Magnetic resonance imaging method, apparatus and device

Abstract

The present application relates to a magnetic resonance imaging method, apparatus, and device, wherein the magnetic resonance imaging method is used to generate a first image and a second image in a single magnetic resonance scan; the method comprises: acquiring a myocardial signal of a scanned patient, the myocardial signal comprising multiple consecutive cardiac cycles; determining a first acquisition period and a second acquisition period within the same cardiac cycle, acquiring first K-space data of a region of interest of the scanned subject during the first acquisition period, and acquiring second K-space data of a region of interest of the scanned subject during the second acquisition period; generating a first image based on the first K-space data, and generating a second image based on the second K-space data. This application solves the problem in the prior art that a single magnetic resonance scan can only complete one type of K-space data acquisition and generate one type of magnetic resonance image, reduces the number of magnetic resonance scans, and has the technical effect of higher image generation efficiency.

Description

Technical Field

[0001] The present application relates to the field of magnetic resonance imaging, and in particular to a magnetic resonance imaging method, apparatus and device. Background Art

[0002] Cardiac delayed enhancement MRI is typically performed 10 minutes after contrast agent injection. Using a fast gradient echo imaging sequence under ECG-gated triggering, the imaging sequence utilizes nonselective inversion recovery pulse preparation to selectively suppress normal myocardial signal and highlight enhanced infarcted myocardial tissue. Gradient echo imaging can be performed using either a standard gradient echo (GRE) sequence or a balanced steady-state free precession (GRE_BSSFP) sequence. The GRE_BSSFP sequence offers rapid imaging and a high signal-to-noise ratio, making it suitable for free-breathing delayed enhancement imaging. However, it is associated with inherent black band artifacts.

[0003] Magnetic resonance coronary imaging generally refers to a non-invasive examination technology that uses CT to examine the coronary arteries of the heart by injecting an enhancement agent through the superficial vein to understand whether there are stenosis lesions in the coronary arteries and to make a diagnosis based on the location, range, severity, and wall condition of the lesions.

[0004] Currently, delayed enhancement cardiac MRI and coronary MRI are two completely independent techniques, requiring separate MRI scans to acquire the corresponding imaging data. These separate scans result in longer scan times and lower MRI scanning efficiency.

[0005] Currently, no effective solution has been proposed to address the problem that delayed enhancement cardiac magnetic resonance imaging and coronary magnetic resonance imaging require separate magnetic resonance scans to collect data, resulting in long magnetic resonance scanning time and low scanning efficiency. Summary of the Invention

[0006] In this embodiment, a magnetic resonance imaging method, apparatus, system, electronic device and storage medium are provided to solve the problem in the related art that magnetic resonance cardiac delayed enhancement imaging and magnetic resonance coronary imaging require separate magnetic resonance scans to collect data, resulting in long magnetic resonance scanning time and low scanning efficiency.

[0007] In a first aspect, a magnetic resonance imaging method is provided in this embodiment, wherein the method is used to generate a first image and a second image in a single magnetic resonance scan;

[0008] The method comprises:

[0009] Acquiring a myocardial signal of a scanned patient, wherein the myocardial signal includes a plurality of continuous cardiac cycles;

[0010] Determining a first acquisition period and a second acquisition period within the same cardiac cycle, acquiring first K-space data of a region of interest of the scanned object within the first acquisition period, and acquiring second K-space data of the region of interest of the scanned object within the second acquisition period;

[0011] The first image is generated based on the first K-space data, and the second image is generated based on the second K-space data.

[0012] In some embodiments, determining the first acquisition period and the second acquisition period within the same cardiac cycle includes:

[0013] Determining a start time of the first acquisition period, and determining an end time of the first acquisition period according to the start time of the first acquisition period;

[0014] A start time of the second acquisition period is determined, and an end time of the second acquisition period is determined according to the start time of the second acquisition period.

[0015] In some embodiments, there is a same acquisition period between the first acquisition period and the second acquisition period;

[0016] The first K-space data and the second K-space data have the same K-space data.

[0017] The acquiring of first K-space data in the first acquisition period and the acquiring of second K-space data in the second acquisition period include:

[0018] The same K-space data is acquired within the same acquisition period.

[0019] In some embodiments, the plurality of consecutive cardiac cycles include first cardiac cycles and second cardiac cycles alternating with each other;

[0020] Determining the first acquisition period and the second acquisition period within the same cardiac cycle includes:

[0021] The first acquisition period and the second acquisition period are determined in each of the first cardiac cycles, and a third acquisition period is determined in the second cardiac cycle.

[0022] In some embodiments, determining the first acquisition period and the second acquisition period within the same cardiac cycle includes:

[0023] The first acquisition period and the second acquisition period are determined in each cardiac cycle.

[0024] In some embodiments, determining the first acquisition period and the second acquisition period within the same cardiac cycle includes:

[0025] applying an inversion recovery preparation pulse during the cardiac cycle;

[0026] A first acquisition period and a second acquisition period are determined after the inversion recovery preparation pulse; wherein the first acquisition period and the inversion recovery preparation pulse have a first time interval, and the second acquisition period and the inversion recovery preparation pulse have a second time interval.

[0027] In some embodiments, the first image is a delayed enhancement cardiac image, and the second image is a coronary artery image.

[0028] In some embodiments, determining the first acquisition period and the second acquisition period within the same cardiac cycle includes:

[0029] determining a period of relative cardiac rest within the cardiac cycle;

[0030] The first acquisition period and the second acquisition period are determined during a period in the cardiac cycle when the heart is relatively still.

[0031] In a second aspect, a magnetic resonance imaging apparatus is provided in this embodiment, wherein the apparatus is configured to generate a first image and a second image in a single magnetic resonance scan;

[0032] The device comprises:

[0033] An information acquisition module, configured to acquire a myocardial signal of a scanned patient, wherein the myocardial signal includes a plurality of continuous cardiac cycles;

[0034] a data acquisition module, configured to determine a first acquisition period and a second acquisition period within the same cardiac cycle, acquire first K-space data of a region of interest of the scanned object within the first acquisition period, and acquire second K-space data of the region of interest of the scanned object within the second acquisition period;

[0035] An image generating module is configured to generate the first image based on the first K-space data and to generate the second image based on the second K-space data.

[0036] In a third aspect, a magnetic resonance imaging device is provided in this embodiment, comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor implements the magnetic resonance imaging method described in the first aspect when executing the computer program.

[0037] In a fourth aspect, a storage medium is provided in this embodiment, on which a computer program is stored. When the program is executed by a processor, the magnetic resonance imaging method described in the first aspect is implemented.

[0038] Compared to related technologies, the magnetic resonance imaging method provided in this embodiment uses an MRI scanner to acquire both first and second K-space data during the same cardiac cycle of a patient. Therefore, the MRI scanning system can simultaneously acquire both first and second K-space data during a single scan, eliminating the need for separate acquisitions through two MRI scans. This allows for simultaneous generation of the first and second images. Compared to prior art methods in which a single MRI scan only acquires one type of K-space data and generates one MRI image, the MRI imaging method provided in this embodiment reduces the number of MRI scans and achieves a more efficient image generation process.

[0039] The details of one or more embodiments of the present application are set forth in the following drawings and description to make other features, objects, and advantages of the present application more readily apparent. BRIEF DESCRIPTION OF THE DRAWINGS

[0040] The drawings described herein are used to provide a further understanding of the present application and constitute a part of the present application. The illustrative embodiments of the present application and their descriptions are used to explain the present application and do not constitute an improper limitation on the present application. In the drawings:

[0041] Figure 1 FIG. 4 is a block diagram of the hardware structure of a terminal of the magnetic resonance imaging method according to this embodiment.

[0042] Figure 2 FIG. 4 is a flow chart of the magnetic resonance imaging method of this embodiment.

[0043] Figure 3 This is a schematic diagram of the partial overlap of the first acquisition period and the second acquisition period in this embodiment.

[0044] Figure 4 This is a magnetic resonance imaging timing diagram in this preferred embodiment.

[0045] Figure 5 This is another magnetic resonance imaging timing diagram in this preferred embodiment.

[0046] Figure 6 This is another magnetic resonance imaging timing diagram in this preferred embodiment.

[0047] Figure 7 FIG. 4 is a block diagram of the structure of the magnetic resonance imaging apparatus of this embodiment. DETAILED DESCRIPTION

[0048] In order to more clearly understand the purpose, technical solutions and advantages of the present application, the present application is described and illustrated below in conjunction with the accompanying drawings and embodiments.

[0049] Unless otherwise defined, the technical terms or scientific terms involved in this application should have the general meaning understood by people with ordinary skills in the technical field to which this application belongs. The words "one", "an", "a", "the", "these" and the like in this application do not indicate quantitative restrictions, and they can be singular or plural. The terms "include", "comprise", "have" and any variants thereof involved in this application are intended to cover non-exclusive inclusions; for example, a process, method and system, product or device comprising a series of steps or modules (units) is not limited to the listed steps or modules (units), but may include unlisted steps or modules (units), or may include other steps or modules (units) inherent to these processes, methods, products or devices. The words "connect", "connected", "coupled" and the like involved in this application are not limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. The "plurality" involved in this application refers to two or more. "And / or" describes the relationship between related objects, indicating that three possible relationships exist. For example, "A and / or B" can represent: A exists alone, A and B exist simultaneously, and B exists alone. Generally, the character " / " indicates that the related objects are in an "or" relationship. The terms "first," "second," "third," etc. used in this application are only used to distinguish similar objects and do not represent a specific ordering of the objects.

[0050] The method embodiment provided in this embodiment can be executed in a terminal, a computer or a similar computing device. For example, running on a terminal, Figure 1 FIG. 1 is a block diagram of the hardware structure of the terminal of the magnetic resonance imaging method of this embodiment. Figure 1 As shown, the terminal may include one or more ( Figure 1 Only one is shown) a processor 102 and a memory 104 for storing data, wherein the processor 102 may include but is not limited to a processing device such as a microprocessor MCU or a programmable logic device FPGA. The above terminal may also include a transmission device 106 and an input and output device 108 for communication functions. It will be understood by those skilled in the art that Figure 1 The structure shown is only for illustration and does not limit the structure of the above terminal. Figure 1 More or fewer components than shown, or with Figure 1 Different configurations shown.

[0051] The memory 104 can be used to store computer programs, such as software programs and modules of application software, such as the computer program corresponding to the magnetic resonance imaging method in this embodiment. The processor 102 executes the computer programs stored in the memory 104 to perform various functional applications and data processing, thereby implementing the above-mentioned method. The memory 104 may include high-speed random access memory (RAM) and may also include non-volatile memory, such as one or more magnetic storage devices, flash memory, or other non-volatile solid-state memory. In some examples, the memory 104 may further include memory remotely located relative to the processor 102, and such remote memory may be connected to the terminal via a network. Examples of such networks include, but are not limited to, the Internet, an intranet, a local area network, a mobile communication network, and combinations thereof.

[0052] The transmission device 106 is used to receive or send data via a network. The network may include a wireless network provided by the terminal's telecommunications provider. In one embodiment, the transmission device 106 includes a network interface controller (NIC), which can be connected to other network devices via a base station to enable communication with the Internet. In another embodiment, the transmission device 106 may be a radio frequency (RF) module, which is used to communicate with the Internet wirelessly.

[0053] In this embodiment, a magnetic resonance imaging method is provided, which is used to generate a first image and a second image in a single magnetic resonance scan. Specifically, magnetic resonance scanning has multiple types of imaging, such as magnetic resonance coronary imaging, delayed enhancement magnetic resonance imaging, etc. In the prior art, generally only one imaging operation can be performed in a single magnetic resonance scan. When a patient requires different magnetic resonance images, multiple magnetic resonance scans are required to obtain different magnetic resonance images. The magnetic resonance imaging method provided in this embodiment can generate a first image and a second image in a single magnetic resonance scan. The first image and the second image correspond to different magnetic resonance images, respectively, thereby improving the efficiency of magnetic resonance imaging. Figure 2 is a flow chart of the magnetic resonance imaging method of this embodiment, as shown in FIG. Figure 2 As shown, the process includes the following steps:

[0054] Step S210 , acquiring a myocardial signal of the scanned patient, where the myocardial signal includes a plurality of continuous cardiac cycles.

[0055] Specifically, the myocardial signal is obtained by a cardiac monitoring device, such as an electrocardiogram. The myocardial signal is mainly used to determine the cardiac condition of the scanned object. Therefore, in this step, multiple continuous cardiac cycles are also determined based on the myocardial signal of the scanned object, so as to facilitate the subsequent acquisition of K-space data within the cardiac cycle. Magnetic resonance imaging technology requires corresponding K-space data to generate magnetic resonance images, and magnetic resonance scanning is to acquire corresponding scanning data within the patient's cardiac cycle to form K-space data, and finally reconstruct these K-space data to generate corresponding images. Specifically, inverse Fourier transform can be used to achieve image reconstruction. Therefore, the magnetic resonance scanning system needs to determine the myocardial signal of the patient to be scanned during the magnetic resonance scanning process. The myocardial signal includes multiple continuous cardiac cycles. After the patient's cardiac cycle is determined, K-space data is then acquired within the cardiac cycle.

[0056] Step S220 , determining a first acquisition period and a second acquisition period in the same cardiac cycle, acquiring first K-space data of the region of interest of the scanned object in the first acquisition period, and acquiring second K-space data of the region of interest of the scanned object in the second acquisition period.

[0057] Specifically, the region of interest refers to the chest, abdomen, heart, etc. The region of interest for each MRI scan is determined based on the actual conditions of the scanned subject. Furthermore, the MRI scanning process acquires K-space data of the scanned subject's region of interest. The MRI scanning system determines the first and second acquisition periods within the same cardiac cycle, meaning that the first and second acquisition periods fall within the same cardiac cycle. It should be noted that the first and second acquisition periods can partially overlap or be completely independent, and the specific determination can be based on actual conditions. Furthermore, the first and second acquisition periods can be determined within a continuous cardiac cycle, meaning that during the scan, the first and second acquisition periods are determined within each cardiac cycle of the patient. They can also be determined within discontinuous cardiac cycles. For example, the first and second acquisition periods can be determined within each cardiac cycle, or they can be determined intermittently within the cardiac cycle. Intermittent acquisition includes both regular and irregular intervals.

[0058] After the first acquisition period and the second acquisition period are determined, the MRI scanning device acquires first K-space data during the first acquisition period and second K-space data during the second acquisition period. The first K-space data is used to generate the first image, and the second K-space data is used to generate the second image. Therefore, the MRI scanning system can simultaneously acquire the first K-space data and the second K-space data during a single scan, eliminating the need for separate acquisitions in two MRI scans, thereby simultaneously generating the first image and the second image.

[0059] It should be further explained that, within the same cardiac cycle, it is necessary to determine the period of time when the heart beats the lightest and slowest for collecting K-space data. Therefore, the first acquisition period and the second acquisition period need to be set as far as possible within this relatively slow time range.

[0060] In step S230 , a first image is generated based on the first K-space data, and a second image is generated based on the second K-space data.

[0061] Specifically, after completing the acquisition of the first K-space data and the second K-space data, the magnetic resonance scanning system reconstructs the first K-space data and the second K-space data to generate a first image and a second image.

[0062] Through the above steps, the MRI scanning device acquires both the first K-space data and the second K-space data during the same cardiac cycle of the patient. Therefore, the MRI scanning system can simultaneously acquire the first K-space data and the second K-space data during a single scan, eliminating the need for separate acquisitions through two MRI scans. This allows the first image and the second image to be generated simultaneously. Compared to the prior art, where a single MRI scan can only acquire one type of K-space data and generate one MRI image, the MRI imaging method provided in this embodiment reduces the number of MRI scans and achieves a more efficient image generation.

[0063] The first image is a delayed cardiac enhancement image, and the second image is a coronary artery image (or the first image is a coronary artery image, and the second image is a delayed cardiac enhancement image).

[0064] Specifically, in this embodiment, the magnetic resonance imaging method is used to generate a cardiac delayed enhancement image and a coronary artery image in a single magnetic resonance scan. Cardiac delayed enhancement imaging and coronary artery imaging share certain commonalities. For example, both imaging methods require applying an inversion recovery preparation pulse after a certain delay time from the ECG R wave, and then starting to acquire the corresponding k-space data a certain time after the inversion recovery preparation pulse. Therefore, when cardiac delayed enhancement imaging and coronary artery imaging are performed simultaneously in a single magnetic resonance scan, a single inversion recovery preparation pulse can be applied after a certain delay time from the ECG R wave, and then the required k-space data for each can be acquired after the inversion recovery preparation pulse. It should also be noted that when the first image and the second image are, respectively, a cardiac delayed enhancement image and a coronary artery image, it is also necessary to suppress normal myocardial signals and enhance abnormal myocardial signals during relatively stable periods within the cardiac cycle. Specifically, for cardiac delayed enhancement imaging, a fast gradient echo imaging sequence is used, utilizing a non-selective inversion recovery preparation pulse to selectively suppress normal myocardial signals and highlight enhanced infarcted myocardial tissue. For coronary artery images, the myocardial signal is suppressed by setting an appropriate inversion recovery time through the inversion recovery preparation pulse, the bright blood coronary signal is displayed using a common gradient echo sequence, and the fat suppression module is used to suppress fat or the water-fat separation technology is used to remove the influence of fat.

[0065] In some embodiments, determining the first acquisition period and the second acquisition period within the same cardiac cycle in step S220 specifically includes:

[0066] Determine the start time of the first collection period, and determine the end time of the first collection period according to the start time of the first collection period;

[0067] A start time of the second acquisition period is determined, and an end time of the second acquisition period is determined according to the start time of the second acquisition period.

[0068] Specifically, the start times of the first and second acquisition periods must be determined. During the scan, a rapid imaging sequence is applied at the start of each acquisition period, and the corresponding K-space data is acquired after the rapid imaging sequence is applied. The end times of the first and second acquisition periods are determined based on their respective start times, the parameters of the rapid imaging sequence, and a relatively stable time period within the cardiac cycle. While meeting objective imaging requirements, the start and end times of the two acquisition periods should be set as close as possible to a period of relatively still heart activity within the cardiac cycle.

[0069] Reference Figure 3 In a specific embodiment, there exists a same collection period between the first collection period and the second collection period;

[0070] There is the same k-space data between the first k-space data and the second k-space data.

[0071] Acquiring first K-space data in the first acquisition period and acquiring second K-space data in the second acquisition period in step S220 includes:

[0072] The same K-space data is acquired within the same acquisition period.

[0073] Specifically, in some cases, the first acquisition period as a whole precedes the second acquisition period, but the start time of the second acquisition period is set before the end time of the first acquisition period (or the second acquisition period as a whole precedes the first acquisition period, but the start time of the first acquisition period is set before the end time of the second acquisition period). Therefore, the first acquisition period and the second acquisition period have some common acquisition periods, and the K-space data acquired in these common acquisition periods are shareable data, which can be used as both the first K-space data and the second K-space data. Therefore, the first K-space data and the second K-space data have some common K-space data.

[0074] Furthermore, during the k-space data acquisition process, different tags are added to the k-space data collected in different time periods to distinguish them. Specifically, the k-space data collected in the first acquisition period is added with a tag related to the first acquisition period, and the k-space data collected in the second acquisition period is added with a tag related to the second acquisition period. Then, from the total acquired data, the first k-space data and the second k-space data are filtered out based on the differences in the above data tags. It should be further explained that the k-space data collected in the same acquisition period between the first acquisition period and the second acquisition period are simultaneously added with both data tags. This tagging can confirm that this portion of k-space data is shared data and can be used for both the first and second images.

[0075] In some embodiments, the plurality of consecutive cardiac cycles include first cardiac cycles and second cardiac cycles alternating with each other;

[0076] The step of determining the first acquisition period and the second acquisition period within the same cardiac cycle specifically includes:

[0077] A first acquisition period and a second acquisition period are determined in each first cardiac cycle, and a third acquisition period is determined in the second cardiac cycle; wherein the third acquisition period is used to acquire third K-space data.

[0078] Specifically, in this embodiment, a continuous cardiac cycle is composed of a first cardiac cycle and a second cardiac cycle that alternate with each other. A first acquisition period and a second acquisition period are determined within the first cardiac cycle. That is, the acquisition period is determined intermittently within the cardiac cycle, rather than continuously within the cardiac cycle. Correspondingly, third K-space data is acquired within the second cardiac cycle, and the third K-space data can be used to generate a reference image. In other words, a rapid imaging sequence and a reference imaging sequence are applied alternately within a continuous cardiac cycle. The advantage of this technical solution is that, after applying the reference imaging sequence, the start time of acquisition of the K-space data of the delayed enhancement cardiac image is relatively relaxed, thereby enabling it to be better determined during a period of relatively slow cardiac movement.

[0079] Accordingly, in some other embodiments, the step of determining the first acquisition period and the second acquisition period within the same cardiac cycle specifically includes:

[0080] A first acquisition period and a second acquisition period are determined in each cardiac cycle.

[0081] Specifically in this embodiment, the first acquisition segment and the second acquisition segment are determined in each cardiac cycle in the magnetic resonance scanning period, so the acquisition period is determined in a continuous cardiac cycle, so that the first K-space data and the second K-space data are acquired in each cardiac cycle.

[0082] In some embodiments, the step of determining the first acquisition period and the second acquisition period within the same cardiac cycle specifically includes:

[0083] Applying an inversion recovery preparation pulse during the cardiac cycle;

[0084] A first acquisition period and a second acquisition period are determined after the inversion recovery preparation pulse; wherein the first acquisition period and the inversion recovery preparation pulse have a first time interval, and the second acquisition period and the inversion recovery preparation pulse have a second time interval.

[0085] Specifically, in an actual MRI scan sequence, an inversion recovery preparation pulse is applied after a certain delay time for each ECG R wave, and then K-space data acquisition begins a certain time after the inversion recovery preparation pulse. Therefore, in this embodiment, an inversion recovery preparation pulse is applied at the initial stage of the cardiac cycle, and then a first acquisition period and a second acquisition period are determined after the inversion recovery preparation pulse. In other words, the first K-space data acquisition begins after a first time interval has passed since the inversion recovery preparation pulse was applied, and the second K-space data acquisition begins after a second time interval has passed. Furthermore, the first and second time intervals can be set within the scan sequence based on the patient's myocardial signal.

[0086] In one optional embodiment, the step of determining the first acquisition period and the second acquisition period within the same cardiac cycle specifically includes:

[0087] Determine periods of relative cardiac stillness within the cardiac cycle;

[0088] The first acquisition period and the second acquisition period are determined during a period in the cardiac cycle when the heart is relatively still.

[0089] Specifically, in this embodiment, during magnetic resonance imaging (MRI), respiratory motion can be detected using diaphragm navigation technology to determine periods of stable respiratory signals. ECG signals can then be used to detect cardiac cycles. Cardiac cine imaging or prior statistical laws can be used to determine periods of relative cardiac stillness within the cardiac cycle, and K-space data can be collected during these periods. Diaphragm navigation utilizes a cylindrical excitation pulse to determine the position of the diaphragm during scanning, collecting signals during intervals where the diaphragm position is relatively fixed, thereby freezing respiratory motion. Collecting corresponding K-space data during periods of relative cardiac stillness within the cardiac cycle can reduce or avoid image artifacts, and the patient can breathe freely.

[0090] The present embodiment is described and illustrated below through preferred embodiments.

[0091] In a preferred embodiment, a magnetic resonance imaging method is provided, which fully utilizes the time within the cardiac cycle and simultaneously realizes magnetic resonance coronary imaging and delayed enhancement imaging in one sequence without increasing additional scanning time.

[0092] The magnetic resonance imaging method of this preferred embodiment performs magnetic resonance coronary imaging by setting the same or different TI values while performing delayed enhancement cardiac imaging. Specifically, the magnetic resonance scanning method includes:

[0093] Step A: Apply IR after a certain delay time of each ECG R wave. IR stands for inversion recovery preparation pulse.

[0094] Step B: Use the inversion recovery time TI1 to acquire K-space data K1 for delayed enhancement imaging, and use the inversion recovery time TI2 to acquire another K-space data K2 for coronary artery imaging.

[0095] Specifically, a rapid imaging sequence IMG is applied at TI1 after IR and used to reconstruct the K-space data of the delayed enhancement image. An appropriate TI2 time is set after IR to suppress the myocardial signal, and a rapid imaging sequence IMG is applied to acquire the K-space data for the coronary image. A normal gradient echo sequence is used to display the bright blood coronary signal, and a fat suppression module is used to suppress fat or water-fat separation technology is used to remove the influence of fat. Then, in the next cardiac cycle, a reference imaging sequence Ref may be applied or not. Here, IMG represents a rapid imaging sequence, and Ref is a reference imaging sequence in phase sensitive inversion recovery (PSIR).

[0096] The K-space data K1 and the K-space data K2 may be two completely different K-space data, or may share a portion of the K-space data.

[0097] Figure 4 This is a magnetic resonance imaging timing diagram in this preferred embodiment. Figure 4 In one specific embodiment, the inversion recovery time TI1 is less than the inversion recovery time TI2, and Ref in delayed enhancement imaging is acquired simultaneously (Ref and K-space data K1 and K2 are acquired alternately in different cardiac cycles), and K1 and K2 are two independent K spaces.

[0098] Specifically, the acquisition start times of the k-space data K1 and K-space data K2 are determined by setting inversion recovery times TI1 and TI2, respectively, after the inversion recovery preparation pulse IR. The acquisition start time of the k-space data K2 is equal to or later than the acquisition end time of the k-space data K1. That is, acquisition of the k-space data K2 begins only after the acquisition of the k-space data K1 is complete. Therefore, the k-space data K1 and K2 are completely independent data.

[0099] Figure 5 This is another magnetic resonance imaging timing diagram in this preferred embodiment. Figure 5 In another specific embodiment, the inversion recovery time TI1 is less than the inversion recovery time TI2, and Ref is acquired simultaneously for delayed enhancement imaging (Ref and K-space data K1 and K2 are acquired alternately during different cardiac cycles), with K1 and K2 sharing a portion of data. Specifically, shared data means that the acquired data is populated into both K1 and K2 space. The K1 space data is then discrete Fourier transformed to generate a delayed enhancement image, and the K2 space data is discrete Fourier transformed to generate a coronary artery image.

[0100] Specifically, the acquisition start time of k-space data K1 and the acquisition start time of k-space data K2 are determined by setting inversion recovery times TI1 and TI2, respectively, after the inversion recovery preparation pulse IR. The acquisition periods of k-space data K1 and k-space data K2 partially overlap, i.e., the acquisition start time of k-space data K1 is the earliest, while the acquisition end time of k-space data K2 is the latest. However, the acquisition start time of k-space data K2 is earlier than the acquisition end time of k-space data K1. Therefore, the k-space data acquired during these overlapping acquisition periods is shared data and can be used as both k-space data K1 and k-space data K2.

[0101] In some other specific embodiments, the inversion recovery time TI1 may be greater than the inversion recovery time TI2, that is, the K2 spatial data is collected first, and then the K1 spatial data is collected.

[0102] Figure 6 This is another magnetic resonance imaging timing diagram in this preferred embodiment. Figure 6 In another specific embodiment, the navigation technology Nav is used during the magnetic resonance scanning process to monitor respiratory movement, and at the same time, Ref images are not collected (i.e., K1 spatial data and K2 spatial data are collected during continuous cardiac cycles), and 3D whole-heart free-breathing delayed enhancement imaging and coronary artery imaging are performed.

[0103] This embodiment also provides a magnetic resonance imaging device for implementing the above-mentioned embodiments and preferred embodiments. Details already described will not be repeated. The terms "module," "unit," "subunit," etc., used below, may refer to a combination of software and / or hardware that implements a predetermined function. Although the devices described in the following embodiments are preferably implemented using software, implementation using hardware, or a combination of software and hardware, is also possible and contemplated.

[0104] Figure 7 FIG. 1 is a block diagram of the structure of the magnetic resonance imaging apparatus of this embodiment. Figure 7 As shown, the device includes:

[0105] An information acquisition module 710 is configured to acquire a myocardial signal of a scanned patient, where the myocardial signal includes a plurality of consecutive cardiac cycles;

[0106] The data acquisition module 720 is configured to determine a first acquisition period and a second acquisition period within the same cardiac cycle, acquire first K-space data of a region of interest of the scanned object within the first acquisition period, and acquire second K-space data of the region of interest of the scanned object within the second acquisition period;

[0107] The image generating module 730 is configured to generate a first image based on the first K-space data and a second image based on the second K-space data.

[0108] It should be noted that the above modules can be functional modules or program modules, and can be implemented through software or hardware. For modules implemented through hardware, the above modules can be located in the same processor; or the above modules can be located in different processors in any combination.

[0109] This embodiment further provides a magnetic resonance imaging device, comprising a memory and a processor, wherein the memory stores a computer program, and the processor is configured to run the computer program to execute the steps of any one of the above method embodiments.

[0110] Optionally, the magnetic resonance imaging device may further include a transmission device and an input / output device, wherein the transmission device is connected to the processor, and the input / output device is connected to the processor.

[0111] Optionally, in this embodiment, the processor may be configured to execute the following steps through a computer program:

[0112] S1, acquiring a myocardial signal of a scanned patient, where the myocardial signal includes multiple continuous cardiac cycles.

[0113] S2, determining a first acquisition period and a second acquisition period in the same cardiac cycle, acquiring first K-space data of a region of interest of the scanned object in the first acquisition period, and acquiring second K-space data of the region of interest of the scanned object in the second acquisition period.

[0114] S3 , generating a first image based on the first K-space data, and generating a second image based on the second K-space data.

[0115] It should be noted that, for specific examples in this embodiment, reference may be made to the examples described in the above embodiments and optional implementation modes, and will not be repeated in this embodiment.

[0116] In addition, in conjunction with the magnetic resonance imaging method provided in the above embodiments, a storage medium may be provided in this embodiment to implement the method. The storage medium stores a computer program that, when executed by a processor, implements any one of the magnetic resonance imaging methods in the above embodiments.

[0117] It should be noted that the user information (including but not limited to user device information, user personal information, etc.) and data (including but not limited to data used for analysis, stored data, displayed data, etc.) involved in this application are all information and data authorized by the user or fully authorized by all parties.

[0118] It should be understood that the specific embodiments described herein are only used to explain this application and are not used to limit it. Based on the embodiments provided in this application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of this application.

[0119] Obviously, the accompanying drawings are merely examples or embodiments of the present application. A person skilled in the art can also apply the present application to other similar situations based on these drawings without inventive effort. Furthermore, it is understandable that, although the work involved in this development process may be complex and lengthy, certain design, manufacturing, or production changes based on the technical content disclosed in this application are merely routine technical means for a person skilled in the art and should not be considered to constitute a deficiency in the disclosure of the present application.

[0120] The term "embodiment" as used in this application refers to specific features, structures, or characteristics described in conjunction with the embodiment that can be included in at least one embodiment of this application. The appearance of this phrase in various places in the specification does not necessarily mean that the embodiment is the same, nor does it mean that it is mutually exclusive with other embodiments and is independent or optional. It is understood, either explicitly or implicitly, by those skilled in the art that the embodiments described in this application can be combined with other embodiments when there is no conflict.

[0121] The above-described embodiments merely represent several implementation methods of the present application. While the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of patent protection. It should be noted that a person of ordinary skill in the art may make various modifications and improvements without departing from the spirit of the present application, and these modifications and improvements fall within the scope of protection of the present application. Therefore, the scope of protection of the present application shall be determined by the appended claims.

Claims

1. A magnetic resonance imaging method, characterized in that: The method is used to generate a first image and a second image in a single magnetic resonance scan; The method comprises: Acquiring a myocardial signal of a scanned patient, wherein the myocardial signal includes a plurality of continuous cardiac cycles; Determining a first acquisition period and a second acquisition period within the same cardiac cycle, acquiring first K-space data of a region of interest of the scanned object within the first acquisition period, and acquiring second K-space data of the region of interest of the scanned object within the second acquisition period; The first image is generated based on the first K-space data, and the second image is generated based on the second K-space data; the first image and the second image respectively correspond to different magnetic resonance images.

2. The magnetic resonance imaging method according to claim 1, wherein Determining the first acquisition period and the second acquisition period within the same cardiac cycle includes: Determining a start time of the first acquisition period, and determining an end time of the first acquisition period according to the start time of the first acquisition period; A start time of the second acquisition period is determined, and an end time of the second acquisition period is determined according to the start time of the second acquisition period.

3. The magnetic resonance imaging method according to claim 2, wherein: There is a common collection period between the first collection period and the second collection period; The first K-space data and the second K-space data have the same K-space data. The acquiring of first K-space data in the first acquisition period and the acquiring of second K-space data in the second acquisition period include: The same K-space data is acquired within the same acquisition period.

4. The magnetic resonance imaging method according to any one of claims 1 to 3, characterized in that: The plurality of consecutive cardiac cycles include a first cardiac cycle and a second cardiac cycle that alternate with each other; Determining the first acquisition period and the second acquisition period within the same cardiac cycle includes: The first acquisition period and the second acquisition period are determined in each of the first cardiac cycles, and a third acquisition period is determined in the second cardiac cycle.

5. The magnetic resonance imaging method according to any one of claims 1 to 3, characterized in that: Determining the first acquisition period and the second acquisition period within the same cardiac cycle includes: The first acquisition period and the second acquisition period are determined in each cardiac cycle.

6. The magnetic resonance imaging method according to any one of claims 1 to 3, characterized in that: Determining the first acquisition period and the second acquisition period within the same cardiac cycle includes: applying an inversion recovery preparation pulse during the cardiac cycle; A first acquisition period and a second acquisition period are determined after the inversion recovery preparation pulse; wherein the first acquisition period and the inversion recovery preparation pulse have a first time interval, and the second acquisition period and the inversion recovery preparation pulse have a second time interval.

7. The magnetic resonance imaging method according to any one of claims 1 to 3, characterized in that: The first image is a delayed enhancement cardiac image, and the second image is a coronary artery image.

8. The magnetic resonance imaging method according to any one of claims 1 to 3, characterized in that: Determining the first acquisition period and the second acquisition period within the same cardiac cycle includes: determining a period of relative cardiac rest within the cardiac cycle; The first acquisition period and the second acquisition period are determined during a period in the cardiac cycle when the heart is relatively still.

9. A magnetic resonance imaging apparatus, characterized in that: The apparatus is configured to generate a first image and a second image in a single magnetic resonance scan; The device comprises: An information acquisition module, configured to acquire a myocardial signal of a scanned patient, wherein the myocardial signal includes a plurality of continuous cardiac cycles; a data acquisition module, configured to determine a first acquisition period and a second acquisition period within the same cardiac cycle, acquire first K-space data of a region of interest of the scanned object within the first acquisition period, and acquire second K-space data of the region of interest of the scanned object within the second acquisition period; The image generation module is configured to generate the first image based on the first K-space data and to generate the second image based on the second K-space data; the first image and the second image respectively correspond to different magnetic resonance images.

10. A magnetic resonance imaging device comprising a memory and a processor, characterized in that: A computer program is stored in the memory, and the processor is configured to run the computer program to perform the magnetic resonance imaging method according to any one of claims 1 to 7.

Images