WO2020019412A1 - 磁共振成像方法、装置、设备及存储介质 - Google Patents
磁共振成像方法、装置、设备及存储介质 Download PDFInfo
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- Embodiments of the present disclosure relate to the field of image processing technologies, and for example, to a magnetic resonance imaging method, apparatus, device, and storage medium.
- magnetic resonance imaging As a radiation-free clinical diagnostic image, magnetic resonance imaging is more and more widely used in clinical diagnosis. However, it is difficult for magnetic resonance imaging methods in related technologies to take into account higher image quality and shorter data sampling time, so it is used in clinical practice. In the process, people often need to choose between higher image quality and shorter data sampling time according to their needs.
- the embodiments of the present disclosure provide a magnetic resonance imaging method, device, device, and storage medium, which solve the technical problem that it is difficult for the magnetic resonance imaging method to take into account both higher image quality and shorter data sampling time.
- An embodiment of the present disclosure provides a magnetic resonance imaging method, including:
- the wave-controlled aliasing parallel imaging method (wave-CAIPI) is used to adjust the coding strategy of three-dimension balanced-free free precession (3DbSSFP).
- the coding strategy includes a coding strategy in a phase direction and a coding strategy in a layer selection direction;
- Image reconstruction is performed on the three-dimensional under-acquisition data according to the three-dimensional point spread function and the sensitivity map to generate a magnetic resonance image of a target object.
- An embodiment of the present disclosure further provides a magnetic resonance imaging apparatus, including:
- a 3D point spread function acquisition module configured to obtain a 3D point spread function of a target object
- Sensitivity map acquisition module configured to obtain the target object's sum sensitivity map
- the coding strategy adjustment module is configured to adjust a coding strategy of a balanced steady-state free precession pulse sequence by a wave gradient pulse controllable aliasing parallel imaging method, wherein the coding strategy includes a phase direction coding strategy and a layer selection direction coding strategy ;
- the three-dimensional under-acquisition data acquisition module is configured to obtain a three-dimensional under-acquisition data of a target object based on a balanced steady-state free precession pulse sequence adjusted based on an encoding strategy, wherein the three-dimensional under-acquisition data is the same as the imaging field of view of the sensitivity map. ;
- the reconstruction module is configured to perform image reconstruction on the three-dimensional under-acquisition data according to the three-dimensional point spread function and the sensitivity map to generate a magnetic resonance image of a target object.
- An embodiment of the present disclosure further provides a device, where the device includes:
- One or more processors are One or more processors;
- a storage device configured to store one or more programs
- the one or more processors When the one or more programs are executed by the one or more processors, the one or more processors implement the magnetic resonance imaging method as described above.
- An embodiment of the present disclosure also provides a storage medium containing computer-executable instructions, which are executed by a computer processor to perform the magnetic resonance imaging method as described above.
- the magnetic resonance imaging method provided by the embodiment of the present disclosure obtains a magnetic resonance image obtained by balancing a steady-state free precession pulse sequence with a high spatial resolution and a high signal-to-noise ratio, which can more clearly display the tissue structure and effectively reduce the volume effect.
- wave gradient pulse controllable aliasing parallel imaging method uses sine / The cosine magnetic field gradient disperses the K-space signal, and adjusts the coding strategy of the phase direction and the layer selection direction to reduce the geometric factor, thereby improving the acceleration of the 3D balanced steady-state free precession pulse sequence under the premise of ensuring the image quality. Multiples, and has high robustness.
- FIG. 1 is a flowchart of a magnetic resonance imaging method according to an embodiment
- FIG. 2 is a gradient echo sequence diagram provided by an embodiment
- FIG. 3 is a schematic diagram of a data acquisition strategy based on a wave gradient pulse controllable aliasing parallel imaging method according to an embodiment (2 ⁇ 2 times acceleration);
- FIG. 4 is a schematic diagram of a data acquisition strategy based on a wave gradient pulse controllable aliasing parallel imaging method according to an embodiment (3 ⁇ 3 times acceleration);
- FIG. 5 is a sequence diagram of a balanced steady-state free precession pulse after the encoding strategy is adjusted according to an embodiment.
- FIG. 6 is a flowchart of a method for acquiring a three-dimensional point spread function according to an embodiment
- FIG. 7 is a two-dimensional balanced steady-state free precession pulse sequence diagram in a layer selection direction according to an embodiment
- FIG. 9 is a two-dimensional balanced steady-state free precession pulse sequence diagram in which a cosine gradient magnetic field is applied in a layer selection direction according to an embodiment
- 10 is a two-dimensional balanced steady-state free precession pulse sequence diagram of a cosine gradient magnetic field applied in a phase direction according to an embodiment
- FIG. 11 is a 2 ⁇ 2 times accelerated test result of a phantom provided by an embodiment
- FIG. 12 is a 3 ⁇ 3 times accelerated test result of a phantom provided by an embodiment
- FIG. 13 is a 2 ⁇ 2 times accelerated test result of a human brain according to an embodiment
- FIG. 14 is a 3 ⁇ 3 times accelerated test result of the human brain according to an embodiment
- FIG. 15 is a structural block diagram of a magnetic resonance imaging apparatus according to an embodiment
- FIG. 16 is a schematic structural diagram of a device according to an embodiment.
- the three-dimensional equilibrium steady-state free precession method has a wide range of applications in the field of magnetic resonance imaging (MRI). It is also called in commercial magnetic resonance: true fast-imaging fast imaging method (steady- stateprecession, true-FISP).
- the three-dimensional equilibrium steady-state free-rotation method has the characteristics of high spatial resolution of magnetic resonance three-dimensional imaging, which can more clearly display the tissue structure and effectively reduce the volume effect.
- TR repetition time
- three-dimensional The equilibrium steady-state free precession method applies zero net magnetic field gradients in three directions (layer selection direction, readout direction, and phase direction). This structure effectively uses the magnetic resonance signals possessed by unspinned spins.
- the 3D equilibrium steady-state free precession method has a high signal-to-noise ratio; in addition, the 3D equilibrium steady-state free precession method has a structure in which the magnetic field gradient is zero within the repetition time (TR), which makes the 3D equilibrium steady-state free
- the magnetic resonance image obtained by the screw-in method has a unique T2 / T1 contrast, which is helpful in distinguishing certain specific tissue structures or lesions in clinical diagnosis, such as the heart muscle or tumor.
- the scanning time is long and the time resolution is low, which limits the application of the technology in many fields, such as for sports tissues (heart and abdomen). Imaging, etc. In addition, too long scanning time can easily cause patient discomfort.
- Parallel imaging technologies such as sensitivity encoding (SENSE), generalized autocalibrating partially parallel acquisitions (GRAPPA), and partial Fourier reconstruction (PF), only acquire part K Spatial data, and using the prior information contained in multi-channel coils or under-collected K-space to reconstruct the complete image to achieve the purpose of accelerating the acquisition, however, images accelerated by parallel imaging technology will have a root acceleration factor (Where R is the acceleration factor) and the geometric signal factor multiples, and the performance of the multi-channel coil, the accuracy of the prior information, and the reconstruction model have a greater impact on the geometric factor.
- SENSE sensitivity encoding
- GRAPPA generalized autocalibrating partially parallel acquisitions
- PF partial Fourier reconstruction
- the geometric factor is also called "noise amplification factor".
- the geometric factor is unique to parallel imaging and is a measure of coil separation. The geometric factor depends on the number of repeated acquisitions of each point and the corresponding coil sensitivity difference. It is not a constant, but changes with the image position. It reflects the separation of pixels that are superimposed due to aliasing in a specific RF coil configuration. As the value of the geometric factor increases, the effective signal-to-noise ratio associated with reconstruction decreases. The larger the geometric factor, the smaller the signal-to-noise ratio of the resulting magnetic resonance image.
- the related art acceleration technology based on the equilibrium steady-state free-spinning method has either a limited acceleration factor or an unstable factor.
- the embodiment of the present disclosure proposes a magnetic resonance imaging method, device, device, and storage medium. The method is explained.
- FIG. 1 is a flowchart of a magnetic resonance imaging method provided by this embodiment.
- the technical solution of this embodiment is applicable to a case where the data collection time is shortened without affecting the quality of magnetic resonance imaging.
- the method may be performed by a magnetic resonance apparatus provided by an embodiment of the present disclosure, and the apparatus may be implemented in software and / or hardware, and configured to be applied in a processor. As shown in FIG. 1, the method includes the following steps.
- Step 1010 Obtain a three-dimensional point spread function of the target object.
- the 3D point spread function of the target object is obtained, and the sampling trajectory in the frequency domain space (K space) is corrected by the 3D point spread function (PSF).
- Step 1020 Obtain a sensitivity map of the target object.
- this embodiment adopts a multi-layer parallel acquisition method to acquire magnetic resonance imaging data of a target object. Because different receiving coils have different sensitivities to different layers, it is necessary to use the sensitivity map to separate the images of each layer from the aliased images. For this reason, in this embodiment, the sensitivity map is obtained from the three-dimensional low-resolution data of the target object, and the three-dimensional low-resolution data can be obtained by a three-dimensional low-resolution data acquisition method, such as a gradient echo method, a spin echo method, or a balance Steady-state free spinning method, etc.
- a three-dimensional low-resolution data acquisition method such as a gradient echo method, a spin echo method, or a balance Steady-state free spinning method, etc.
- a gradient echo method is used to obtain three-dimensional low-resolution data (see FIG. 2), where the gradient echo method is: the readout of the damaged magnetic field gradient in each repetition time (TR) is applied in the readout direction After the magnetic field gradient.
- the gradient echo method is: the readout of the damaged magnetic field gradient in each repetition time (TR) is applied in the readout direction After the magnetic field gradient.
- RF radio frequency
- the RF spoiler technology is: after the magnetic pulse (Magnetic Resonance, MR) signal of the previous pulse is collected, and before the next RF pulse is excited, the xy plane still retains a fairly strong transverse magnetization vector M xy in each pulse cycle Phase detection pulses are applied after the detection of signals to accelerate the phase loss, so that before the next period of RF pulse excitation, the transverse magnetization vector M xy is destroyed and disappears to zero, so only the longitudinal magnetization vector M z contributes to the next MR signal.
- MR Magnetic Resonance
- Step 1030 Adjust the encoding strategy of the balanced steady-state free precession pulse sequence by a wave gradient pulse controllable aliasing parallel imaging method, wherein the encoding strategy includes a phase direction encoding strategy and a layer selection direction encoding strategy.
- the wave gradient pulse controllable aliasing parallel imaging method not only implements data downsampling in the phase direction and / or layer selection direction based on the traditional multi-layer simultaneous excitation, but also
- the layer signal adds different linear phases along the phase direction and the layer selection direction to adjust the coding strategy, so that the data collected in the phase direction and the layer selection direction have a linear phase offset, and the data caused by undersampling will be mixed.
- the overlay is dispersed into the phase direction and the layer selection direction at the same time, making more effective use of the background area in the field of view, making different layers of images form different displacements in the overlay image, increasing the sensitivity difference between layers, further
- the geometric factor is reduced, and aliasing artifacts that may be caused in the reconstructed image are avoided.
- the direction perpendicular to the plane is the readout direction, and the intersection of the black dotted lines is the readout line required for full sampling.
- the readout line required for the undersampling strategy adopted in this embodiment is indicated by a bold solid origin.
- Figure 3 shows 2 ⁇ 2 times undersampling (2 times undersampling in the phase direction, and 2 times undersampling in the layer selection direction).
- the total acceleration multiple is 4.
- the required acquisition time repetition time (TR) ⁇ number of phase encoding lines ( Np) ⁇ number of layer selection lines (Ns) / 4;
- Figure 4 shows 3 ⁇ 3 times undersampling (3 times undersampling in the phase direction, 3 times undersampling in the layer selection direction), and the total acceleration factor is 9, which is required.
- Acquisition time repetition time (TR) ⁇ number of phase encoding lines (Np) ⁇ number of layer selection encoding lines (Ns) / 9.
- the balanced steady-state free-spinning pulse sequence can ensure that the transverse magnetization is not damaged before the next RF pulse is applied, so that the transverse magnetization returns to the original phase, and then the transverse magnetization is carried to the next phase.
- TR is superimposed on the transverse magnetization pulse generated by the RF pulse. After a certain number of TR repeats, the magnetization reaches a steady state, and the transverse magnetization from two or three consecutive TRs combine to form a powerful signal.
- a sine gradient magnetic field and a cosine gradient magnetic field with a phase difference of 90 degrees are simultaneously applied in the layer selection direction and the phase direction of a balanced steady-state free precession pulse sequence. It can be understood that, for two sine signals and cosine signals with the same frequency, the phase difference at each moment is 90 degrees.
- a sine gradient magnetic field is applied between the two-body-encoded gradient pulses in each period of the layer selection direction, and a cosine gradient magnetic field is applied between the two-phase-encoded gradient pulses in each period in the phase direction.
- Step 1040 Obtain three-dimensional under-acquisition data of the target object based on the balanced steady-state free precession pulse sequence adjusted by the encoding strategy, where the three-dimensional under-acquisition data is the same as the imaging field of the sensitivity map.
- the imaging field of view of the three-dimensional under-acquisition data is set to be the same as the imaging field of the sensitivity map, and then the three-dimensional under-acquisition data of the target object is obtained based on the balanced steady-state free precession pulse sequence adjusted by the encoding strategy.
- Step 1050 Perform image reconstruction on the 3D under-acquisition data according to the 3D point spread function and the sensitivity map to generate a magnetic resonance image of the target object.
- the 3D point spread function is represented by PSF yz (k x , y, z)
- the sensitivity map is represented by C (x, y, z) indicates that the magnetic resonance reconstruction image can be calculated by the following formula:
- recon (x, y, z) is the reconstructed image, wave (x, y, z) three-dimensional under-acquisition data, F x and Are the one-dimensional Fourier transform and the inverse one-dimensional Fourier transform along the x direction.
- the above-mentioned magnetic resonance image reconstruction process corrects the K-space trajectory of three-dimensional under-acquisition data through a three-dimensional point spread function, and separates each layer image from the aliased image by using a sensitivity map.
- the above method step sequence is the method step sequence of this embodiment.
- the acquisition order of the three-dimensional point spread function, the sensitivity map, and the three-dimensional under-acquisition data can be arbitrarily combined, but considering that the acquisition time of the three-dimensional under-acquisition data is relatively longer than the acquisition time of the corresponding data of the three-dimensional point spread function and sensitivity map. It is long, so the step of 3D undermined data is put last.
- the technical solution of the magnetic resonance imaging method provided by this embodiment has a high spatial resolution and a high signal-to-noise ratio by means of a balanced steady-state free precession pulse sequence.
- the magnetic resonance image can more clearly display the tissue structure and effectively reduce Volume effect, meanwhile, the T2 / T1 weighted contrast characteristic of this magnetic resonance image can help to distinguish some specific tissue structures or lesions, such as myocardium or tumor, in clinical diagnosis;
- wave gradient pulse controllable aliasing parallel imaging method uses The sine / cosine magnetic field gradient disperses the K-space signal, and adjusts the coding strategy of the phase direction and layer selection direction to reduce the geometric factor, thereby improving the 3D equilibrium steady-state free-rotation pulse sequence under the premise of ensuring image quality Speedup, and has high robustness.
- FIG. 6 is a flowchart of a method for acquiring a three-dimensional point spread function according to an embodiment. This embodiment optimizes the three-dimensional point spread function of the target object based on the above embodiment.
- Step 10110 Obtain mapping data of the target object based on the balanced steady-state free precession pulse sequence.
- two-dimensional mapping data of the target object in the layer selection direction and two-dimensional mapping data in the phase direction are obtained. For example, as shown in FIG. 7, based on a two-dimensional balanced steady-state free precession pulse sequence in the layer selection direction, two-dimensional mapping data of the target object in the layer selection direction, that is, two-dimensional mapping data in the xz plane is obtained; as shown in FIG. 8. As shown in the figure, two-dimensional mapping data of the target object in the phase direction is obtained based on the two-dimensional equilibrium steady-state free precession pulse sequence in the phase direction, that is, two-dimensional mapping data in the xy plane.
- a cosine magnetic field gradient is applied in the layer selection direction of the two-dimensional balanced steady-state free precession pulse sequence to obtain the gradient two-dimensional mapping data of the target object in the layer selection direction.
- a cosine magnetic field gradient is applied in the layer selection direction of the two-dimensional balanced steady-state free-spinning pulse sequence in the layer selection direction, and based on the two-dimensional balanced steady-state free rotation in which the cosine magnetic field gradient is added in the layer selection direction.
- the progressive pulse sequence acquires the gradient two-dimensional mapping data of the target object in the layer selection direction, that is, the two-dimensional mapping data of the xz plane.
- a cosine magnetic field gradient is applied in the phase direction of the two-dimensional balanced steady-state free precession pulse sequence to obtain gradient two-dimensional mapping data in the phase direction.
- a cosine magnetic field gradient is applied in the phase direction of a two-dimensional balanced steady-state free-running pulse sequence in the phase direction, and based on a two-dimensional balanced steady-state free-running pulse sequence in which a cosine magnetic field gradient is added in the phase direction Obtain the gradient two-dimensional mapping data of the target object in the phase direction, that is, the two-dimensional mapping data of the xy plane.
- the time required to collect mapping data in the layer selection direction is 2 ⁇ repetition time (TR) ⁇ number of layer selection coding lines (Ns), including the time when the cosine magnetic field gradient is applied in the layer selection direction and the time when the cosine magnetic field gradient is not applied;
- the time required to acquire phase direction mapping data is 2 ⁇ repetition time (TR) ⁇ number of phase encoding lines (Np), including the time when the cosine magnetic field gradient is applied in the phase direction and the time when the cosine magnetic field gradient is not applied. Since the above mapping data collects two-dimensional data, the required scanning time is shorter.
- Step 10120 Obtain a three-dimensional point spread function of the target object according to the mapping data.
- the three-dimensional point spread function can be obtained directly from the three-dimensional mapping data, or the three-dimensional point spread function can be obtained from the two-dimensional point spread function of two intersecting planes. This embodiment uses the latter to reduce the acquisition time of mapping data.
- a three-dimensional point is calculated based on the two-dimensional mapping data in the layer selection direction and the two-dimensional mapping data in the phase direction, and the two-dimensional gradient data in the layer selection direction and the two-dimensional gradient data in the phase direction. Diffusion function.
- a two-dimensional point spread function in the layer selection direction is obtained based on the two-dimensional map data in the layer selection direction and the gradient two-dimensional map data in the layer selection direction.
- the two-dimensional map data of the gradient is waveP z
- the cosine magnetic field gradient in the layer selection direction is collected.
- a two-dimensional point spread function in the phase direction is obtained based on a two-dimensional map function in the phase direction and a gradient two-dimensional map function in the phase direction.
- a gradient-dimensional map data is acquired waveP y
- no phase sinusoidal magnetic field gradient direction (FIG. 8) acquired two-dimensional
- the mapping data is P y
- a three-dimensional point spread function is obtained based on the two two-dimensional point spread functions.
- PSF yz (k x , y, z) PSF z (k x , z) ⁇ PSF y (k x , y), which is the value of any point (k x , y, z) in the three-dimensional point spread function PSF yz
- PSF yz (k x , z) PSF yz (k x , z).
- a two-dimensional point spread function in a layer selection direction is determined by two-dimensional mapping data with and without a cosine magnetic field gradient applied in a layer selection direction; through a phase direction
- the two-dimensional mapping data with and without the cosine magnetic field gradient is applied to determine the two-dimensional point spread function in the phase direction, and then the two-dimensional point spread function in the layer selection direction and the two-dimensional point spread in the phase direction are determined.
- the function determines the three-dimensional point spread function. Compared with determining three-dimensional point spread function through three-dimensional mapping data, the time for collecting mapping data can be greatly reduced, and the time for collecting magnetic resonance imaging data can be reduced.
- a phantom and a human brain test are performed on a magnetic resonance imaging system, and the feasibility of the magnetic resonance imaging method described in any of the foregoing embodiments of the present disclosure is confirmed.
- Fig. 11 and Fig. 12 show the results of the simulation test.
- Figure a in Figure 11 and Figure a in Figure 12 are MRI images obtained based on the Fourier transform method;
- Figure b in Figure 11 and Figure b in Figure 12 are MRI images obtained based on the sensitivity coding method;
- FIG. C in FIG. 11 and FIG. C in FIG. 12 are MRI images obtained based on the magnetic resonance imaging method according to the embodiment of the present disclosure;
- FIG. E in FIG. 11 and FIG. E in FIG. 12 are geometric factors corresponding to the magnetic resonance imaging method according to the embodiment of the present disclosure during image reconstruction.
- Figure 13 and Figure 14 show the results of the human brain test.
- Figure a in Figure 13 and Figure a in Figure 14 are MRI images obtained based on the Fourier transform method;
- Figure b in Figure 13 and Figure b in Figure 14 are MRI images obtained based on the sensitivity coding method;
- FIG. C in FIG. 13 and FIG. C in FIG. 14 are MRI images obtained based on the magnetic resonance imaging method according to the embodiment of the present disclosure;
- FIG. E in FIG. 13 and FIG. E in FIG. 14 are geometric factors corresponding to the magnetic resonance imaging method according to the embodiment of the present disclosure during the image reconstruction process.
- the magnetic resonance imaging method has a lower geometric factor (g-factor) (see FIG. E in FIG. 13 and FIG. E in FIG. 14).
- g-factor geometric factor
- the acceleration factor is large, the reconstructed The image has better image quality (see Figure c in Figure 14).
- This embodiment compares the actual magnetic resonance imaging data acquisition time and image quality of the phantom and the human body, and illustrates that the magnetic resonance imaging method described in the foregoing embodiment of the present disclosure can pass the larger Accelerating multiples reduces data collection time, which is conducive to improving the patient experience and clinical promotion.
- FIG. 15 is a structural block diagram of a magnetic resonance imaging apparatus according to an embodiment.
- the device is configured to execute the magnetic resonance imaging device provided in any of the foregoing embodiments, and the device may be implemented by software or hardware. As shown in Figure 15, the device includes:
- the three-dimensional point spread function acquisition module 11 is set to acquire the three-dimensional point spread function of the target object;
- the sensitivity map acquisition module 12 is set to acquire the target object's sum sensitivity map;
- the coding strategy adjustment module 13 is set to controllable mixing by wave gradient pulses
- the superimposed parallel imaging method adjusts the encoding strategy of the balanced steady-state free precession pulse sequence, wherein the encoding strategy includes the encoding strategy in the phase direction and the encoding strategy in the layer selection direction;
- the three-dimensional under-acquisition data acquisition module 14 is set to be based on the encoding strategy
- the adjusted balanced steady-state free precession pulse sequence acquires three-dimensional under-acquisition data of the target object, wherein the three-dimensional under-acquisition data is the same as the imaging field of view of the sensitivity map;
- the reconstruction module 15 is configured to diffuse according to the three-dimensional point diffusion
- the function and the sensitivity map perform image reconstruction on the three-dimensional under-acquisition data to generate a magnetic resonance image of a target object
- the magnetic resonance image obtained by balancing the steady-state free-rotation pulse sequence has high spatial resolution and high signal-to-noise ratio, which can more clearly display the tissue structure and effectively reduce
- the volume effect and the T2 / T1 weighted contrast characteristic of this magnetic resonance image are helpful for distinguishing certain specified tissue structures or lesions, such as myocardium or tumor, in clinical diagnosis;
- wave gradient pulse controllable aliasing parallel imaging method Use the sine / cosine magnetic field gradient to disperse the K-space signal, and adjust the phase direction and layer selection direction coding strategy to reduce the geometric factor, so as to ensure the image quality, improve the three-dimensional equilibrium steady-state free precession pulse Acceleration multiple of the sequence, and has high robustness.
- the magnetic resonance imaging apparatus provided by this embodiment can execute the magnetic resonance imaging method provided by any embodiment of the present disclosure, and has the corresponding functional modules and beneficial effects of executing the method.
- FIG. 16 is a schematic structural diagram of a device according to an embodiment.
- the device includes a processor 201, a memory 202, an input device 203, and an output device 204; the number of processors 201 in the device may be one or more, and one processor 201 is taken as an example in FIG. 16; the device The processor 201, the memory 202, the input device 203, and the output device 204 may be connected through a bus or other methods. In FIG. 16, the connection through a bus is taken as an example.
- the memory 202 is a computer-readable storage medium, and can be used to store software programs, computer-executable programs, and modules, such as program instructions / modules corresponding to the magnetic resonance imaging method in the embodiment of the present disclosure (for example, a three-dimensional point spread function acquisition module 11. Sensitivity map acquisition module 12, encoding strategy adjustment module 13, three-dimensional under-acquisition data acquisition module 14, and reconstruction module 15).
- the processor 201 executes one or more functional applications and data processing of the device by running software programs, instructions, and modules stored in the memory 202, that is, the above-mentioned magnetic resonance imaging method is implemented.
- the memory 202 may mainly include a storage program area and a storage data area, where the storage program area may store an operating system and application programs required for at least one function; the storage data area may store data created according to the use of the terminal, and the like.
- the memory 202 may include a high-speed random access memory, and may further include a non-volatile memory, such as at least one magnetic disk storage device, a flash memory device, or other non-volatile solid-state storage device.
- the memory 202 may include memory remotely set relative to the processor 201, and these remote memories may be connected to the device through a network. Examples of the above network include, but are not limited to, the Internet, an intranet, a local area network, a mobile communication network, and combinations thereof.
- the input device 203 may be configured to receive inputted numeric or character information and generate key signal inputs related to user settings and function control of the device.
- the output device 204 may include a display device such as a display screen, for example, a display screen of a user terminal.
- the above device further includes a collector 205, which is configured to obtain a three-dimensional point spread function of the target object, obtain a target object and a sensitivity map, and adjust the balance and stability by a wave gradient pulse controllable aliasing parallel imaging method.
- the encoding strategy of the state free precession pulse sequence and the balanced steady-state free precession pulse sequence adjusted based on the encoding strategy are used to obtain the 3D undermined data of the target object.
- An embodiment of the present disclosure further provides a storage medium including computer-executable instructions, which are executed by a computer processor to perform a magnetic resonance imaging method, the method including:
- the storage medium provided by this embodiment includes computer-executable instructions, and the computer-executable instructions are not limited to the method operations described above, and may also perform related operations in the magnetic resonance imaging method provided by any embodiment of the present disclosure. operating.
- the present disclosure can be implemented by software and necessary general-purpose hardware, and of course, can also be implemented by hardware, but the former is a better implementation in many cases.
- the technical solution of the present disclosure that is essential or contributes to related technologies may be embodied in the form of a software product.
- the computer software product may be stored in a computer-readable storage medium, such as a computer floppy disk, Read-only memory (ROM), random access memory (RAM), flash memory (FLASH), hard disk or optical disk, etc., including multiple instructions to make a computer device (can be a personal computer , Server, or network device, etc.) execute the magnetic resonance imaging method described in any embodiment of the present disclosure.
- the multiple units and modules included are only divided according to functional logic, but are not limited to the above division, as long as the corresponding functions can be realized;
- the names of each functional unit are only for the convenience of distinguishing from each other, and are not used to limit the protection scope of the present disclosure.
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Claims (10)
- 一种磁共振成像方法,包括:获取目标对象的三维点扩散函数;获取所述目标对象的灵敏度图;通过波浪梯度脉冲可控混叠并行成像方法调整平衡稳态自由旋进脉冲序列的编码策略,其中,所述编码策略包括相位方向的编码策略和选层方向的编码策略;基于所述编码策略调整后的平衡稳态自由旋进脉冲序列获取所述目标对象的三维欠采数据,其中,所述三维欠采数据与所述灵敏度图的成像视野相同;根据所述三维点扩散函数和所述灵敏度图对所述三维欠采数据进行图像重建,以生成所述目标对象的磁共振图像。
- 根据权利要求1所述的方法,其中,所述获取目标对象的三维点扩散函数,包括:基于所述平衡稳态自由旋进脉冲序列获取所述目标对象的映射数据;根据所述映射数据求取所述目标对象的三维点扩散函数。
- 根据权利要求2所述的磁共振成像方法,其中,所述基于所述平衡稳态自由旋进脉冲序列获取所述目标对象的映射数据,包括:基于二维平衡稳态自由旋进脉冲序列获取所述目标对象在所述选层方向上的二维映射数据和所述相位方向上的二维映射数据;在所述二维平衡稳态自由旋进脉冲序列的选层方向施加余弦磁场梯度,以获取所述目标对象在所述相位方向上的梯度二维映射数据;在所述二维平衡稳态自由旋进脉冲序列的相位方向施加余弦磁场梯度,以获取所述目标对象在所述选层方向上的梯度二维映射数据;所述根据所述映射数据求取所述目标对象的三维点扩散函数,包括:基于所述选层方向上的二维映射数据、所述相位方向上的二维映射数据、所述选层方向上的梯度二维映射数据以及所述相位方向上的梯度二维映射数据计算所述三维点扩散函数。
- 根据权利要求3所述的磁共振成像方法,其中,所述基于所述选层方向上的二维映射数据、所述相位方向上的二维映射数据、所述选层方向上的梯度二维映射数据以及所述相位方向上的梯度二维映射数据计算所述三维点扩散函数,包括:基于所述选层方向上的二维映射数据和所述选层方向上的梯度二维映射数 据求取所述选层方向上的二维点扩散函数;基于所述相位方向上的二维映射函数和所述相位方向上的梯度二维映射函数求取所述相位方向上的二维点扩散函数;基于所述选层方向上的二维点扩散函数和所述相位方向上的二维点扩散函数求取所述三维点扩散函数。
- 根据权利要求1-4任一项所述的磁共振成像方法,其中,所述获取所述目标对象的灵敏度图,包括:获取所述目标对象的三维低分辨率数据;根据所述三维低分辨率数据计算所述目标对象的灵敏度图。
- 根据权利要求5所述的磁共振成像方法,其中,所述获取所述目标对象的三维低分辨率数据,包括:基于梯度回波脉冲序列、自旋回波脉冲序列或所述平衡稳态自由旋进脉冲序列获取所述目标对象的三维低分辨率数据。
- 根据权利要求1-6任一项所述的磁共振成像方法,其中,所述通过波浪梯度脉冲可控混叠并行成像方法调整平衡稳态自由旋进脉冲序列的编码策略,其中,所述编码策略包括相位方向的编码策略和选层方向的编码策略,包括:在所述平衡稳态自由旋进脉冲序列的相位方向和所述平衡稳态自由旋进脉冲序列的选层方向同时分别施加相位相差90度的正弦磁场梯度和余弦磁场梯度,以调整所述平衡稳态自由旋进脉冲序列的编码策略。
- 一种磁共振成像装置,包括:三维点扩散函数获取模块,设置为获取目标对象的三维点扩散函数;灵敏度图获取模块,设置为获取所述目标对象的和灵敏度图;编码策略调整模块,设置为通过波浪梯度脉冲可控混叠并行成像方法调整平衡稳态自由旋进脉冲序列的编码策略,其中,所述编码策略包括相位方向的编码策略和选层方向的编码策略;三维欠采数据获取模块,设置为基于编码策略调整后的平衡稳态自由旋进脉冲序列获取所述目标对象的三维欠采数据,其中,所述三维欠采数据与所述灵敏度图的成像视野相同;重建模块,设置为根据所述三维点扩散函数和所述灵敏度图对所述三维欠采数据进行图像重建,以生成所述目标对象的磁共振图像。
- 一种设备,所述设备包括:一个或多个处理器;存储装置,设置为存储一个或多个程序;当所述一个或多个程序被所述一个或多个处理器执行,使得所述一个或多个处理器实现如权利要求1-7中任一项所述的磁共振成像方法。
- 一种包含计算机可执行指令的存储介质,所述计算机可执行指令在由计算机处理器执行时用于执行如权利要求1-7中任一项所述的磁共振成像方法。
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