A magnetic resonance angiography method, system and electronic device

Abstract

The present invention discloses a magnetic resonance angiography method, system and electronic device, relating to the technical field of magnetic resonance imaging. By adopting a 3D acquisition mode (constituted by two-dimensional radial acquisition and one-dimensional Cartesian acquisition), an improved dual-echo fat-water separation technique and a compressed sensing technique, the present invention fuses them into a T1-FFE sequence to generate a new type of MRA sequence (3DmDixon-MRA) sequence. The acquisition mode of this sequence can form magnetic resonance angiography images of the neck arteries to be imaged, thereby improving the quality of magnetic resonance angiography images and shortening the scanning time.

Description

Technical Field

[0001] The present invention relates to the technical field of magnetic resonance imaging, and particularly to a magnetic resonance angiography method, system and electronic device. Background Art

[0002] Carotid and vertebral artery stenosis is an important risk factor for ischemic stroke, accounting for 20% - 30% of all ischemic strokes. Carotid atherosclerotic plaques mostly occur at the proximal branch of the common carotid artery. Vertebral artery variation and stenosis are common at its origin. Due to its simplicity and the absence of the need for contrast agents, time-of-flight MR angiography (TOF-MRA) technology is widely used in head and neck vascular examinations. However, TOF-MRA technology relies on blood flow imaging, and signal loss is likely to occur due to blood turbulence at the vascular stenosis and tortuosity, thus overestimating vascular stenosis. In particular, the origin of the carotid and vertebral arteries near the chest is particularly affected by respiratory motion artifacts. Summary of the Invention

[0003] To solve this technical problem, the present invention provides a magnetic resonance angiography method, system and electronic device.

[0004] To achieve the above object, the present invention provides the following solutions:

[0005] A magnetic resonance angiography method is applied to neck artery imaging; the method includes:

[0006] Acquiring magnetic resonance angiography images of the neck artery to be imaged by using an improved sequence mode; the improved sequence mode is a fusion technology of a three-dimensional imaging sequence mode, a dual-echo fat-water separation technology and a compressed sensing technology; the three-dimensional imaging sequence mode is a 3D acquisition mode composed of two-dimensional radial acquisition and one-dimensional Cartesian acquisition.

[0007] Optionally, the two-dimensional radial acquisition uses a pseudo-golden angle mode for K-space filling, and adding one dimension of Cartesian acquisition forms the final three-dimensional K-space data.

[0008] Optionally, when modifying and optimizing the T1-FFE sequence to form the magnetic resonance angiography sequence, acquiring magnetic resonance angiography images of the neck artery to be imaged by using the improved sequence mode specifically includes:

[0009] Changing the 3D Cartesian mode used in the process of acquiring the T1-FFE sequence to an in-plane pseudo-golden angle radial K-space filling mode and a one-dimensional Cartesian acquisition mode to form the final three-dimensional K-space data;

[0010] Change the anti-phase technique for suppressing the background used in the process of obtaining the T1-FFE sequence to the dual-echo fat-water separation technique;

[0011] Meanwhile, in the slice direction, change the parallel acquisition acceleration mode used in the process of obtaining the T1-FFE sequence to the compressed sensing technique to form the magnetic resonance angiography sequence.

[0012] According to the specific embodiments provided by the present invention, the present invention discloses the following technical effects:

[0013] The magnetic resonance angiography method provided by the present invention generates a new type of MRA sequence (3D mDixon-MRA) sequence by integrating a 3D acquisition mode (composed of two-dimensional radial and one-dimensional Cartesian acquisitions), an improved dual-echo fat-water separation technique, and a compressed sensing technique into the T1-FFE sequence. The acquisition mode of this sequence can form magnetic resonance angiography images of the neck arteries to be imaged, thereby improving the quality of magnetic resonance angiography images and shortening the scanning time.

[0014] Corresponding to the magnetic resonance angiography method provided above, the present invention also provides the following implementation structures:

[0015] A magnetic resonance angiography system for neck artery imaging; the system includes:

[0016] An imaging sequence acquisition module for acquiring magnetic resonance angiography images of the neck arteries to be imaged by using an improved sequence mode; the improved sequence mode is a fusion technique of a three-dimensional imaging sequence mode, a dual-echo fat-water separation technique, and a compressed sensing technique; the three-dimensional imaging sequence mode is a 3D acquisition mode composed of two-dimensional radial acquisition and one-dimensional Cartesian acquisition.

[0017] An electronic device includes:

[0018] A memory for storing a computer program;

[0019] A processor connected to the memory for retrieving and executing the computer program to implement the magnetic resonance angiography method provided above.

[0020] Optionally, the memory is a computer-readable storage medium.

[0021] Since the technical effects achieved by the above two implementation structures provided by the present invention are the same as those achieved by the magnetic resonance angiography method provided by the present invention, they will not be elaborated here. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the following will briefly introduce the accompanying drawings required in the embodiments. Obviously, the accompanying drawings in the following description are only some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other accompanying drawings can be obtained based on these drawings.

[0023] Figure 1 It is a comparison result diagram of carotid artery imaging of patient 1 provided by an embodiment of the present invention; wherein, Figure 1 1A is a 3D TOF-MRA imaging diagram of the left common carotid artery of patient 1, Figure 1 1B is a 3D TOF-MRA imaging diagram of the bilateral vertebral arteries of patient 1, Figure 1 1C is a 3D TOF-MRA imaging diagram of the bilateral common carotid arteries of patient 1, Figure 1 1D is a 3D TOF-MRA imaging diagram of the bilateral internal carotid arteries of patient 1, Figure 1 1E is a 3D mDixon-MRA imaging diagram of the left common carotid artery of patient 1, Figure 1 1F is a 3D mDixon-MRA imaging diagram of the bilateral vertebral arteries of patient 1, Figure 1 1G is a 3D mDixon-MRA imaging diagram of the bilateral common carotid arteries of patient 1, Figure 1 1H is a 3D mDixon-MRA imaging diagram of the bilateral internal carotid arteries of patient 1;

[0024] Figure 2 It is a comparison result diagram of carotid artery imaging of patient 2 provided by an embodiment of the present invention; wherein, Figure 2 2A is a 3D TOF-MRA imaging diagram of the left and right subclavian arteries and the right vertebral artery near the chest of patient 2, Figure 2 2B is a 3D mDixon-MRA imaging diagram of the left and right subclavian arteries and the right vertebral artery near the chest of patient 2;

[0025] Figure 3 It is a comparison result diagram of carotid artery imaging of patient 3 provided by an embodiment of the present invention; wherein, Figure 3 3A is a 3D TOF-MRA imaging diagram of the subclavian artery and vertebral artery of patient 3, Figure 3 3B is a 3D mDixon-MRA imaging diagram of the subclavian artery and vertebral artery of patient 3;

[0026] Figure 4 It is a comparison result diagram of carotid artery imaging of patient 4 provided by an embodiment of the present invention; wherein, Figure 4 4A is a 3D TOF-MRA imaging diagram of the neck arteries of patient 4, Figure 44B is the 3D mDixon-MRA imaging of the carotid artery in patient 4's neck, Figure 4 4C is the CT angiography MIP of the carotid artery in patient 4's neck;

[0027] Figure 5 This is the comparison result diagram of carotid artery imaging of patient 5 provided by the embodiment of the present invention; among them, Figure 5 5A is the 3D TOF-MRA MIP imaging of the carotid artery in patient 5's neck, Figure 5 5B is the 3D mDixon-MRA imaging of the carotid artery in patient 5's neck, Figure 5 5C is the CT angiography MIP of the carotid artery in patient 5's neck. Detailed implementation manners

[0028] Next, the technical solutions in the embodiments of the present invention will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present invention.

[0029] The purpose of the present invention is to provide a magnetic resonance angiography method, system and electronic device, which can improve the image quality and shorten the scanning time when used for carotid artery imaging.

[0030] To make the above objects, features and advantages of the present invention more obvious and understandable, the present invention will be further described in detail below in conjunction with the accompanying drawings and specific implementation manners.

[0031] The improved dual-echo water-fat separation (mDixon) technology uses a shorter TE and different precession frequencies of water and fat to suppress the background signal and generate a relatively stable vascular signal contrast. The radial k-space filling technology can make the MR sequence have better anti-motion artifact ability, higher signal-to-noise ratio (SNR) and contrast-to-noise ratio (CNR), etc. However, the traditional Cartesian linear k-space filling mode is sensitive to motion and is prone to respiratory motion artifacts when used for 3D imaging of the carotid artery root. Compressed sensing (CS) technology can shorten the sampling time and improve the image quality while ensuring the image quality through sparse sampling. Based on this, the present invention combines the radial k-space filling and CS technologies with the mDixon technology to develop a new magnetic resonance angiography sequence (also called a new MRA sequence, 3D mDixon-MRA), and explores its feasibility for carotid artery imaging.

[0032] Based on this, the present invention provides a magnetic resonance angiography method, which includes:

[0033] Acquire magnetic resonance angiography images of the neck artery to be imaged using an improved sequence pattern; the improved sequence pattern is a fusion technology of a three-dimensional imaging sequence pattern, a dual-echo water-fat separation technique, and a compressed sensing technique; the three-dimensional imaging sequence pattern is a 3D acquisition pattern composed of two-dimensional radial acquisition and one-dimensional Cartesian acquisition. Among them, the two-dimensional radial acquisition fills the K-space in a pseudo-golden angle pattern, and adding the one-dimensional Cartesian acquisition forms the final three-dimensional K-space data.

[0034] Embodiment 1

[0035] In this embodiment, taking the modification and optimization of the T1-FFE sequence to form a magnetic resonance angiography sequence as an example, the specific implementation process of the magnetic resonance angiography method provided above by the present invention is described. Specifically, in this embodiment, the mDixon imaging sequence is mainly modified and optimized, and the radial k-space filling technology and the compressed sensing technology are integrated into the mDixon technology to develop a new magnetic resonance angiography sequence (3D mDixon-MRA). The specific steps are as follows:

[0036] Step 1: Change the image data acquisition mode from a 3D Cartesian mode to in-plane pseudo-golden angle radial K-space filling, and then add one-dimensional Cartesian acquisition to form the final three-dimensional K-space data. By repeatedly sampling the K-space center, in-plane artifacts (i.e., image motion artifacts generated due to the influence of the patient's respiratory motion during traditional sequence acquisition) are effectively removed, thereby effectively removing respiratory motion artifacts at the carotid artery root and realizing 3D scanning of the carotid artery with full free breathing.

[0037] Step 2: Change the traditional background suppression out-of-phase technique to a dual-echo water-fat separation (mDIXON) technique, which can simultaneously obtain in-phase, out-of-phase, water-phase, and fat images, and the fat tissue suppression of anatomical parts with complex shapes and heterogeneous structures is more thorough. Compared with the traditional DIXON two-point fixation method, the improved mDIXON technique can use any TE value, and the more flexible selection of the TE time is beneficial to vascular signal imaging, with higher acquisition efficiency. A better scan field of view and spatial resolution can be obtained within the same scan time. Moreover, the 7-peak fat model considers 7 different fat resonance frequencies, making the water-fat separation more effective. Among them, the dual-echo water-fat separation (mDIXON) technique adopted by the present invention is the latest improved dual-echo water-fat separation (mDIXON) technique in the prior art.

[0038] Step 3: Change from the traditional parallel acquisition acceleration mode to the compressed sensing technique in the slice direction to effectively improve the scanning speed, which can improve the acquisition efficiency of the mDixon (in-phase, opposed-phase, water-phase, and fat-phase) sequence and significantly shorten the scanning time of 3D carotid artery imaging. The compressed sensing technique can recover ideal image information from a small amount of pseudo-randomly under-sampled data through sparse sampling and non-linear iterative reconstruction, greatly shortening the sampling time while ensuring image quality.

[0039] Furthermore, in this embodiment, multiple groups of experimental data are used to verify and illustrate the advantages of the magnetic resonance angiography method provided in this embodiment.

[0040] Prospectively collect 45 patients suspected of having cervical artery diseases due to vertigo and transient ischemic attack. All of them completed 3D mDixon-MRA and 3D TOF-MRA examinations. After the scanning, maximum intensity projection (MIP) reconstruction was performed.

[0041] Import the results of 3D mDixon-MRA and 3D TOF-MRA examinations into the Philips workstation. Place circular ROIs with an area greater than 75% of the cross-sectional area of the blood vessels at the roots and mid-distal segments of the bilateral common carotid arteries, the roots and mid-distal segments of the bilateral vertebral arteries, and the roots of the bilateral internal and external carotid arteries. Measure the signal intensity (SI) of each blood vessel, and measure the SI of the bilateral cervical arteries adjacent to the sternocleidomastoid muscle. Measure the standard deviation (SD) of the SI in the background area of the same-layer image, and use the SD as the noise. Take the mean of the bilateral measurement results for analysis. Calculate the signal-to-noise ratio (SNR) and contrast-to-noise ratio (CNR) of the arterial images in the MRA results using formulas (1) and (2).

[0042] SNR = 10 × log 10 (SI 血管 / SD) (1)

[0043] CNR = (SI 血管 -SI 组织 ) / SD (2)

[0044] In the formula, SI 血管 is the signal intensity of the blood vessel, and SI 组织 is the signal intensity of the bilateral cervical arteries adjacent to the sternocleidomastoid muscle.

[0045] Score the original images and MIP images of the cervical artery images according to the 5-point scale method:

[0046] 1 point - The blood vessel boundary is blurred, the background interference is severe, the image artifacts are obvious, and the diagnosis is very uncertain.

[0047] 2 points - The signal of the blood vessel lumen is weak, the details are blurred, the background interference is relatively heavy, the image artifacts are less, and the diagnosis is uncertain.

[0048] 3 points - The display quality of the blood vessels is medium, the details are acceptable, the background suppression is average, there are almost no artifacts, and the diagnosis is certain.

[0049] 4 points - The blood vessels are clearly displayed, the details in the middle and far segments of the blood vessels are acceptable, the background suppression is good, there are no artifacts, and the diagnosis is relatively certain.

[0050] 5 points - The blood vessel boundary is clear, the lumen signal is high, the details are well displayed, the background suppression is good, and the diagnosis is very certain.

[0051] The signal-to-noise ratio (SNR), contrast-to-noise ratio (CNR) of the images, and the visualization effect evaluation scores were statistically analyzed using R software (version 3.6.3). Measurement data conforming to a normal distribution were expressed as

[0052] The SNR of each artery in 3D mDixon-MRA was significantly higher than that in 3D TOF-MRA (all P < 0.01). There was no significant difference in the CNR of the root of the common carotid artery between 3D mDixon-MRA and 3D TOF-MRA (P = 0.13), and the CNR of the remaining arteries was significantly higher than that in 3D TOF-MRA (all P < 0.01). The above comparison results are shown in Tables 1 and 2.

[0053] Table 1 Comparison of arterial SNR between two MRAs (n = 45)

[0054]

[0055] Table 2 Comparison of arterial CNR between two MRAs (n = 45)

[0056]

[0057] During the visualization scoring process, the subjective scores of the root of the common carotid artery, the root of the vertebral artery, and the middle and far segments of the vertebral artery in 3D mDixon-MRA were all higher than those in 3D TOF-MRA (all P < 0.05), and there was no significant difference in the subjective scores of the remaining arteries compared with 3D TOF-MRA (all P > 0.05). The specific evaluation results are shown in Table 3 and Figures 1 to 5 . Among them, Figure 1Contrast results of carotid artery imaging for Patient 1. Patient 1, female, 53 years old, no obvious abnormality was found in the neck arteries. In the contrast results of two original axial MRA images of the neck arteries, the 3D TOF-MRA images from 1A to 1D showed unclear display of the root of the right vertebral artery and blurred vascular boundaries, and poor suppression of fat signals in the neck soft tissues. The visualization scores of the root of the left common carotid artery (arrow in 1A), the roots of both vertebral arteries (arrows in 1B), the mid-distal segments of both common carotid arteries (short arrows in 1C), the mid-distal segments of the vertebral arteries (long arrows in 1C), and the roots of both internal carotid arteries (arrows in 1D) were 3, 2, 5, 5, and 4 respectively. Figure 1 In it, 1E - 1H and Figure 1 the corresponding 3D mDixon-MRA diagrams of 1A - 1D in it showed sharper display of the trachea and vascular boundaries, clear display of the root of the right vertebral artery, and good suppression of fat signals in the neck soft tissues. The visualization scores were 4, 4, 5, 5, and 5 respectively. Figure 2 Contrast results of carotid artery imaging for Patient 2. Patient 2, female, 57 years old, no obvious abnormality was found in the neck arteries. In the contrast results of two reconstructed MIP images of the neck arteries, in the 3D TOF-MRA MIP diagram in 2A, the signal of the lumen of the left (long arrow) and right (short arrow) subclavian arteries near the chest cavity and the root of the right vertebral artery decreased, and the connection of the vascular boundaries was interrupted. The visualization scores of the roots of the common carotid artery and the vertebral artery were 3 and 2 respectively. In the 3D mDixon-MRA MIP diagram corresponding to 2B and 2A, the signal of the vascular lumen was higher and the vascular boundaries were clear. The visualization scores of the roots of the common carotid artery and the vertebral artery were 5 and 4 respectively. Figure 3 Contrast results of carotid artery imaging for Patient 3. Patient 3, male, 62 years old, no obvious abnormality was found in the neck arteries. In the contrast results of two reconstructed MIP images of the neck arteries, in the 3D TOF-MRA MIP diagram in 3A, the signal of the lumen of the left subclavian artery decreased and the connection of the vascular boundaries was interrupted. The roots of the left (long arrow) and right (short arrow) vertebral arteries were blurred. The visualization scores of the roots of the common carotid artery and the vertebral artery were 3 and 2 respectively. In the 3D mDixon-MRA MIP diagram corresponding to 3B and 3A, the signal of the lumen of the subclavian artery and the roots of the vertebral arteries was higher and the vascular boundaries were clear. The visualization scores of the roots of the common carotid artery and the vertebral artery were both 4. Figure 4Contrast results of carotid artery imaging for Patient 4. Patient 4, male, 75 years old, with stenosis at the root of the right vertebral artery. In the 3D TOF-MRA MIP image of the cervical arteries in 4A, the root of the right vertebral artery (short arrow) is missing, and there is an interruption at the tortuous middle and distal segments (long arrow). The visualization scores of the common carotid artery and the root of the vertebral artery are 3 and 1 respectively. In the 3D mDixon-MRA MIP image of the cervical arteries in 4B, the root of the right vertebral artery (short arrow) is stenotic, and the tortuous middle and distal segments (long arrow) are clearly shown. The visualization scores of the common carotid artery and the root of the vertebral artery are both 3. In the MIP image of CT angiography of the cervical arteries in 4C, there is no obvious abnormality at the root of the right vertebral artery (short arrow) and the tortuous middle and distal segments (long arrow). Figure 5 Contrast results of carotid artery imaging for Patient 5. Patient 5, male, 62 years old, with stenosis at the root of the right vertebral artery. In the 3D TOF-MRA MIP image of the cervical arteries in 5A, the root of the right vertebral artery (arrow) is interrupted, and there is no blood flow signal in the lumen. The visualization scores of the common carotid artery and the root of the vertebral artery are 4 and 3 respectively. In the 3D mDixon-MRA MIP image of the cervical arteries in 5B, the root of the right vertebral artery (arrow) is stenotic. The visualization scores of the common carotid artery and the root of the vertebral artery are 5 and 4 respectively. In the MIP image of CT angiography of the cervical arteries in 5C, it shows stenosis at the root of the right vertebral artery (arrow).

[0058] Table 3 Visual evaluation score table of two MRA image qualities (n = 45)

[0059]

[0060] Based on the above description, it can be obtained that the 3D mDixon-MRA sequence obtained by using the magnetic resonance angiography method provided by the present invention can be used for cervical artery imaging, can improve the image quality, shorten the scanning time, and thus can be popularized and applied in clinical practice.

[0061] Example 2

[0062] In this example, a magnetic resonance angiography system is provided to apply the method provided in the above Example 1 to achieve cervical artery imaging. The system includes:

[0063] An imaging sequence acquisition module, configured to acquire magnetic resonance angiography images of the cervical arteries to be imaged by using an improved sequence mode; the improved sequence mode is a fusion technology of a three-dimensional imaging sequence mode, a dual-echo fat-water separation technology, and a compressed sensing technology; the three-dimensional imaging sequence mode is a 3D acquisition mode composed of two-dimensional radial acquisition and one-dimensional Cartesian acquisition.

[0064] A vascular image acquisition module, configured to form magnetic resonance angiography images of the cervical arteries to be imaged based on the magnetic resonance angiography sequence.

[0065] Example 3

[0066] In this example, an electronic device is provided, which includes a memory and a processor.

[0067] The memory is used to store a computer program.

[0068] The processor is connected to the memory to retrieve and execute the computer program to implement the magnetic resonance angiography method provided in the above Example 1.

[0069] In addition, when the computer program in the above memory is implemented in the form of a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on such an understanding, the technical solution of the present invention, in essence, or the part that makes a contribution to the prior art, or a part of the technical solution, can be embodied in the form of a software product. The computer software product is stored in a storage medium and includes several instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to execute all or part of the steps of the methods in various embodiments of the present invention. The foregoing storage medium includes: various media such as USB flash drives, mobile hard disks, read-only memories, random access memories, magnetic disks, or optical discs that can store program codes.

[0070] Furthermore, the neck tissue contour is irregular and belongs to a heterogeneous structure. The mDixon technique is relatively insensitive to the inhomogeneity of the B0 and B1 fields and is suitable for imaging of complex anatomical structures. The present invention combines the radial k-space filling and CS techniques with the mDixon technique to develop a new MRA sequence (3D mDixon-MRA) for neck artery imaging. The results show that the SNR and CNR of each artery in 3D mDixon-MRA are higher than those of the traditional 3D TOF-MRA. The main reasons are as follows:

[0071] ① 3D mDixon-MRA uses a radial trajectory to densely fill the center of the k-space, which can reduce the interference of motion artifacts, improve the image SNR and CNR, compared with the Cartesian acquisition mode used in the traditional 3D TOF-MRA.

[0072] ② The mDixon technique obtains fat and water images based on the difference in the resonance frequencies of fat and water protons. The uniform suppression of peripheral fat in the neck helps to reduce artifacts and suppress background tissues.

[0073] In the present invention, in 3D mDixon-MRA, the scores of the common carotid artery, the root of the vertebral artery, and the middle and distal segments of the vertebral artery with a more tortuous vascular course are higher than those in 3D TOF-MRA, and the visualization effect is better. 3D mDixon-MRA has different phase encoding directions, and the artifacts generated can be distributed in different directions in the image, making them less obvious. Moreover, all the spokes of the radial sampling carry equal amounts of information. Even if the information of some k-space spokes is damaged, the remaining sampling spokes can still be compensated by the averaging effect, reducing the influence of motion artifacts. In contrast, 3D TOF-MRA is prone to generating motion artifacts in the phase encoding direction. In addition, 3D mDixon-MRA uses a gradient echo sequence combined with the mDixon technique. The characteristics of short TR, short TE, and small FA have less impact on blood flow, and the signals of tortuous vessels are not easily saturated. 3D TOF-MRA mainly forms MR signals by using the inflow enhancement effect generated by blood flow perpendicular to the scanning plane. Its basic premise is blood flow. Turbulence formed by blood in the stenotic lumen resulting in the loss of blood flow signals or the saturation of blood flow signals due to the tortuous vascular course can both affect the quality of vascular imaging, thus affecting clinical diagnosis. In addition, since the CS technique utilizes the sparsity and compressibility of signals in a specific transform domain, data is acquired under conditions less than the Nyquist sampling rate, and the original signal can be accurately restored by optimizing the reconstruction algorithm, achieving the purpose of shortening the scanning time and maintaining the original signal. In this group, the scanning time of 3D TOF-MRA was 5 minutes and 48 seconds, and that of 3D mDixon-MRA was 3 minutes and 54 seconds.

[0074] In summary, the 3D mDixon-MRA sequence can be used for neck artery imaging, which can improve the image quality, shorten the scanning time, and can be popularized and applied in clinical practice.

[0075] In this specification, each embodiment is described in a progressive manner. The key point of each embodiment is to illustrate the differences from other embodiments. The same or similar parts among the embodiments can be referred to each other. For the system disclosed in the embodiments, since it corresponds to the method disclosed in the embodiments, the description is relatively simple, and the relevant parts can be referred to the description of the method part.

[0076] In this article, specific examples are used to elaborate on the principles and implementation methods of the present invention. The descriptions of the above embodiments are only used to help understand the method of the present invention and its core idea. At the same time, for those of ordinary skill in the art, based on the idea of the present invention, there will be changes in the specific implementation methods and application scopes. In summary, the content of this specification should not be construed as a limitation to the present invention.

Claims

1. A magnetic resonance angiography method, characterized in that, Applied to carotid artery imaging; the method includes: Acquiring the carotid artery to be imaged using an improved sequence pattern to obtain a magnetic resonance angiography image; the improved sequence pattern is a fusion technology of a three-dimensional imaging sequence pattern, a dual-echo fat-water separation technique, and a compressed sensing technique; the three-dimensional imaging sequence pattern is a 3D acquisition pattern composed of two-dimensional radial acquisition and one-dimensional Cartesian acquisition; fusing the radial k-space filling technique and the compressed sensing technique into the dual-echo fat-water separation technique to obtain a magnetic resonance angiography sequence. The two-dimensional radial acquisition uses a pseudo-golden angle pattern for k-space filling, plus one dimension of Cartesian acquisition to form the final three-dimensional k-space data. When modifying and optimizing the T1-FFE sequence to form the magnetic resonance angiography sequence, acquiring the carotid artery to be imaged using the improved sequence pattern to obtain a magnetic resonance angiography image specifically includes: Changing the 3D Cartesian mode used in the process of obtaining the T1-FFE sequence to an in-plane pseudo-golden angle radial k-space filling mode, and using a one-dimensional Cartesian acquisition mode to form the final three-dimensional k-space data. Changing the opposed-phase technique for suppressing the background used in the process of obtaining the T1-FFE sequence to a dual-echo fat-water separation technique. At the same time, in the slice direction, changing the parallel acquisition acceleration mode used in the process of obtaining the T1-FFE sequence to a compressed sensing technique to form the magnetic resonance angiography sequence.

2. A magnetic resonance angiography system, characterized by Applied to carotid artery imaging; the system is used to implement the magnetic resonance angiography method as claimed in claim 1; the system includes: An imaging sequence acquisition module for acquiring the carotid artery to be imaged using an improved sequence pattern to obtain a magnetic resonance angiography image; the improved sequence pattern is a fusion technology of a three-dimensional imaging sequence pattern, a dual-echo fat-water separation technique, and a compressed sensing technique; the three-dimensional imaging sequence pattern is a 3D acquisition pattern composed of two-dimensional radial acquisition and one-dimensional Cartesian acquisition.

3. An electronic device, characterized in that, Including: A memory for storing a computer program. A processor connected to the memory for retrieving and executing the computer program to implement the magnetic resonance angiography method as claimed in claim 1.

4. The electronic device according to claim 3, characterized in that, The memory is a computer-readable storage medium.

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