Magnetic resonance imaging method and apparatus

Abstract

This disclosure relates to a magnetic resonance imaging method and apparatus, belonging to the field of medical technology. The magnetic resonance imaging method includes: applying a magnetic resonance pulse signal to a test site at a predetermined echo time to obtain an echo signal corresponding to the magnetic resonance pulse signal, wherein the predetermined echo time indicates the time interval between the applied magnetic resonance pulse signal and the received echo signal; performing phase encoding on the echo signal along a predetermined phase encoding direction to obtain an encoded echo signal; and generating a magnetic resonance scan image based on the encoded echo signal. This method can provide more reliable imaging results.

Description

Technical Field

[0001] This disclosure relates to the field of medical technology, and in particular to a magnetic resonance imaging method and apparatus. Background Technology

[0002] TOF-MRA (Time-of-Flight Magnetic Resonance Angiography) is a magnetic resonance angiography technique that generates high-resolution vascular images by detecting the signal differences between flowing blood and stationary tissue. It does not require the injection of contrast agents and is commonly used for the diagnosis of head and neck arterial diseases.

[0003] In TOF-MRA imaging, significant differences in magnetic susceptibility may exist at the detection interface for blood vessels in certain locations, leading to severe artifacts. This will distort the imaging results and affect the accurate assessment of the blood vessel condition.

[0004] The methods described in this section are not necessarily methods that had been previously conceived or adopted. Unless otherwise specified, no method described in this section should be assumed to be relevant art simply because it is included in this section. Similarly, unless otherwise specified, the issues mentioned in this section should not be considered to be generally accepted in any relevant art. Summary of the Invention

[0005] In view of the above, according to a first aspect of this disclosure, a magnetic resonance imaging method is proposed, comprising: applying a magnetic resonance pulse signal to a test site for a predetermined echo time to obtain an echo signal corresponding to the magnetic resonance pulse signal, wherein the predetermined echo time indicates the time interval between applying the magnetic resonance pulse signal and receiving the echo signal; performing phase encoding on the echo signal along a predetermined phase encoding direction to obtain an encoded echo signal; and generating a magnetic resonance scan image based on the encoded echo signal.

[0006] According to a second aspect of this disclosure, a magnetic resonance imaging apparatus is provided, comprising: an application module for applying a magnetic resonance pulse signal to a test site at a predetermined echo time to obtain an echo signal corresponding to the magnetic resonance pulse signal, wherein the predetermined echo time indicates the time interval between applying the magnetic resonance pulse signal and receiving the echo signal; an encoding module for performing phase encoding on the echo signal along a predetermined phase encoding direction to obtain an encoded echo signal; and a generation module for generating a magnetic resonance scan image based on the encoded echo signal.

[0007] According to one or more embodiments of this disclosure, artifacts can be reduced and distortion in the imaging results can be minimized by setting the echo time and phase encoding direction during magnetic resonance imaging, thereby providing more reliable imaging results and providing more accurate imaging basis for determining the state of blood vessels. Attached Figure Description

[0008] The embodiments of the present invention will now be described in detail with reference to the accompanying drawings, so that those skilled in the art can more clearly understand the above and other features and advantages of the present invention, in which: Figure 1 This is a schematic flowchart of a magnetic resonance imaging method according to some embodiments of the present disclosure; Figure 2 This is a schematic diagram of the process for acquiring echo signals and performing flow compensation according to some embodiments of the present disclosure; Figure 3 This is a schematic block diagram of a magnetic resonance imaging apparatus according to some embodiments of the present disclosure; Figure 4 This is a schematic block diagram of a computing device according to some embodiments of the present disclosure; Figure 5 An example of an imaging result obtained according to the magnetic resonance imaging method of this disclosure; Figure 6 This is another example of an imaging result obtained according to the magnetic resonance imaging method of this disclosure; Figure 7 This is yet another example of an imaging result obtained according to the magnetic resonance imaging method of this disclosure. Detailed Implementation

[0009] To provide a clearer understanding of the technical features, objectives, and effects of the present invention, specific embodiments of the invention will now be described with reference to the accompanying drawings, in which the same reference numerals denote the same parts.

[0010] In this document, “illustrative” means “serving as an example, illustration or description”, and any illustration or implementation described herein as “illustrative” should not be construed as a more preferred or advantageous technical solution.

[0011] To keep the drawings concise, only the parts relevant to the invention are shown schematically in each figure, and they do not represent the actual structure of the product. Furthermore, for ease of understanding, in some figures, components with the same structure or function are shown only schematically, or only one is labeled.

[0012] In this article, "one" can mean not only "only one" but also "more than one". In this article, "first", "second", etc., are used only to distinguish one from another, not to indicate their importance, order, or mutual dependence.

[0013] TOF-MRA (Time-of-Flight Magnetic Resonance Angiography) is a magnetic resonance angiography technique that generates high-resolution vascular images by detecting the signal differences between flowing blood and stationary tissue. It does not require the injection of contrast agents and is commonly used for the diagnosis of head and neck arterial diseases.

[0014] In TOF-MRA imaging, significant differences in magnetic susceptibility at the detection interface can occur in certain blood vessels, leading to severe artifacts. For example, in TOF-MRA imaging using a 7-Tesla (7T) ultra-high field magnetic resonance imaging (MRI) device, when imaging the internal carotid artery, the petrous segment of the internal carotid artery, located in the parasellar region (the area around the sella turcica at the base of the skull), exhibits significant magnetic susceptibility differences at the air-bone interface, potentially causing severe magnetization artifacts. This can result in asymmetry and signal loss in blood flow signals. Furthermore, physiological movements such as pulsation artifacts can further degrade image quality, leading to suboptimal visualization of the petrous segment of the internal carotid artery and affecting the accurate assessment of vascular condition.

[0015] To improve imaging quality, the magnetic resonance imaging method provided in this disclosure can be used. By reasonably setting the echo time and phase encoding direction in magnetic resonance imaging, artifacts can be effectively reduced, distortion in the imaging results can be minimized, and more reliable imaging results can be provided, thereby providing more accurate imaging basis for determining the state of blood vessels.

[0016] Exemplary embodiments of this disclosure will now be described in detail with reference to the accompanying drawings.

[0017] This disclosure provides a magnetic resonance imaging method. (See also...) Figure 1 The magnetic resonance imaging method 100 includes steps 110 to 130.

[0018] Step 110: Apply a magnetic resonance pulse signal to the tested area for a predetermined echo time to obtain an echo signal corresponding to the magnetic resonance pulse signal. The predetermined echo time indicates the time interval between applying the magnetic resonance pulse signal and receiving the echo signal.

[0019] Step 120: Perform phase encoding on the echo signal along the predetermined phase encoding direction to obtain the encoded echo signal.

[0020] Step 130: Generate a magnetic resonance scan image based on the encoded echo signal.

[0021] The magnetic resonance imaging method 100 disclosed herein coordinates the echo time and phase encoding direction during the magnetic resonance imaging process, thereby improving the quality of the final image. The magnetic resonance imaging method 100 can be used, for example, in scenarios such as vascular imaging, where the tested area can be blood vessels in areas such as the head and neck.

[0022] During magnetic resonance imaging (MRI), a constant main magnetic field is applied to the tested area of ​​the human body, providing a static magnetic field that forms the physical basis for MRI. Based on this main magnetic field, a radio frequency pulse signal, i.e., an electromagnetic wave of a specific frequency, is applied to invert the magnetization vector, thereby generating an echo signal that can be used for detection. After signal processing, the echo signal can be reconstructed into an image, namely an MRI scan image.

[0023] In step 110, a magnetic resonance pulse signal, i.e., a radio frequency pulse signal, is applied to the main magnetic field at a preset echo time. After the pulse signal is applied to the test site, a corresponding echo signal will be obtained at the test site. In embodiments of this disclosure, "echo time" can indicate the time interval between the application of the magnetic resonance pulse signal and the receipt of the echo signal during magnetic resonance imaging.

[0024] In some embodiments, the predetermined echo time is greater than 1.7 milliseconds (ms) and less than 1.8 milliseconds.

[0025] Currently, in TOF-MRA imaging, the echo time is typically set to an anti-phase value of 3.57 ms; however, this setting has limited effectiveness in suppressing artifacts. In this disclosure, by optimizing and shortening the echo time, the contrast between the scanned object, such as a blood vessel, and the background can be significantly improved.

[0026] In one example, the scheduled echo time can be set to 1.79 ms.

[0027] In addition to the main magnetic field and radio frequency pulse signal, since the received signal is a superposition of echo signals generated throughout the imaging area, it also needs to be spatially encoded to determine the signal's spatial coordinates and achieve spatial localization. This spatial encoding can be achieved by applying a gradient magnetic field, which is superimposed on the main magnetic field. Because the gradient magnetic field typically varies with spatial position, spatial encoding can be implemented to spatially locate the received signal.

[0028] To achieve spatial localization, spatial encoding is typically performed in three directions to achieve three-dimensional spatial localization. In one example, the three encoding directions are slice selection, frequency encoding (also known as readout), and phase encoding. These three encoding directions are distinct from each other, and gradient magnetic fields can be applied in each of these directions to achieve spatial encoding. Based on the spatially encoded echo signal, the three-dimensional spatial information can be integrated to reconstruct the signal intensity of each pixel at each coordinate, thus obtaining the final magnetic resonance imaging (MRI) scan image.

[0029] To achieve the reduction in echo time mentioned above, it can be achieved by optimizing the acquisition bandwidth and motion compensation. Different combinations of acquisition bandwidth and motion compensation can achieve different extreme values ​​for echo time.

[0030] In some embodiments, the magnetic resonance imaging method 100 further includes a first process 200. (Reference) Figure 2 The first process 200 includes steps 210 to 220.

[0031] Step 210: Acquire the echo signal with a predetermined acquisition bandwidth. The predetermined acquisition bandwidth is greater than 530 Hz / pixel and less than 540 Hz / pixel.

[0032] Step 220: Perform flow compensation on the echo signal along a predetermined compensation direction. The predetermined compensation direction includes a predetermined readout direction and a predetermined layer selection direction. The predetermined readout direction and the predetermined layer selection direction are different.

[0033] In some embodiments, step 210 includes: acquiring the echo signal along a predetermined readout direction with a predetermined acquisition bandwidth.

[0034] In magnetic resonance imaging, the acquisition bandwidth (BW) refers to the frequency range of signals sampled in the readout (frequency-encoded) direction, typically expressed in Hertz per pixel (BW). In one example, the predetermined acquisition bandwidth can be set to 531 Hertz per pixel, and in step 210, acquisition can be performed along the readout direction with an acquisition bandwidth of 531 Hertz per pixel.

[0035] In step 220, flow compensation can be used to suppress motion artifacts caused by the flow of blood, cerebrospinal fluid, etc. Flow compensation can be performed in different directions. Currently, in TOF-MRA imaging, flow compensation is typically performed in all three directions: slice selection, readout, and phase encoding. However, in the embodiments of this disclosure, the direction of flow compensation is optimized, and flow compensation is performed only in the readout and slice selection directions.

[0036] By optimizing the acquisition bandwidth and the direction of flow compensation, the echo time can be effectively shortened, further improving the contrast between blood vessels and the background and enhancing imaging quality. Furthermore, using different combinations of acquisition bandwidth and compensation direction allows for adjustment of the echo time, enabling further reduction.

[0037] In some embodiments, the tested region includes the head and neck. The predetermined phase encoding direction includes from the posterior side of the head and neck to the anterior side.

[0038] As mentioned above, imaging results may be poor for blood vessels in the head and neck, such as the petrous segment of the internal carotid artery. Therefore, for magnetic resonance imaging (MRI) of the head and neck, phase encoding can be performed from a specific encoding direction. In traditional MRI, the phase encoding direction is usually from left to right. However, in the embodiments of this disclosure, the phase encoding direction is changed to back to front, that is, from the back of the head and neck to the front, which can also be understood as from the plane of the back of the body to the plane of the face. Changing the phase encoding direction to back to front allows the pulsation artifacts of blood vessels such as the internal carotid artery to be aligned along the sagittal axis of the body (i.e., from the ventral side to the dorsal side, perpendicular to the long axis of the body), which can effectively reduce the phenomenon of crossover and overlap of the petrous segments of the bilateral internal carotid arteries on the image plane and improve image quality.

[0039] By co-optimizing echo time and phase encoding direction, rather than relying on a single shimming technique, the effects of magnetic susceptibility and physiological motion on imaging results can be improved simultaneously, resulting in more realistic imaging results.

[0040] In some embodiments, the predetermined readout direction, the predetermined layer selection direction, and the predetermined phase encoding direction are perpendicular to each other.

[0041] As mentioned above, three encoding directions are used to achieve 3D spatial positioning. The predetermined layer selection direction is used to determine the imaging layer, the predetermined readout direction enables positioning along the readout direction, and the predetermined phase encoding direction enables positioning along the phase encoding direction. Therefore, setting these three directions to be perpendicular to each other allows for better and more accurate 3D positioning. In one example, the predetermined phase encoding direction is the back-to-front direction mentioned above, the predetermined readout direction is the left-to-right direction of the human body, and the predetermined layer direction is the top-to-bottom direction of the human body.

[0042] In some embodiments, step 130 includes: generating magnetic resonance imaging images with predetermined spatial resolutions in a predetermined readout direction, a predetermined layer selection direction, and a predetermined phase encoding, based on the encoded echo signal. The spatial resolutions of the predetermined readout direction, the predetermined layer selection direction, and the predetermined phase encoding are equal.

[0043] While optimizing echo time and phase encoding direction, high-resolution isotropic voxels can be maintained, meaning that the same isotropic high spatial resolution is maintained in three encoding directions: the predetermined readout direction, the predetermined layer selection direction, and the predetermined phase encoding. High-resolution isotropic voxels are a special acquisition and reconstruction method in magnetic resonance imaging, referring to cubic pixels with the same spatial resolution in three directions. Because voxels are cubes, multi-plane image reconstruction can be performed along any plane after scanning, without the image blurring caused by low resolution in a certain direction as in 2D scanning.

[0044] In one example, a cubic pixel of 0.4 × 0.4 × 0.4 mm³ can be used, which means a spatial resolution of 0.4 mm in each direction, thereby achieving high resolution, maintaining the ability to visualize smaller blood vessels, and preventing fine structures from being "averaged" out by a thicker direction, resulting in a clearer and more accurate display.

[0045] By adjusting the spatial resolution, the echo time can also be adjusted. For example, the echo time can be shortened by increasing the spatial resolution to meet the imaging requirements of certain specific scenarios.

[0046] In some embodiments, the magnetic resonance pulse signal has a predetermined repetition time and a predetermined flip angle. The predetermined repetition time indicates the time interval between any two adjacent pulses in the magnetic resonance pulse signal and is set to be greater than 20 milliseconds and less than 30 milliseconds. The predetermined flip angle indicates the deviation angle of the magnetization vector during the application of the magnetic resonance pulse signal and is set to be greater than 20 degrees and less than 30 degrees.

[0047] Repetition time (TR) indicates the time interval between two adjacent radio frequency (RF) pulses. Flip angle (FA) indicates the angle by which the longitudinal magnetization vector deviates from the direction of the main magnetic field after the application of an RF pulse signal in magnetic resonance imaging.

[0048] While optimizing the echo time and phase encoding direction, the repetition time and flip angle can be set collaboratively to improve imaging performance. In one example, the predetermined repetition time can be set to 25 ms, and the predetermined flip angle can be set to 25 degrees.

[0049] In some embodiments, the magnetic resonance imaging method 100 further includes: acquiring echo signals within a predetermined acquisition time. The predetermined acquisition time is greater than 8 minutes and less than 9 minutes.

[0050] Acquisition time (TA) indicates the total time required to complete a single data acquisition in magnetic resonance imaging (MRI). In one example, the predetermined acquisition time could be set to 8 minutes and 15 seconds. By setting the acquisition time appropriately, a reasonable trade-off can be achieved between scanning efficiency and image quality, improving imaging efficiency while maintaining good image quality.

[0051] Table 1 illustrates the four configuration combinations used in magnetic resonance imaging. TE indicates echo time, Phase encoding indicates phase encoding direction, Bandwidth indicates acquisition bandwidth, Flow compensation indicates flow compensation direction, TA indicates acquisition time, TR indicates repetition time, FA indicates flip angle, and Voxel size indicates spatial resolution.

[0052] Table 1

[0053] As shown in Table 1, in Group A, an echo time of 3.57 ms was used, with a phase encoding direction from left to right (L>>R), an acquisition bandwidth of 531 Hz / Px, and flow compensation directions of slice selection and readout. The acquisition time was 8 minutes and 15 seconds, the repetition time was 25 ms, the flip angle was 25°, and an isometric high spatial resolution of 0.4×0.4×0.4 mm³ was used. In Group B, an echo time of 3.57 ms was used, with a phase encoding direction from back to front (P>>A), an acquisition bandwidth of 531 Hz / Px, and flow compensation directions of slice selection and readout. The acquisition time was 8 minutes and 15 seconds, the repetition time was 25 ms, the flip angle was 25°, and an isometric high spatial resolution of 0.4×0.4×0.4 mm³ was used. In Group C, an echo time of 1.79 ms was used, with phase encoding from left to right (L>>R), an acquisition bandwidth of 531 Hz / Px, and flow compensation in both slice and readout directions. The acquisition time was 8 minutes and 15 seconds, the repetition time was 25 ms, the flip angle was 25°, and an isometric high spatial resolution of 0.4 × 0.4 × 0.4 mm³ was used. In Group D, an echo time of 1.79 ms was used, with phase encoding from back to front (P>>A), an acquisition bandwidth of 531 Hz / Px, and flow compensation in both slice and readout directions. The acquisition time was 8 minutes and 15 seconds, the repetition time was 25 ms, the flip angle was 25°, and an isometric high spatial resolution of 0.4 × 0.4 × 0.4 mm³ was used.

[0054] Figures 5 to 7 The images illustrate the original TOF-MRA images and maximum intensity projection (MIP) reconstructed images obtained by magnetic resonance imaging of different test subjects using configurations A through D.

[0055] Figure 5 The test subject was a healthy 17-year-old male, and imaging of the internal carotid artery was performed using four different configurations. Figure 5 As can be seen, taking the blood vessel indicated by the red circle on the left as an example, the image obtained using the D configuration is significantly clearer. (Comparison) Figure 5 The imaging results from the four configurations show that shorter echo times (groups C and D) significantly reduce the distortion of the cross-sectional shape of the petrous segment of the internal carotid artery compared to longer echo times (groups A and B).

[0056] Figure 6 The test subject was a healthy 35-year-old woman, and imaging of the internal carotid artery was performed using four different configurations. Figure 6As can be seen, the image obtained using the D group configuration is also clearer. (Comparison) Figure 6 The imaging results from the four configurations show that when the phase encoding direction is from back to front (P>>A) (groups B and D), the vascular pulsation artifacts are arranged along the posterior-anterior direction, thus avoiding mutual interference between bilateral vessels and making the blood flow signal more uniform. In addition, for groups with the same phase encoding direction, a shorter echo time (comparison between group C and group A) significantly reduced vascular pulsation artifacts.

[0057] Figure 7 The test subject was a 77-year-old male with atherosclerosis, and imaging of the internal carotid artery was performed using four different configurations. Figure 7 As can be seen, the image obtained using the D group configuration is also clearer and does not exhibit the artifacts found in the A group imaging results. (Comparison) Figure 7 The imaging results from the four configurations show that shorter echo times (groups C and D) are more effective in suppressing vascular pulsation artifacts, and shortening the echo time can improve the uniformity of blood flow signals. In addition, under the condition of pulsation artifacts, using the phase encoding direction from back to front (P>>A) (groups B and D) can effectively prevent cross-vessel interference caused by pulsation-related artifacts.

[0058] from Figures 5 to 7 As can be seen, shortening the echo time to 1.79 ms, a reduction of approximately 50%, effectively improves image quality. For example, it can reduce the distortion of the cross-sectional shape of the petrous segment of the internal carotid artery by 60-80% and improve signal homogeneity. Furthermore, the phase encoding direction from posterior to anterior (P>>A) changes the artifact distribution from transverse (interfering with bilateral vessels) to longitudinal (harmless), effectively reducing the cross-artifact effect in patients with severe pulsation and resulting in more accurate and clear imaging results. Due to the improved visualization score of vessels and increased clarity of vessel wall boundaries, more reliable imaging data can be provided, leading to accurate assessments of vascular condition.

[0059] Based on the same technical concept, embodiments of this application provide a magnetic resonance imaging (MRI) apparatus. Embodiments of the MRI apparatus can be referenced to embodiments of the MRI method; repeated details will not be repeated. Reference Figure 3 The magnetic resonance imaging device 300 includes an application module 310, an encoding module 320, and a generation module 330.

[0060] The application module 310 is used to apply a magnetic resonance pulse signal to the tested area for a predetermined echo time to obtain an echo signal corresponding to the magnetic resonance pulse signal. The predetermined echo time indicates the time interval between applying the magnetic resonance pulse signal and receiving the echo signal.

[0061] The encoding module 320 is used to perform phase encoding on the echo signal along a predetermined phase encoding direction to obtain the encoded echo signal.

[0062] The generation module 330 is used to generate magnetic resonance scan images based on the encoded echo signals.

[0063] The application module 310, encoding module 320, and generation module 330 in the magnetic resonance imaging apparatus 300 can correspond to steps 110 to 130 in the magnetic resonance imaging method 100, and will not be described in detail here for the sake of brevity. It should be understood that, corresponding to the embodiments of the magnetic resonance imaging method 100, the embodiments of the magnetic resonance imaging apparatus 300 may also include more modules.

[0064] It should be noted that the functions of the modules discussed herein can be divided into multiple modules, and / or at least some functions of multiple modules can be combined into a single module. The specific actions performed by a particular module discussed herein include the specific module itself performing the action, or alternatively, the specific module calling or otherwise accessing another component or module that performs the action (or performs the action in conjunction with the specific module). Therefore, a specific module performing an action can include the specific module performing the action itself and / or another module that performs the action, called or otherwise accessed by the specific module.

[0065] It should also be understood that this article can describe various technologies in the general context of software and hardware components or program modules. The above regarding... Figure 3 The described modules can be implemented in hardware or in hardware in combination with software and / or firmware. For example, these modules can be implemented as computer program code / instructions configured to execute in one or more processors and stored in a computer-readable storage medium. Alternatively, these modules can be implemented as hardware logic / circuit. Hardware logic / circuit may include integrated circuit chips (which include processors (e.g., Central Processing Unit (CPU), microcontrollers, microprocessors, digital signal processors (DSPs), etc.), memory, one or more communication interfaces, and / or one or more components in other circuitry), and may optionally execute received program code and / or include embedded firmware to perform functions.

[0066] This application embodiment provides a computing device 400, such as... Figure 4 As shown. Figure 4An example configuration of a computing device 400 that can be used to implement the magnetic resonance imaging method 100 described herein is shown. For example, the magnetic resonance imaging apparatus 300 described above may be implemented wholly or at least partially by the computing device 400 or a similar device or system.

[0067] The computing device 400 may include at least one processor 405 capable of communicating with each other, such as via a bus 404 or other suitable connection, a memory 407, multiple communication interfaces 402, a display device 401, other input / output (I / O) devices 403, and one or more mass storage devices 406. Instructions are stored on the memory 407 that, when executed by the processor 405, cause the processor 405 to perform the magnetic resonance imaging method as described in the above embodiments.

[0068] The computing device 400 can be a variety of different types of devices. Examples of the computing device 400 include, but are not limited to: desktop computers, server computers, laptop or netbook computers, mobile devices (e.g., tablets, cellular or other wireless phones (e.g., smartphones), notebook computers, mobile stations), wearable devices (e.g., glasses, watches), entertainment devices (e.g., entertainment appliances, set-top boxes communicatively coupled to a display device, game consoles), televisions or other display devices, automotive computers, and so on.

[0069] Processor 405 may be a single processing unit or multiple processing units, and all processing units may include single or multiple computing units or multiple cores. Processor 405 may be implemented as one or more microprocessors, microcomputers, microcontrollers, digital signal processors, central processing units, state machines, logic circuits, and / or any device that manipulates signals based on operating instructions. Among other capabilities, processor 405 may be configured to acquire and execute computer-readable instructions stored in memory 407, mass storage device 406, or other computer-readable media, such as program code of operating system 408, program code of application program 409, program code of other program 410, etc.

[0070] Memory 407 and mass storage device 406 are examples of computer-readable storage media for storing instructions executed by processor 405 to perform the various functions described above. For example, memory 407 may generally include both volatile and non-volatile memory (e.g., RAM, ROM, etc.). Furthermore, mass storage device 406 may generally include hard disk drives, solid-state drives, removable media, including external and removable drives, memory cards, flash memory, floppy disks, optical disks (e.g., CDs, DVDs), storage arrays, network-attached storage, storage area networks, etc. Both memory 407 and mass storage device 406 may be collectively referred to herein as memory or computer-readable storage media, and may be non-transitory media capable of storing computer-readable, processor-executable program instructions as computer program code, which may be executed by processor 405 as a specific machine configured to perform the operations and functions described in the examples herein.

[0071] Multiple programs may be stored on mass storage device 406. These programs include operating system 408, one or more application programs 409, other programs 410, and program data 411, and they may be loaded into memory 407 for execution. Examples of such application programs or program modules may include, for example, computer program logic (e.g., computer program code or instructions) for implementing components / functions such as magnetic resonance imaging apparatus 300 (including application module 310, encoding module 320, and generation module 330), magnetic resonance imaging method 100 (including any suitable steps of magnetic resonance imaging method 100), and / or other embodiments described herein.

[0072] Although Figure 4 The data is illustrated as being stored in memory 407 of computing device 400, but operating system 408, application program 409, other programs 410 and program data 411 or portions thereof may be implemented using any form of computer-readable medium accessible by computing device 400.

[0073] One or more communication interfaces 402 are used for exchanging data with other devices, such as via a network, direct connection, etc. Such communication interfaces can be one or more of the following: any type of network interface (e.g., a network interface card (NIC)), wired or wireless (such as IEEE 802.11 Wireless LAN (WLAN)) wireless interface, Wi-MAX interface, Ethernet interface, Universal Serial Bus (USB) interface, cellular network interface, Bluetooth™ interface, Near Field Communication (NFC) interface, etc. Communication interface 402 can facilitate communication across various network and protocol types, including wired networks (e.g., LAN, cable, etc.) and wireless networks (e.g., WLAN, cellular, satellite, etc.), the Internet, etc. Communication interface 402 can also provide communication with external storage devices (not shown), such as storage arrays, network-attached storage, storage area networks, etc.

[0074] In some examples, a display device 401, such as a monitor, may be included for displaying information and images to the user. Other I / O devices 403 may be devices that receive various inputs from the user and provide various outputs to the user, and may include touch input devices, gesture input devices, cameras, keyboards, remote controls, mice, printers, audio input / output devices, and so on.

[0075] The technologies described herein can be supported by these various configurations of computing device 400, and are not limited to specific examples of the technologies described herein. For example, the functionality can also be implemented wholly or partially on a “cloud” using a distributed system. A cloud includes and / or represents a platform for resources. The platform abstracts the underlying functionality of the cloud’s hardware (e.g., servers) and software resources. Resources may include applications and / or data that can be used when performing computational processing on servers remote from computing device 400. Resources may also include services provided via the Internet and / or via subscriber networks such as cellular or Wi-Fi networks. The platform can abstract resources and functionality to connect computing device 400 to other computing devices. Therefore, the implementation of the functionality described herein can be distributed throughout the cloud. For example, the functionality can be implemented partly on computing device 400 and partly through a platform that abstracts the functionality of the cloud.

[0076] This application also provides a computer-readable storage medium storing instructions that, when executed individually or jointly by one or more processors of a computing device, cause the computing device to perform the methods described in any of the above embodiments.

[0077] Computer-readable storage media include volatile and non-volatile, removable and non-removable media implemented by any method or technology for storing information such as computer-readable instructions, data structures, program modules, or other data. Computer-readable storage media include, but are not limited to, RAM, ROM, EEPROM, flash memory or other memory technologies, CD-ROM, Digital Universal Disc (DVD) or other optical storage devices, magnetic cassettes, magnetic tapes, disk storage devices or other magnetic storage devices, or any other non-transmission medium that can be used to store information for access by computer equipment.

[0078] This application also provides a computer program product including instructions that, when executed individually or jointly by one or more processors of a computing device, cause the computing device to perform the methods as described in any of the above embodiments.

[0079] The above description is merely an embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A magnetic resonance imaging method, comprising: A magnetic resonance pulse signal is applied to the test site for a predetermined echo time to obtain an echo signal corresponding to the magnetic resonance pulse signal. The predetermined echo time indicates the time interval between applying the magnetic resonance pulse signal and receiving the echo signal. The echo signal is phase-coded along a predetermined phase coding direction to obtain a coded echo signal; and A magnetic resonance imaging image is generated based on the encoded echo signal.

2. The magnetic resonance imaging method according to claim 1, wherein, The predetermined echo time is greater than 1.7 milliseconds and less than 1.8 milliseconds.

3. The magnetic resonance imaging method according to claim 1, wherein, The tested area includes the head and neck, and the predetermined phase encoding direction includes from the posterior side of the head and neck to the anterior side of the head and neck.

4. The magnetic resonance imaging method according to any one of claims 1-3, further comprising: The echo signal is acquired with a predetermined acquisition bandwidth, wherein the predetermined acquisition bandwidth is greater than 530 Hz / pixel and less than 540 Hz / pixel; as well as The echo signal is flow compensated along a predetermined compensation direction, which includes a predetermined readout direction and a predetermined layer selection direction, and the predetermined readout direction and the predetermined layer selection direction are different.

5. The magnetic resonance imaging method according to claim 4, wherein, The predetermined readout direction, the predetermined layer selection direction, and the predetermined phase encoding direction are all perpendicular to each other.

6. The magnetic resonance imaging method according to claim 4, wherein, The acquisition of the echo signal with a predetermined acquisition bandwidth includes: The echo signal is acquired along the predetermined readout direction with the predetermined acquisition bandwidth.

7. The magnetic resonance imaging method according to claim 4, wherein, The process of generating a magnetic resonance imaging image based on the encoded echo signal includes: Based on the encoded echo signal, the magnetic resonance scanning image is generated at a predetermined spatial resolution in the predetermined readout direction, the predetermined layer selection direction, and the predetermined phase encoding, respectively, wherein the spatial resolution of the predetermined readout direction, the spatial resolution of the predetermined layer selection direction, and the spatial resolution of the predetermined phase encoding are equal.

8. The magnetic resonance imaging method according to any one of claims 1-3, wherein, The magnetic resonance pulse signal has a predetermined repetition time and a predetermined flip angle, wherein the predetermined repetition time indicates the time interval between any two adjacent pulses in the magnetic resonance pulse signal and is set to be greater than 20 milliseconds and less than 30 milliseconds, and the predetermined flip angle indicates the deviation angle of the magnetization vector during the application of the magnetic resonance pulse signal and is set to be greater than 20 degrees and less than 30 degrees.

9. The magnetic resonance imaging method according to any one of claims 1-3, further comprising: The echo signal is acquired within a predetermined acquisition time, which is greater than 8 minutes and less than 9 minutes.

10. A magnetic resonance imaging device, comprising: An application module is used to apply a magnetic resonance pulse signal to the test site for a predetermined echo time to obtain an echo signal corresponding to the magnetic resonance pulse signal, wherein the predetermined echo time indicates the time interval between applying the magnetic resonance pulse signal and receiving the echo signal; An encoding module is used to perform phase encoding on the echo signal along a predetermined phase encoding direction to obtain an encoded echo signal; as well as The generation module is used to generate a magnetic resonance scan image based on the encoded echo signal.

Images