CN113133756B - Three-dimensional cardiac cine imaging method, magnetic resonance imaging system and storage medium - Google Patents
Three-dimensional cardiac cine imaging method, magnetic resonance imaging system and storage medium Download PDFInfo
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Abstract
The application relates to a three-dimensional cardiac cine imaging method, a magnetic resonance imaging system and a computer readable storage medium, wherein the method comprises the following steps: performing three-dimensional radio frequency excitation on the heart region; four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value are acquired in each cardiac cycle, and four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles are acquired, wherein the dimensions of the four-dimensional magnetic resonance data are layer selection dimensions, phase encoding dimensions, reading dimensions and time dimensions respectively; segmenting four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles according to a time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data corresponding to a plurality of phases in the cardiac cycle respectively; and respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data to obtain three-dimensional heart film images. The application solves the problem of long imaging time of the three-dimensional heart film and shortens the imaging time of the three-dimensional heart film.
Description
Technical Field
The present application relates to the field of magnetic resonance imaging, and in particular to a three-dimensional cardiac cine imaging method, a magnetic resonance imaging system and a computer readable storage medium.
Background
MR heart Cine (CMR) technology uses a cine mode to continuously display a plurality of heart images at different times in a single Cardiac cycle, so that the motion condition of the myocardial wall can be directly observed. The multi-layer film image is mainly used for evaluating the local and global functions (ejection fraction, stroke volume, myocardial quality, heart wall systolic thickening rate and the like) of the heart, and is one of the conventional CMR examination sequences. Current technology requires imaging one layer at a time, and dynamic movie images covering the whole heart can be formed after multiple acquisitions, but the time required is relatively long.
Disclosure of Invention
In this embodiment, a three-dimensional cardiac cine imaging method, a magnetic resonance imaging system, and a computer-readable storage medium are provided to solve the problem of long three-dimensional cardiac cine imaging time in the related art.
In a first aspect, an embodiment of the present application provides a three-dimensional cardiac cine imaging method, including:
performing three-dimensional radio frequency excitation on the heart region;
four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value are acquired in each cardiac cycle, and four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles are obtained, wherein the dimensions of the four-dimensional magnetic resonance data are respectively a layer selection dimension, a phase coding dimension, a reading dimension and a time dimension;
segmenting four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles according to a time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data corresponding to a plurality of periods in the cardiac cycle respectively;
and respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data to obtain three-dimensional heart film images.
In some of these embodiments, both the slice selection dimension and the readout dimension are fully acquired and the phase encoding dimension is downscaled when acquiring the four-dimensional magnetic resonance data.
In some of these embodiments, acquiring four-dimensional magnetic resonance data for a plurality of volume layers corresponding to one horizon selection value during each cardiac cycle includes:
after a preset time interval of R waves in the current cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of body layers corresponding to the current horizon selection value are collected until a preset number of magnetic resonance data lines are collected or R waves in the next cardiac cycle are detected;
after the preset time interval of the R wave in the next cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of body layers corresponding to the next horizon selection value are collected until the preset number of magnetic resonance data lines are collected or the R wave in the next cardiac cycle is detected;
wherein the magnetic resonance data lines lie in a K-space plane defined by the phase encoding dimension and the readout dimension.
In some of these embodiments, the preset number is determined based on an optimized value for the number of magnetic resonance data lines acquired over a plurality of cardiac cycles, the optimized value comprising: average or minimum.
In some of these embodiments, where the acquisition of four-dimensional magnetic resonance data in each cardiac cycle is until an R-wave in the next cardiac cycle is detected, the method further comprises:
and intercepting the magnetic resonance data lines acquired in each cardiac cycle to acquire the preset number of the magnetic resonance data lines acquired earlier in each cardiac cycle.
In some of these embodiments, a field of view of a magnetic resonance apparatus for acquiring four-dimensional magnetic resonance data in the phase encoding dimension is larger than the cardiac region.
In some of these embodiments, image reconstruction is performed on each set of the four-dimensional magnetic resonance data separately, and obtaining the three-dimensional cardiac cine image includes:
estimating a coil sensitivity function for acquiring the four-dimensional magnetic resonance data according to the magnetic resonance data of the phase coding dimension in each group of the four-dimensional magnetic resonance data;
and respectively carrying out parallel imaging on each group of four-dimensional magnetic resonance data based on the coil sensitivity function to obtain the three-dimensional heart film image.
In some embodiments, sampling is performed by using a preset pseudo-random sampling track when four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value are acquired in each cardiac cycle; wherein, respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data, and obtaining three-dimensional heart film images comprises the following steps:
reconstructing each set of four-dimensional magnetic resonance data based on the pseudo-random sampling track to obtain a plurality of sets of reconstructed four-dimensional magnetic resonance data;
and respectively carrying out image reconstruction on each group of reconstructed four-dimensional magnetic resonance data to obtain the three-dimensional heart film image.
In a second aspect, an embodiment of the application provides a magnetic resonance imaging system comprising a memory and a processor, the memory having stored therein a computer program, the processor being arranged to run the computer program to perform the three-dimensional cardiac cine imaging method of the first aspect.
In a third aspect, embodiments of the present application provide a computer readable storage medium having stored thereon computer program instructions which, when executed by a processor, implement the three-dimensional cardiac cine imaging method of the first aspect.
Compared with the related art, the three-dimensional cardiac cine imaging method, the magnetic resonance imaging system and the computer-readable storage medium provided in the present embodiment perform three-dimensional radio frequency excitation on a cardiac region; four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value are acquired in each cardiac cycle, and four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles are acquired, wherein the dimensions of the four-dimensional magnetic resonance data are layer selection dimensions, phase encoding dimensions, reading dimensions and time dimensions respectively; segmenting four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles according to a time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data corresponding to a plurality of phases in the cardiac cycle respectively; and respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data to obtain three-dimensional heart film images, so that the problem of long imaging time of the three-dimensional heart film is solved, and the imaging time of the three-dimensional heart film is shortened.
The details of one or more embodiments of the application are set forth in the accompanying drawings and the description below to provide a more thorough understanding of the other features, objects, and advantages of the application.
Drawings
These and other features, aspects, and advantages of the present application, as well as the methods of operation and functions of the related elements of structure and the combination of parts and economies of manufacture, will become more apparent upon consideration of the following description with reference to the accompanying drawings, all of which form a part of this specification. It is to be understood, however, that the drawings are designed solely for the purposes of illustration and description and are not intended as a definition of the limits of the application. It should be understood that the drawings are not to scale.
In the drawings:
fig. 1 is a schematic diagram of a K-space according to an embodiment of the present application.
Fig. 2 is a flow chart of a three-dimensional cardiac cine imaging method in accordance with an embodiment of the present application.
Figure 3 is a schematic diagram of a four-dimensional magnetic resonance data segment of an embodiment of the present application.
Fig. 4 is a schematic diagram of ellipse acquisition of an embodiment of the present application.
Figure 5 is a schematic diagram of a magnetic resonance imaging system of an embodiment of the present application.
Detailed Description
The present application will be described and illustrated with reference to the accompanying drawings and examples for a clearer understanding of the objects, technical solutions and advantages of the present application. However, it will be apparent to one of ordinary skill in the art that the present application may be practiced without these specific details. In some instances, well known methods, procedures, systems, components, and/or circuits have been described at a high-level so as not to obscure aspects of the present application with unnecessary description. It will be apparent to those having ordinary skill in the art that various changes can be made to the disclosed embodiments of the application and that the general principles defined herein may be applied to other embodiments and applications without departing from the spirit and scope of the application. Thus, the present application is not limited to the embodiments shown, but is to be accorded the widest scope consistent with the scope of the application as claimed.
Unless defined otherwise, technical or scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application. As used herein, the terms "a," "an," "the," "these," and the like are not intended to be limiting in number, but rather are singular or plural. The terms "comprising," "including," "having," and any variations thereof, as used herein, are intended to encompass non-exclusive inclusion; for example, a process, method, and system, article, or apparatus that comprises a list of steps or modules (units) is not limited to the list of steps or modules (units), but may include other steps or modules (units) not listed or inherent to such process, method, article, or apparatus.
The term "plurality" as used herein means two or more. Typically, the character "/" indicates that the associated object is an "or" relationship. The terms "first," "second," "third," and the like, as referred to in this disclosure, merely distinguish similar objects and do not represent a particular ordering for objects.
The terms "system," "engine," "unit," "module," and/or "block" as used herein are intended to refer to a method for distinguishing between different components, elements, parts, components, assemblies, or functions at different levels by level. These terms may be replaced by other expressions which achieve the same purpose. In general, the terms "module," "unit," or "block" used herein refer to a collection of logic or software instructions embodied in hardware or firmware. The "modules," "units," or "blocks" described herein may be implemented as software and/or hardware, and where implemented as software, they may be stored in any type of non-volatile computer-readable storage medium or memory.
In some embodiments, software modules/units/blocks may be compiled and linked into an executable program. It will be appreciated that a software module may be callable from other modules/units/blocks or from itself, and/or may be invoked in response to a detected event or interrupt. The software modules/units/blocks configured to execute on the computing device may be provided on a computer readable storage medium, such as an optical disk, digital video disk, flash drive, magnetic disk, or any other tangible medium, or as a digital download (and may be initially stored in a compressed or installable format that requires installation, decompression, or decryption prior to execution). Such software code may be stored in part or in whole on a memory of the executing computing device and applied in the operation of the computing device. The software instructions may be embedded in firmware, such as EPROM. It will also be appreciated that the hardware modules/units/blocks may be included in connected logic components, such as gates and flip-flops, and/or may be included in programmable units, such as programmable gate arrays or processors. The modules/units/blocks or computing device functions described herein may be implemented as software modules/units/blocks, and may also be represented in hardware or firmware. In general, the modules/units/blocks described herein may be combined with other modules/units/blocks or, although physically organized or stored, may be divided into sub-modules/sub-units/sub-blocks. The description may apply to a system, an engine, or a portion thereof.
It will be understood that when an element, engine, module or block is referred to as being "on," "connected to" or "coupled to" another element, engine, module or block, it can be directly on, connected or coupled to or in communication with the other element, engine, module or block, or intervening elements, engines, modules or blocks may be present unless the context clearly indicates otherwise. In the present application, the term "and/or" may include any one or more of the associated listed items or combinations thereof.
The term "image" in the present application is used to refer to image data (e.g., scan data, projection data) and/or various forms of images, including two-dimensional (2D) images, three-dimensional (3D) images, and the like. The terms "pixel" and "voxel" are used interchangeably herein to refer to an element of an image. In the present application, the terms "region", "position" and "region" may refer to the position of an anatomical structure shown in an image, or to the actual position of an anatomical structure present within or on a target object. The image may thus indicate the actual location of certain anatomical structures present in or on the target object.
MRI data acquisition is performed in the fourier transform space of the image. After acquisition is completed, inverse fourier transform is required to obtain an image. The three dimensions of space, which we generally refer to as the readout dimension (RO), the phase encoding dimension (PE) and the slice selection dimension (SPE), are also referred to as the readout direction, the phase encoding direction and the slice selection direction, respectively, in each of which a different encoding scheme is used.
Fig. 1 is a schematic diagram of a K-space according to an embodiment of the present application, and fig. 1 shows three dimensions (directions) of the K-space in space, namely, RO direction, SPE direction and PE direction. The MRI imaging sequence typically acquires one line per excitation, which is along the RO direction. The RO direction acquisition speed is fast, and is full acquisition. The problem of three-dimensional acquisition can be simplified into an acquisition problem on PE-SPE two-dimensional planes, wherein the point on each two-dimensional plane represents an RO line, and each time the radio frequency excitation acquires a point on the PE-SPE two-dimensional plane. The magnetic resonance acquisition sequence requires approximately three milliseconds per radio frequency excitation + magnetic field gradient encoding + acquisition. About 270 RO-lines can be acquired for one cardiac cycle of a person, but since the magnetic resonance data of the heart region also has sparsity in the time dimension, each RO-line acquired in one cardiac cycle has a different time period phase, and the magnetic resonance image cannot be reconstructed directly from these magnetic resonance data.
The embodiment provides a three-dimensional cardiac cine imaging method, fig. 2 is a flowchart of the three-dimensional cardiac cine imaging method according to the embodiment of the application, as shown in fig. 2, the flowchart includes the following steps:
in step S201, three-dimensional radio frequency excitation is performed on the heart region.
Step S202, four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value are acquired in each cardiac cycle, and the four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles are obtained.
Step S203, segmenting the four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles according to the time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data corresponding to a plurality of periods in the cardiac cycle.
And step S204, respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data to obtain three-dimensional heart film images.
In the above step S202, four dimensions refer to having a spatial three-dimensional+temporal dimension (3d+t), specifically: a slice selection dimension, a phase encoding dimension, a readout dimension, and a time dimension.
Through the steps, the three-dimensional radio frequency excitation is carried out on the heart region, four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value are acquired in each cardiac cycle, and compared with the mode that only one body layer of magnetic resonance data is acquired in each cardiac cycle in the related art, the acquisition time is shortened by adopting the mode, so that the imaging time of the whole three-dimensional heart film is shortened.
After four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles are obtained, the four-dimensional magnetic resonance data are segmented according to the time dimension of the four-dimensional magnetic resonance data, so that a plurality of groups of four-dimensional magnetic resonance data corresponding to a plurality of phases in the cardiac cycle are obtained, each group of four-dimensional magnetic resonance data can be reconstructed to obtain a three-dimensional heart static image of one phase, and the three-dimensional heart static images of the plurality of phases are combined into a dynamic image according to the sequence of the phases, namely the three-dimensional heart movie image.
Figure 3 is a schematic diagram of a four-dimensional magnetic resonance data segment of an embodiment of the present application, and figure 3 shows a three-dimensional K-space corresponding to each phase. Wherein, the x-axis direction of the three-dimensional K space represents the RO direction, the y-axis direction represents the phase encoding direction, and the z-axis direction represents the slice selection direction. Since one cardiac cycle is about 800ms, each radio frequency excitation + magnetic field gradient encoding + acquisition requires about three milliseconds, then about 270 RO lines can be acquired in one cardiac cycle. If the cardiac cycle is divided into 30 segments with the R wave as the time base point, each segment is called a time period phase (abbreviated as a period phase). Then, the 270 RO lines are filled into the three-dimensional K space corresponding to each phase, 9 RO lines are acquired in each cardiac cycle. After four-dimensional magnetic resonance data acquisition of about 20-30 cardiac cycles, about 300 RO lines are acquired in each three-dimensional K space, a three-dimensional heart static image of a time phase can be obtained by reconstruction according to the magnetic resonance data in the three-dimensional K space, the magnetic resonance acquisition time is about 18-24 seconds, and the acquisition of all four-dimensional magnetic resonance data required by reconstructing a three-dimensional heart film image can be completed in one breath hold, and the acquisition time is greatly shortened.
In the above step S202, four-dimensional magnetic resonance data acquisition may be performed based on an electrocardiographic gating technique. In this embodiment, a prospective electrocardiographic gating technique, also called an electrocardiographic triggering technique, is mainly represented by that after the peak of the electrocardiographic R wave is detected, the electrocardiographic R wave enters the end diastole stage through a delay, the scanning sequence is triggered and started, and then the radio frequency pulse excitation and signal acquisition are started until the next systole. In this way, the imaging signal acquisition is ensured to be concentrated in the middle and later stages of diastole, and the heart is relatively stationary, so that imaging heart motion artifacts can be obviously reduced.
In step S202 of the present embodiment, after detecting a preset time interval of R-waves in a current cardiac cycle, four-dimensional magnetic resonance data of multiple body layers corresponding to a current level selection value is collected until a preset number of magnetic resonance data lines are collected or R-waves in a next cardiac cycle are detected; after a preset time interval of the R-wave in the next cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of volume layers corresponding to the next horizon selection value are acquired until a preset number of magnetic resonance data lines are acquired or the R-wave in the next cardiac cycle is detected, wherein the magnetic resonance data lines are located in a K-space plane determined by a phase encoding dimension and a readout dimension, i.e. RO-lines. In this way, four-dimensional magnetic resonance data of a plurality of volume layers corresponding to one horizon selection value is acquired in each cardiac cycle, wherein the horizon selection value refers to one dimension value in a horizon selection dimension, and each horizon selection value corresponds to a plurality of volume layers of a heart region.
In the above embodiment, the preset number is determined based on an optimized value for the number of magnetic resonance data lines acquired in a plurality of cardiac cycles, the optimized value including: average or minimum. Different scanning modes (magnetic resonance sequences, acquisition modes, etc.) can be provided with corresponding preset numbers. For example, in historical three-dimensional cardiac cine imaging, magnetic resonance data is acquired for a cardiac region of a scanned object according to a certain scanning mode, the number of RO lines acquired in each cardiac cycle is counted, an average value of the RO lines acquired in each cardiac cycle is obtained, and the average value is used as a preset number corresponding to the certain scanning mode.
In step S202 of some embodiments, if R-waves of the next cardiac cycle are directly acquired when magnetic resonance data are acquired, namely: after a preset time interval of R waves in the current cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of body layers corresponding to the current horizon selection value are collected until the R waves in the next cardiac cycle are detected; after a preset time interval of detecting the R wave in the next cardiac cycle, four-dimensional magnetic resonance data of a plurality of body layers corresponding to the next horizon selection value are acquired until the R wave in the next cardiac cycle is detected. In this case, the alignment of the number of magnetic resonance data lines may be achieved by intercepting the magnetic resonance data lines acquired in each cardiac cycle to obtain a preset number of magnetic resonance data lines acquired earlier in each cardiac cycle, since the time length of each cardiac cycle is not exactly the same, which would result in a difference in the number of magnetic resonance data lines acquired in each cardiac cycle.
To further shorten the scan time, downsampling may be performed in certain dimensions of the four-dimensional magnetic resonance data. In this embodiment, when four-dimensional magnetic resonance data is acquired, full acquisition is performed on both the slice selection dimension and the readout dimension, and downsampling is performed on the phase encoding dimension. After downsampling in the phase encoding dimension, a sparse sampling-based magnetic resonance imaging technique may be employed in the phase encoding dimension to reconstruct the image. The magnetic resonance imaging technology based on sparse sampling is an imaging method based on an informatics theory, for example, a compressed sensing reconstruction algorithm is a reconstruction method based on redundancy sparsity of signal data, and the compressed sensing reconstruction algorithm only needs to collect limited data which are randomly and uniformly distributed, so that an original signal can be reconstructed with high probability.
In some embodiments, about 60% of the magnetic resonance data can be acquired in the slice encoding direction, so that a partial fourier imaging technique is used, a partial K-space data scan filling mode is adopted, and unscanned data in K-space are obtained based on conjugate symmetry properties of K-space data distribution, so as to realize reconstruction of a magnetic resonance image in the slice encoding direction.
The compressed sensing reconstruction algorithm in this embodiment adopts a preset pseudo-random sampling track to sample when four-dimensional magnetic resonance data of multiple body layers corresponding to one horizon selection value is acquired in each cardiac cycle. After sampling four-dimensional magnetic resonance data by adopting a pseudo-random sampling track and obtaining each group of four-dimensional magnetic resonance data by segmentation, reconstructing each group of four-dimensional magnetic resonance data based on the pseudo-random sampling track to obtain a plurality of groups of reconstructed four-dimensional magnetic resonance data; and then, respectively carrying out image reconstruction on each set of reconstructed four-dimensional magnetic resonance data to obtain three-dimensional heart film images.
The pseudo-random sampling trajectories described above may enable sampling trajectories of magnetic resonance data on a PE-SPE two-dimensional plane within each three-dimensional K-space to be elliptical or rectangular. Fig. 4 is a schematic diagram of ellipse acquisition according to an embodiment of the present application, as shown in fig. 4, by adopting the pseudo-random sampling trajectory sampling, acquiring and filling magnetic resonance data in a three-dimensional K space according to rows, after each row of magnetic resonance data is acquired and filled, acquiring and filling the next row of magnetic resonance data, where the whole scanning trajectory is in an ellipse shape, that is, does not acquire magnetic resonance data at four corners of the three-dimensional K space, the time required for phase encoding is reduced by about 21%, and the image resolution and quality of a magnetic resonance image obtained by reconstructing the three-dimensional K space based on the ellipse acquisition are not significantly reduced.
In order to further increase the magnetic resonance imaging speed, a magnetic resonance imaging technique based on parallel and sparse imaging theory may also be used in the present embodiment. The parallel magnetic resonance imaging technology adopts a multichannel coil to simultaneously receive magnetic resonance signals, and the magnetic resonance imaging speed is accelerated by utilizing the difference of the spatial sensitivity information (namely coil sensitivity function) of the multichannel coil. For example, when image reconstruction is performed on each set of four-dimensional magnetic resonance data in the above embodiment, a coil sensitivity function for acquiring the four-dimensional magnetic resonance data may be estimated from magnetic resonance data of a phase encoding dimension in each set of four-dimensional magnetic resonance data; and respectively carrying out parallel imaging on each group of four-dimensional magnetic resonance data based on the coil sensitivity function to obtain a three-dimensional heart film image.
In order to improve the magnetic resonance imaging technology in the related art, downsampling is generally performed in both a layer selection dimension and a phase encoding dimension, and parallel magnetic resonance imaging technology is adopted for imaging. However, after downsampling for a dimension, the field of view (FOV) in this direction needs to be larger than the region of the heart being scanned in order to estimate the coil sensitivity functions required for parallel magnetic resonance imaging techniques in that dimension. Thus, both the FOV of the layer selection dimension and the FOV of the phase encoding dimension in the related art are selected to be sufficiently large. However, a large FOV may reduce the spatial resolution, especially selecting a sufficiently large FOV in the slice selection dimension will result in a spatial resolution of the slice selection dimension that is too low to reconstruct the magnetic resonance image. In addition, the large FOV has requirements on the proficiency of operators, the situation that reconstruction is unsuccessful is easy to occur, and the technical robustness is greatly reduced.
For this reason, in the present embodiment, the magnetic resonance apparatus for acquiring four-dimensional magnetic resonance data has a field of view larger than the heart region in the phase encoding dimension, and the magnetic resonance apparatus for acquiring four-dimensional magnetic resonance data selects a small FOV in the slice selection dimension, which is not larger than the field of view in the phase encoding dimension, to ensure a proper spatial resolution in the slice selection dimension. In this embodiment, the direction of the slice-encoding dimension is along the direction of the long axis of the heart.
In order to improve the spatial resolution of images in dimensions such as a slice selection dimension, after reconstructing three-dimensional cardiac static images corresponding to each set of four-dimensional magnetic resonance images, super-resolution processing may be performed on the image resolution of the slice selection dimension or other spatial dimensions based on various super-resolution imaging techniques.
It should be noted that the steps illustrated in the above-described flow or flow diagrams of the figures may be performed in a computer system, such as a set of computer-executable instructions, and that, although a logical order is illustrated in the flow diagrams, in some cases, the steps illustrated or described may be performed in an order other than that illustrated herein.
The embodiment also provides a magnetic resonance imaging system. Figure 5 is a schematic diagram of a magnetic resonance imaging system of an embodiment of the present application. As shown in fig. 5, the magnetic resonance imaging system includes: a scanner and a computer, wherein the computer comprises a memory 125, a processor 122 and a computer program stored on the memory 125 and executable on the processor 122.
The scanner has a bore with an imaging field of view, which typically includes a magnetic resonance gantry within which is a main magnet 101, which main magnet 101 may be formed of superconducting coils for generating a main magnetic field, and in some cases permanent magnets may also be employed. The main magnet 101 may be used to produce a main magnetic field strength of 0.2 tesla, 0.5 tesla, 1.0 tesla, 1.5 tesla, 3.0 tesla, or higher. In magnetic resonance imaging, the imaging subject 150 is carried by the patient table 106, and the imaging subject 150 is moved into the region 105 where the main magnetic field is more uniformly distributed as the table moves. Typically for a magnetic resonance imaging system, as shown in fig. 5, the z-direction of the spatial coordinate system (i.e. the coordinate system of the device) is set to be the same as the axial direction of the gantry of the magnetic resonance imaging system, the patient's length direction is usually imaged in line with the z-direction, the horizontal plane of the magnetic resonance imaging system is set to be the xz-plane, the x-direction is perpendicular to the z-direction, and the y-direction is perpendicular to both the x-and z-directions.
In magnetic resonance imaging, the pulse control unit 111 controls the rf pulse generation unit 116 to generate rf pulses, and the rf pulses are amplified by the amplifier, passed through the switch control unit 117, and finally emitted by the body coil 103 or the local coil 104 to perform rf excitation on the imaging object 150. The imaging subject 150 generates corresponding radio frequency signals from resonance upon radio frequency excitation. When receiving the radio frequency signals generated by the imaging object 150 according to excitation, the body coil 103 or the local coil 104 can receive the radio frequency signals, and a plurality of radio frequency receiving links can be provided, and the radio frequency signals are further sent to the image reconstruction unit 121 for image reconstruction after being sent to the radio frequency receiving unit 118, so as to form a magnetic resonance image.
The magnetic resonance scanner also includes gradient coils 102 that may be used to spatially encode the radio frequency signals during magnetic resonance imaging. The pulse control unit 111 controls the gradient signal generating unit 112 to generate a gradient signal, which is generally divided into three mutually orthogonal direction signals: gradient signals in the x direction, the y direction and the z direction are amplified by gradient amplifiers (113, 114, 115), and then emitted by the gradient coil 102, so as to generate a gradient magnetic field in the region 105.
The pulse control unit 111, the image reconstruction unit 121, the processor 122, the display unit 123, the input/output device 124, the memory 125 and the communication port 126 can perform data transmission through the communication bus 127, so as to realize the control of the magnetic resonance imaging process.
Processor 122 may be comprised of one or more processors, may include a Central Processing Unit (CPU), or an application specific integrated circuit (Application Specific Integrated Circuit, ASIC), or may be configured to implement one or more integrated circuits of embodiments of the present application.
Among them, the display unit 123 may be a display provided to a user to display an image.
The input/output device 124 may be a keyboard, a mouse, a control box, etc., and supports input/output of corresponding data streams.
Memory 125 may include, among other things, mass storage for data or instructions. By way of example, and not limitation, memory 125 may include a Hard Disk Drive (HDD), floppy Disk Drive, flash memory, optical Disk, magneto-optical Disk, magnetic tape, or universal serial bus (Universal Serial Bus, USB) Drive, or a combination of two or more of the foregoing. The memory 125 may include removable or non-removable (or fixed) media, where appropriate. The memory 125 may be internal or external to the data processing apparatus, where appropriate. In a particular embodiment, the memory 125 is a non-volatile solid-state memory. In particular embodiments, memory 125 includes Read Only Memory (ROM). The ROM may be mask programmed ROM, programmable ROM (PROM), erasable PROM (EPROM), electrically Erasable PROM (EEPROM), electrically rewritable ROM (EAROM), or flash memory, or a combination of two or more of these, where appropriate. Memory 125 may be used to store various data files that need to be processed and/or used for communication, as well as possible program instructions for execution by processor 122. When the processor 122 executes a stored, specified program in the memory 125, the processor 122 may perform a training method of the beat artifact correction model proposed by the present application, and/or a beat artifact correction method.
Among other things, the communication port 126 may enable, among other components, for example: and the external equipment, the image acquisition equipment, the database, the external storage, the image processing workstation and the like are used for data communication.
Wherein the communication bus 127 comprises hardware, software, or both, couples the components of the training device of the beat artifact correction model to each other. By way of example, and not limitation, the buses may include an Accelerated Graphics Port (AGP) or other graphics bus, an Enhanced Industry Standard Architecture (EISA) bus, a Front Side Bus (FSB), a HyperTransport (HT) interconnect, an Industry Standard Architecture (ISA) bus, an infiniband interconnect, a Low Pin Count (LPC) bus, a memory bus, a micro channel architecture (MCa) bus, a Peripheral Component Interconnect (PCI) bus, a PCI-Express (PCI-X) bus, a Serial Advanced Technology Attachment (SATA) bus, a video electronics standards association local (VLB) bus, or other suitable bus, or a combination of two or more of the above. Communication bus 127 may include one or more buses, where appropriate. Although embodiments of the application have been described and illustrated with respect to a particular bus, the application contemplates any suitable bus or interconnect.
The processor 122 is configured to run a computer program stored in the memory 125 to implement the three-dimensional cardiac cine imaging method of the above-described embodiment.
In addition, in combination with the three-dimensional cardiac cine imaging method provided in the above embodiment, a storage medium may be provided in the present embodiment. The storage medium has a computer program stored thereon; the computer program, when executed by a processor, implements any of the three-dimensional cardiac cine imaging methods of the above embodiments.
It should be understood that the specific embodiments described herein are merely illustrative of this application and are not intended to be limiting. All other embodiments, which can be made by one of ordinary skill in the art without undue burden from the present disclosure, are within the scope of the present disclosure in accordance with the embodiments provided herein.
It is to be understood that the drawings are merely illustrative of some embodiments of the present application and that it is possible for those skilled in the art to adapt the present application to other similar situations without the need for inventive work. In addition, it should be appreciated that while the development effort might be complex and lengthy, it will nevertheless be a routine undertaking of design, fabrication, or manufacture for those of ordinary skill having the benefit of this disclosure, and further having the benefit of this disclosure.
The term "embodiment" in this disclosure means that a particular feature, structure, or characteristic described in connection with the embodiment may be included in at least one embodiment of the application. The appearances of such phrases in various places in the specification are not necessarily all referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive. It will be clear or implicitly understood by those of ordinary skill in the art that the embodiments described in the present application can be combined with other embodiments without conflict.
The above examples merely represent a few embodiments of the present application, which are described in more detail and are not to be construed as limiting the scope of the patent claims. It should be noted that it will be apparent to those skilled in the art that several variations and modifications can be made without departing from the spirit of the application, which are all within the scope of the application. Accordingly, the scope of the application should be assessed as that of the appended claims.
Claims (10)
1. A three-dimensional cardiac cine imaging method, comprising:
performing three-dimensional radio frequency excitation on the heart region;
four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value are acquired in each cardiac cycle, and four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles are obtained, wherein the dimensions of the four-dimensional magnetic resonance data are respectively a layer selection dimension, a phase coding dimension, a reading dimension and a time dimension; sampling by adopting a preset pseudo-random sampling track when four-dimensional magnetic resonance data of a plurality of body layers corresponding to one layer selection value are acquired in each cardiac cycle;
segmenting four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles according to a time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data corresponding to a plurality of periods in the cardiac cycle respectively;
and respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data to obtain three-dimensional heart film images.
2. The three-dimensional cardiac cine imaging method of claim 1, wherein, when acquiring four-dimensional magnetic resonance data, both slice selection dimensions and readout dimensions are fully acquired and downscaled in the phase encoding dimension.
3. The three-dimensional cardiac cine imaging method of claim 1, wherein acquiring four-dimensional magnetic resonance data for a plurality of volume layers corresponding to one horizon selection value in each cardiac cycle comprises:
after a preset time interval of R waves in the current cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of body layers corresponding to the current horizon selection value are collected until a preset number of magnetic resonance data lines are collected or R waves in the next cardiac cycle are detected;
after the preset time interval of the R wave in the next cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of body layers corresponding to the next horizon selection value are collected until the preset number of magnetic resonance data lines are collected or the R wave in the next cardiac cycle is detected;
wherein the magnetic resonance data lines lie in a K-space plane defined by the phase encoding dimension and the readout dimension.
4. A three-dimensional cardiac cine imaging method according to claim 3, wherein the preset number is determined based on an optimized value for the number of magnetic resonance data lines acquired over a plurality of cardiac cycles, the optimized value comprising: average or minimum.
5. The three-dimensional cardiac cine imaging method of claim 4, wherein in the event that four-dimensional magnetic resonance data is acquired in each cardiac cycle until an R-wave in a next cardiac cycle is detected, the method further comprises:
and intercepting the magnetic resonance data lines acquired in each cardiac cycle to acquire the preset number of the magnetic resonance data lines acquired earlier in each cardiac cycle.
6. The three-dimensional cardiac cine imaging method of claim 2, wherein a field of view of a magnetic resonance device for acquiring four-dimensional magnetic resonance data in the phase encoding dimension is larger than the cardiac region.
7. The method of three-dimensional cardiac cine imaging of claim 6, wherein performing image reconstruction on each set of four-dimensional magnetic resonance data separately, obtaining three-dimensional cardiac cine images comprises:
estimating a coil sensitivity function for acquiring the four-dimensional magnetic resonance data according to the magnetic resonance data of the phase coding dimension in each group of the four-dimensional magnetic resonance data;
and respectively carrying out parallel imaging on each group of four-dimensional magnetic resonance data based on the coil sensitivity function to obtain the three-dimensional heart film image.
8. The three-dimensional cardiac cine imaging method of claim 2, wherein performing image reconstruction on each set of the four-dimensional magnetic resonance data separately, obtaining three-dimensional cardiac cine images comprises:
reconstructing each set of four-dimensional magnetic resonance data based on the pseudo-random sampling track to obtain a plurality of sets of reconstructed four-dimensional magnetic resonance data;
and respectively carrying out image reconstruction on each group of reconstructed four-dimensional magnetic resonance data to obtain the three-dimensional heart film image.
9. A magnetic resonance imaging system comprising a memory and a processor, characterized in that the memory has stored therein a computer program, the processor being arranged to run the computer program to perform the three-dimensional cardiac cine imaging method of any one of claims 1 to 8.
10. A computer readable storage medium having stored thereon computer program instructions, which when executed by a processor, implement the three-dimensional cardiac cine imaging method of any one of claims 1 to 8.
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