and generate a magnetic resonance image of the detected object.

[0134] In one embodiment, the first determining module 11 includes a first determining unit, a first planning unit, a second planning unit, and a third planning unit.

[0135] The first determining unit is used to determine the first acceleration multiple, the second acceleration multiple, and the third acceleration multiple based on the preset acceleration multiple; the first planning unit is used to obtain the initial K-space filling region, and perform trajectory planning on the initial K-space filling region based on the symmetry of the initial K-space filling region and the first acceleration multiple to obtain the first K-space filling region; the second planning unit is used to perform trajectory planning on the first K-space filling region based on the second acceleration multiple and the parallel acquisition method to obtain the second K-space filling region; the third planning unit is used to perform trajectory planning on the second K-space filling region based on the third acceleration multiple to obtain the target K-space filling region.

[0136] In one embodiment, the third planning unit is configured to determine acceleration parameters based on a third acceleration factor, and to perform trajectory planning in the second K-space using a compressed sensing algorithm based on the acceleration parameters to obtain a target K-space filling region.

[0137] In one embodiment, the first reconstruction module 14 includes a recovery unit and a determination unit. The recovery unit reconstructs and recovers the synthesized K-space data to obtain K-space data corresponding to the initial K-space filling region; the second determination unit performs a Fourier transform on the K-space data corresponding to the initial K-space filling region to determine the magnetic resonance image.

[0138] In one embodiment, the reconstruction unit is specifically used to reconstruct and restore the synthesized K-space data according to the third acceleration factor to obtain the K-space data corresponding to the second K-space filling region; to reconstruct and restore the K-space data corresponding to the second K-space filling region according to the second acceleration factor and the parallel acquisition method to obtain the K-space data corresponding to the first K-space filling region; and to reconstruct and restore the K-space data corresponding to the first K-space filling region according to the first acceleration factor to obtain the K-space data corresponding to the initial K-space filling region.

[0139] In one embodiment, such as Figure 17 As shown, a magnetic resonance imaging (MRI) device 20 is provided, including an acquisition module 21, a third determination module 22, and a second reconstruction module 23. Wherein,

[0140] The acquisition module 21 is used to acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes full-sampled data and undersampled data.

[0141] The third determining module 22 is used to determine the synthesized K-space data for each period using the K-space data corresponding to the period and the undersampled data corresponding to the period other than the period phase.

[0142] The second reconstruction module 23 is used to reconstruct the synthetic K-space data and generate a magnetic resonance image of the detected object.

[0143] In one embodiment, the fully sampled data is low-frequency data, and the undersampled data is high-frequency data.

[0144] In one embodiment, the acquisition module 21 is specifically used to determine the target K-space filling regions corresponding to multiple phases of the detection object according to a preset acceleration factor; and to fill the target K-space filling regions with the magnetic resonance data collected from the detection object in each phase to obtain multiple sets of K-space data.

[0145] Each module in the aforementioned magnetic resonance imaging device can be implemented entirely or partially through software, hardware, or a combination thereof. These modules can be embedded in the processor of a computer device in hardware form or independent of it, or stored in the memory of a computer device in software form, so that the processor can call and execute the operations corresponding to each module.

[0146] In one embodiment, a computer device is provided, which may be a server, and its internal structure diagram may be as follows: Figure 18 As shown, the computer device includes a processor, memory, and a network interface connected via a system bus. The processor provides computational and control capabilities. The memory includes non-volatile storage media and internal memory. The non-volatile storage media stores the operating system, computer programs, and a database. The internal memory provides an environment for the operation of the operating system and computer programs in the non-volatile storage media. The database stores magnetic resonance imaging data and preset acceleration factors, among other data. The network interface communicates with external terminals via a network connection. When executed by the processor, the computer program implements a magnetic resonance imaging method.

[0147] Those skilled in the art will understand that Figure 18 The structure shown is merely a block diagram of a portion of the structure related to the present application and does not constitute a limitation on the computer device to which the present application is applied. Specific computer devices may include more or fewer components than those shown in the figure, or combine certain components, or have different component arrangements.

[0148] In one embodiment, a computer device is provided, including a memory and a processor, wherein the memory stores a computer program, and the processor executes the computer program to perform the following steps:

[0149] A preset acceleration factor is determined. Based on the preset acceleration factor, the target K-space filling regions corresponding to multiple phases of the detection object are determined. The target K-space filling regions include a first region and a second region. The first region corresponds to the full sampling region, and the second region corresponds to the undersampling region.

[0150] The magnetic resonance data collected from the target object in each period are filled into the target K-space filling region to obtain multiple sets of K-space data;

[0151] For each period phase, the composite K-space data is determined by using the K-space data corresponding to the period phase and the data of the second region in the K-space data corresponding to other periods.

[0152] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0153] In one embodiment, when the processor executes the computer program, it further performs the following steps: determining a first acceleration factor, a second acceleration factor, and a third acceleration factor based on a preset acceleration factor; obtaining an initial K-space filling region; performing trajectory planning on the initial K-space filling region based on the symmetry of the initial K-space filling region and the first acceleration factor to obtain a first K-space filling region; performing trajectory planning on the first K-space filling region based on the second acceleration factor and a parallel acquisition method to obtain a second K-space filling region; and performing trajectory planning on the second K-space filling region based on the third acceleration factor to obtain a target K-space filling region.

[0154] In one embodiment, when the processor executes the computer program, it further performs the following steps: determining acceleration parameters based on a third acceleration factor, and using a compressed sensing algorithm to perform trajectory planning on the second K-space based on the acceleration parameters to obtain the target K-space filling region.

[0155] In one embodiment, when the processor executes the computer program, it further performs the following steps: reconstructing and restoring the synthesized K-space data to obtain the K-space data corresponding to the initial K-space filling region; performing a Fourier transform on the K-space data corresponding to the initial K-space filling region to determine the magnetic resonance image.

[0156] In one embodiment, when the processor executes the computer program, it further performs the following steps: reconstructing and restoring the synthesized K-space data according to a third acceleration factor to obtain K-space data corresponding to the second K-space filling region; reconstructing and restoring the K-space data corresponding to the second K-space filling region according to a second acceleration factor and a parallel acquisition method to obtain K-space data corresponding to the first K-space filling region; and reconstructing and restoring the K-space data corresponding to the first K-space filling region according to a first acceleration factor to obtain K-space data corresponding to the initial K-space filling region.

[0157] In one embodiment, the processor, when executing a computer program, also performs the following steps:

[0158] Acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes full-sampled data and undersampled data.

[0159] For each phase, the synthesized K-space data is determined by using the K-space data corresponding to the phase and the undersampled data corresponding to the phases other than the phase itself.

[0160] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0161] In one embodiment, the fully sampled data is low-frequency data, and the undersampled data is high-frequency data.

[0162] In one embodiment, when the processor executes the computer program, it further performs the following steps: determining the target K-space filling regions corresponding to multiple phases of the object to be detected according to a preset acceleration factor; filling the target K-space filling regions with the magnetic resonance data collected from the object to be detected in each phase to obtain multiple sets of K-space data.

[0163] In one embodiment, a computer-readable storage medium is provided having a computer program stored thereon, the computer program performing the following steps when executed by a processor:

[0164] A preset acceleration factor is determined. Based on the preset acceleration factor, the target K-space filling regions corresponding to multiple phases of the detection object are determined. The target K-space filling regions include a first region and a second region. The first region corresponds to the full sampling region, and the second region corresponds to the undersampling region.

[0165] The magnetic resonance data collected from the target object in each period are filled into the target K-space filling region to obtain multiple sets of K-space data;

[0166] For each period phase, the composite K-space data is determined by using the K-space data corresponding to the period phase and the data of the second region in the K-space data corresponding to other periods.

[0167] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0168] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: determining a first acceleration factor, a second acceleration factor, and a third acceleration factor according to a preset acceleration factor; obtaining an initial K-space filling region; performing trajectory planning on the initial K-space filling region based on the symmetry of the initial K-space filling region and the first acceleration factor to obtain a first K-space filling region; performing trajectory planning on the first K-space filling region based on the second acceleration factor and a parallel acquisition method to obtain a second K-space filling region; and performing trajectory planning on the second K-space filling region based on the third acceleration factor to obtain a target K-space filling region.

[0169] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: determining acceleration parameters based on a third acceleration factor, and using a compressed sensing algorithm to perform trajectory planning on the second K-space based on the acceleration parameters to obtain the target K-space filling region.

[0170] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: reconstructing and restoring the synthesized K-space data to obtain the K-space data corresponding to the initial K-space filling region; performing a Fourier transform on the K-space data corresponding to the initial K-space filling region to determine the magnetic resonance image.

[0171] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: reconstructing and restoring the synthesized K-space data according to a third speedup factor to obtain K-space data corresponding to the second K-space filling region; reconstructing and restoring the K-space data corresponding to the second K-space filling region according to a second speedup factor and a parallel acquisition method to obtain K-space data corresponding to the first K-space filling region; and reconstructing and restoring the K-space data corresponding to the first K-space filling region according to a first speedup factor to obtain K-space data corresponding to the initial K-space filling region.

[0172] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0173] Acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes full-sampled data and undersampled data.

[0174] For each phase, the synthesized K-space data is determined by using the K-space data corresponding to the phase and the undersampled data corresponding to the phases other than the phase itself.

[0175] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0176] In one embodiment, the fully sampled data is low-frequency data, and the undersampled data is high-frequency data.

[0177] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: determining the target K-space filling regions corresponding to multiple phases of the detection object according to a preset acceleration factor; filling the target K-space filling regions with the magnetic resonance data collected from the detection object in each phase to obtain multiple sets of K-space data.

[0178] In one embodiment, a computer program product is provided, including a computer program that, when executed by a processor, performs the following steps:

[0179] A preset acceleration factor is determined. Based on the preset acceleration factor, the target K-space filling regions corresponding to multiple phases of the detection object are determined. The target K-space filling regions include a first region and a second region. The first region corresponds to the full sampling region, and the second region corresponds to the undersampling region.

[0180] The magnetic resonance data collected from the target object in each period are filled into the target K-space filling region to obtain multiple sets of K-space data;

[0181] For each period phase, the composite K-space data is determined by using the K-space data corresponding to the period phase and the data of the second region in the K-space data corresponding to other periods.

[0182] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0183] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: determining a first acceleration factor, a second acceleration factor, and a third acceleration factor according to a preset acceleration factor; obtaining an initial K-space filling region; performing trajectory planning on the initial K-space filling region based on the symmetry of the initial K-space filling region and the first acceleration factor to obtain a first K-space filling region; performing trajectory planning on the first K-space filling region based on the second acceleration factor and a parallel acquisition method to obtain a second K-space filling region; and performing trajectory planning on the second K-space filling region based on the third acceleration factor to obtain a target K-space filling region.

[0184] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: determining acceleration parameters based on a third acceleration factor, and using a compressed sensing algorithm to perform trajectory planning on the second K-space based on the acceleration parameters to obtain the target K-space filling region.

[0185] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: reconstructing and restoring the synthesized K-space data to obtain the K-space data corresponding to the initial K-space filling region; performing a Fourier transform on the K-space data corresponding to the initial K-space filling region to determine the magnetic resonance image.

[0186] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: reconstructing and restoring the synthesized K-space data according to a third speedup factor to obtain K-space data corresponding to the second K-space filling region; reconstructing and restoring the K-space data corresponding to the second K-space filling region according to a second speedup factor and a parallel acquisition method to obtain K-space data corresponding to the first K-space filling region; and reconstructing and restoring the K-space data corresponding to the first K-space filling region according to a first speedup factor to obtain K-space data corresponding to the initial K-space filling region.

[0187] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0188] Acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes full-sampled data and undersampled data.

[0189] For each phase, the synthesized K-space data is determined by using the K-space data corresponding to the phase and the undersampled data corresponding to the phases other than the phase itself.

[0190] Reconstruct the synthetic K-space data to generate magnetic resonance images of the detected object.

[0191] In one embodiment, the fully sampled data is low-frequency data, and the undersampled data is high-frequency data.

[0192] In one embodiment, when the computer program is executed by the processor, it further performs the following steps: determining the target K-space filling regions corresponding to multiple phases of the detection object according to a preset acceleration factor; filling the target K-space filling regions with the magnetic resonance data collected from the detection object in each phase to obtain multiple sets of K-space data.

[0193] Those skilled in the art will understand that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. The computer program can be stored in a non-volatile computer-readable storage medium, and when executed, it can include the processes of the embodiments of the above methods. Any references to memory, databases, or other media used in the embodiments provided in this application can include at least one of non-volatile and volatile memory. Non-volatile memory can include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetic random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory can include random access memory (RAM) or external cache memory, etc. By way of illustration and not limitation, RAM can take many forms, such as Static Random Access Memory (SRAM) or Dynamic Random Access Memory (DRAM). The databases involved in the embodiments provided in this application may include at least one type of relational database and non-relational database. Non-relational databases may include, but are not limited to, blockchain-based distributed databases. The processors involved in the embodiments provided in this application may be general-purpose processors, central processing units, graphics processing units, digital signal processors, programmable logic devices, quantum computing-based data processing logic devices, etc., and are not limited to these.

[0194] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0195] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are specific and detailed, they should not be construed as limiting the scope of this patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this application should be determined by the appended claims.

Claims

1. A magnetic resonance imaging method, characterized in that, The method includes: Based on a preset acceleration factor, the target K-space filling regions corresponding to multiple phases of the detection object are determined respectively, and the target K-space filling regions include the filling regions corresponding to undersampling. The magnetic resonance data collected relative to the detection object in each period are filled into the target K-space filling region to obtain multiple sets of K-space data; For each period phase, the synthesized K-space data is determined by using the K-space data corresponding to the period phase and the data of the undersampled filling region in the K-space data corresponding to other periods. The synthetic K-space data is reconstructed to generate a magnetic resonance image of the detected object; The step of determining the target K-space filling regions corresponding to multiple phases of the detection object based on a preset acceleration factor includes: Based on the preset acceleration multiple, determine the first acceleration multiple, the second acceleration multiple, and the third acceleration multiple; For the first acceleration factor, the second acceleration factor, and the third acceleration factor, trajectory planning is performed on the initial K-space filling region of each phase of the detected object using different methods to obtain the third K-space filling region; The target K-space filling region is determined based on the third K-space filling region.

2. The method according to claim 1, characterized in that, The method of trajectory planning for the initial K-space filling region of each phase of the detected object using different methods for the first acceleration factor, the second acceleration factor, and the third acceleration factor to obtain the third K-space filling region includes: Obtain an initial K-space filling region, and perform trajectory planning on the initial K-space filling region based on the symmetry of the initial K-space filling region and the first acceleration factor to obtain a first K-space filling region; Based on the second acceleration factor, trajectory planning is performed on the first K-space filling region to obtain the second K-space filling region; Based on the third acceleration factor, trajectory planning is performed on the second K-space filling region to obtain the third K-space filling region.

3. The method according to claim 2, characterized in that, The step of performing trajectory planning on the second K-space filling region based on the third acceleration factor to obtain the target K-space filling region includes: Acceleration parameters are determined based on the third acceleration factor, and a trajectory is planned in the second K space using a compressed sensing algorithm based on the acceleration parameters to obtain the target K space filling region.

4. The method according to claim 2, characterized in that, The process of reconstructing the synthetic K-space data to generate a magnetic resonance image of the detected object includes: The synthesized K-space data is reconstructed and restored to obtain the K-space data corresponding to the initial K-space filling region; The magnetic resonance image is determined by performing a Fourier transform on the K-space data corresponding to the initial K-space filling region.

5. The method according to claim 4, characterized in that, The process of reconstructing and restoring the synthesized K-space data to obtain the K-space data corresponding to the initial K-space filling region includes: Based on the third acceleration factor, the synthesized K-space data is reconstructed and restored to obtain the K-space data corresponding to the second K-space filling region; Based on the second acceleration factor, the K-space data corresponding to the second K-space filling region is reconstructed and restored to obtain the K-space data corresponding to the first K-space filling region. Based on the first acceleration factor and the symmetry of the initial K-space filling region, the K-space data corresponding to the first K-space filling region is reconstructed and restored to obtain the K-space data corresponding to the initial K-space filling region.

6. A magnetic resonance imaging method, characterized in that, The method includes: Acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in a period. Each set of K-space data includes fully sampled data and undersampled data. For each period phase, the synthesized K-space data is determined using the K-space data corresponding to the period phase and the undersampled data corresponding to other periods phases. The synthetic K-space data is reconstructed to generate a magnetic resonance image of the detected object.

7. The method according to claim 6, characterized in that, The acquisition of multiple sets of K-space data of the detection object includes: Based on a preset acceleration factor, the target K-space filling regions corresponding to the multiple phases of the object being detected are determined respectively; The magnetic resonance data collected relative to the detection object in each period are filled into the target K-space filling region to obtain the multiple sets of K-space data; The step of determining the target K-space filling regions corresponding to the multiple phases of the detection object according to a preset acceleration factor includes: Based on the preset acceleration multiple, determine the first acceleration multiple, the second acceleration multiple, and the third acceleration multiple; For the first acceleration factor, the second acceleration factor, and the third acceleration factor, trajectory planning is performed on the initial K-space filling region of each phase of the detected object using different methods to obtain the third K-space filling region; The target K-space filling region is determined based on the third K-space filling region.

8. A magnetic resonance imaging device, characterized in that, The device includes: The first determining module is used to determine a preset acceleration factor, and based on the preset acceleration factor, determine the target K-space filling regions corresponding to multiple phases of the detection object, wherein the target K-space filling regions include filling regions corresponding to undersampling; A filling module is used to fill the target K-space filling region with magnetic resonance data collected relative to the detection object in each period to obtain multiple sets of K-space data; The second determining module is used to determine the synthesized K-space data for each period by using the K-space data corresponding to the period and the data of the undersampled filling region in the K-space data corresponding to periods other than the period. The first reconstruction module is used to reconstruct the synthetic K-space data and generate a magnetic resonance image of the detected object. The first determining module is specifically used to determine a first acceleration factor, a second acceleration factor, and a third acceleration factor based on the preset acceleration factor; to perform trajectory planning on the initial K-space filling region of each phase of the detection object according to different methods for the first acceleration factor, the second acceleration factor, and the third acceleration factor, to obtain a third K-space filling region; and to determine the target K-space filling region based on the third K-space filling region.

9. A magnetic resonance imaging device, characterized in that, The device includes: The acquisition module is used to acquire multiple sets of K-space data of the detection object. Each set of K-space data corresponds to the data collected relative to the detection object in one period. Each set of K-space data includes full-sampled data and undersampled data. The third determining module is used to determine the synthesized K-space data for each period using the K-space data corresponding to the period and the undersampled data corresponding to other periods besides the period. The second reconstruction module is used to reconstruct the synthetic K-space data and generate a magnetic resonance image of the detected object.

10. A computer device comprising a memory and a processor, wherein the memory stores a computer program, characterized in that, When the processor executes the computer program, it implements the steps of the method according to any one of claims 1 to 7.

Images