CN113133756A - 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 present 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: performing three-dimensional radio frequency excitation on a heart region; acquiring four-dimensional magnetic resonance data of a plurality of body layers corresponding to one layer position selection value in each cardiac cycle to obtain four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles, wherein the dimensions of the four-dimensional magnetic resonance data are respectively selected dimension of a layer surface, encoding dimension of a phase, reading dimension and time dimension; segmenting four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles according to time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data respectively corresponding to a plurality of phases in the cardiac cycles; and respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data to obtain a three-dimensional cardiac cine image. By the method and the device, the problem of long imaging time of the three-dimensional cardiac film is solved, and the imaging time of the three-dimensional cardiac film is shortened.
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
The MR Cardiac Cine (CMR) technique uses a cine mode to continuously display a plurality of Cardiac images at different times in a single Cardiac cycle at a single layer, and can directly observe the motion condition of the myocardial wall. The use of multi-layer cine images for their evaluation mainly for the local and global functions of the heart (ejection fraction, stroke volume, myocardial mass, rate of thickening of the systolic phase of the heart wall, etc.) is one of the conventional examination sequences of CMR. The current technology needs to image one layer at a time, and a dynamic film image covering the whole heart can be formed after multiple acquisitions, but the time is long.
Disclosure of Invention
In the 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 a heart region;
acquiring four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value in each cardiac cycle to obtain four-dimensional magnetic resonance data acquired in the cardiac cycles, wherein the dimensions of the four-dimensional magnetic resonance data are a slice selection dimension, a phase encoding dimension, a reading dimension and a time dimension respectively;
segmenting the four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles according to the time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data respectively corresponding to the plurality of cardiac cycles;
and respectively carrying out image reconstruction on each group of the four-dimensional magnetic resonance data to obtain a three-dimensional cardiac cine image.
In some of these embodiments, when acquiring four-dimensional magnetic resonance data, both the slice select dimension and the readout dimension are fully acquired, and down-sampling is performed in the phase encode dimension.
In some of these embodiments, acquiring four-dimensional magnetic resonance data for a plurality of slice 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, acquiring four-dimensional magnetic resonance data of a plurality of body layers corresponding to the current horizon selection value until a preset number of magnetic resonance data lines are acquired or R waves in the next cardiac cycle are detected;
acquiring four-dimensional magnetic resonance data of a plurality of body slices corresponding to a next horizon selection value after detecting the preset time interval of the R wave in a next cardiac cycle until acquiring the preset number of the magnetic resonance data lines or detecting the R wave in the next cardiac cycle;
wherein the magnetic resonance data lines lie in a K-space plane determined by the phase encoding dimension and the readout dimension.
In some of these embodiments, the preset number is determined based on an optimization value for the number of lines of magnetic resonance data acquired over a plurality of cardiac cycles, the optimization value comprising: average or minimum values.
In some of these embodiments, in the case where four-dimensional magnetic resonance data is acquired in each cardiac cycle until an R-wave in the next cardiac cycle is detected, the method further comprises:
intercepting the magnetic resonance data lines acquired in each cardiac cycle to obtain the preset number of the magnetic resonance data lines acquired earlier in each cardiac cycle.
In some of these embodiments, the field of view of the 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, the image reconstruction is performed on each set of the four-dimensional magnetic resonance data, and obtaining a three-dimensional cardiac cine image includes:
estimating a coil sensitivity function for acquiring the four-dimensional magnetic resonance data from the magnetic resonance data of the phase encoding dimension in each set of the four-dimensional magnetic resonance data;
and respectively carrying out parallel imaging on each group of the four-dimensional magnetic resonance data based on the coil sensitivity function to obtain the three-dimensional cardiac cine images.
In some embodiments, when four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value is acquired in each cardiac cycle, sampling is performed by using a preset pseudo-random sampling track; wherein, respectively reconstructing images of each group of the four-dimensional magnetic resonance data to obtain a three-dimensional cardiac cine image comprises:
reconstructing each group of the four-dimensional magnetic resonance data based on the pseudo-random sampling trajectory to obtain a plurality of groups of reconstructed four-dimensional magnetic resonance data;
and respectively carrying out image reconstruction on each group of the reconstructed four-dimensional magnetic resonance data to obtain the three-dimensional cardiac cine images.
In a second aspect, the present application provides a magnetic resonance imaging system, which includes a memory and a processor, wherein the memory stores a computer program, and the processor is configured to execute the computer program to perform the three-dimensional cardiac cine imaging method of the first aspect.
In a third aspect, the present application provides 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 embodiment perform three-dimensional radio frequency excitation on a cardiac region; acquiring four-dimensional magnetic resonance data of a plurality of body layers corresponding to one layer position selection value in each cardiac cycle to obtain four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles, wherein the dimensions of the four-dimensional magnetic resonance data are respectively selected dimension of a layer surface, encoding dimension of a phase, reading dimension and time dimension; segmenting four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles according to time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data respectively corresponding to a plurality of phases in the cardiac cycles; and image reconstruction is respectively carried out on each group of four-dimensional magnetic resonance data to obtain a three-dimensional heart film image, 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 application.
Drawings
These and other features, characteristics of the present application, as well as the functions and methods of operation 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 in an embodiment of the present application.
Fig. 2 is a flow chart of a three-dimensional cardiac cine imaging method of an embodiment of the present application.
Figure 3 is a schematic diagram of a four-dimensional magnetic resonance data segmentation of an embodiment of the present application.
FIG. 4 is a schematic diagram of an ellipse acquisition of an embodiment of the present application.
Figure 5 is a schematic view of a magnetic resonance imaging system of an embodiment of the present application.
Detailed Description
For a clearer understanding of the objects, aspects and advantages of the present application, reference is made to the following description and accompanying drawings. 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 higher level without undue detail in order to avoid obscuring aspects of the application with unnecessary detail. It will be apparent to those of ordinary skill in the art that various changes can be made to the embodiments disclosed herein, and that the general principles defined herein may be applied to other embodiments and applications without departing from the principles and scope of the present 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 present application as claimed.
Unless defined otherwise, technical or scientific terms used herein shall have the same general 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 in this application, the terms "a," "an," "the," and the like do not denote a limitation of quantity, but rather are used in the singular or the plural. The terms "comprises," "comprising," "has," "having," and any variations thereof, as referred to in this application, are intended to cover non-exclusive inclusions; for example, a process, method, and system, article, or apparatus that comprises a list of steps or modules (elements) is not limited to the listed steps or modules, but may include other steps or modules (elements) not listed or inherent to such process, method, article, or apparatus.
Reference to "a plurality" in this application means two or more. In general, the character "/" indicates a relationship in which the objects associated before and after are an "or". The terms "first," "second," "third," and the like in this application are used for distinguishing between similar items and not necessarily for describing a particular sequential or chronological order.
The terms "system," "engine," "unit," "module," and/or "block" referred to herein is a method for distinguishing, by level, different components, elements, parts, components, assemblies, or functions of different levels. These terms may be replaced with other expressions capable of achieving the same purpose. In general, reference herein to a "module," "unit," or "block" refers 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 in the case of implementation 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 software modules may be invokable from other modules/units/blocks or from themselves, and/or may be invoked in response to detected events or interrupts. Software modules/units/blocks configured for execution on a computing device may be provided on a computer-readable storage medium, such as a compact disc, digital video disc, flash drive, magnetic disk, or any other tangible medium, or downloaded as digital (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 partially or wholly on the 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 an 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. Generally, the modules/units/blocks described herein may be combined with other modules/units/blocks or, although they are physically organized or stored, may be divided into sub-modules/sub-units/sub-blocks. The description may apply to the system, the 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 dictates otherwise. In this application, the term "and/or" may include any one or more of the associated listed items or combinations thereof.
The term "image" is used herein to generically 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 in this application 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 in or on a target object. The image may thus indicate the actual position of certain anatomical structures present in or on the body of the target object.
MRI data acquisition is acquired in the fourier transform space of the image. After the acquisition is finished, the image can be obtained by carrying out inverse Fourier transform. The three dimensions of space are generally referred to as a readout dimension (RO), a phase encoding dimension (PE), and a plane selection dimension (SPE), which are also referred to as a readout direction, a phase encoding direction, and a plane selection direction, respectively, and a different encoding scheme is used in each direction.
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, an RO direction, an SPE direction, and a PE direction. An MRI imaging sequence typically acquires one line per shot, this line being along the RO direction. The RO direction acquisition speed is very fast, and the acquisition is full. The problem of three-dimensional acquisition can be simplified into the acquisition problem on a PE-SPE two-dimensional plane, a point on each two-dimensional plane represents an RO line, and each radio frequency excitation acquires one point on the PE-SPE two-dimensional plane. The magnetic resonance acquisition sequence takes approximately three milliseconds per radio frequency excitation + magnetic field gradient encoding + acquisition. Approximately 800 milliseconds per cardiac cycle of a human, about 270 RO lines can be acquired, but since the magnetic resonance data of the heart region is also sparse in the time dimension, each RO line acquired in one cardiac cycle has a different time phase, and the magnetic resonance image cannot be reconstructed directly from the magnetic resonance data.
The present embodiment provides a three-dimensional cardiac cine imaging method, and fig. 2 is a flowchart of the three-dimensional cardiac cine imaging method according to the embodiment of the present application, and as shown in fig. 2, the flowchart includes the following steps:
step S201, performing three-dimensional radio frequency excitation on the heart region.
Step S202, acquiring four-dimensional magnetic resonance data of a plurality of body slices corresponding to one horizon selection value in each cardiac cycle, and obtaining four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles.
Step S203, four-dimensional magnetic resonance data acquired in a plurality of cardiac cycles are segmented according to time dimension, and a plurality of groups of four-dimensional magnetic resonance data respectively corresponding to the plurality of cardiac cycles are obtained.
And step S204, respectively carrying out image reconstruction on each group of four-dimensional magnetic resonance data to obtain a three-dimensional cardiac cine image.
In the above step S202, the four-dimensional data is a data having three dimensions of space + a time 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 area, and the four-dimensional magnetic resonance data of a plurality of body layers corresponding to one layer position selection value is acquired in each cardiac cycle, so that compared with the mode of acquiring the magnetic resonance data of only one body layer in each cardiac cycle in the related art, the acquisition time is shortened by adopting the mode, and the whole three-dimensional cardiac cine imaging time 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 to obtain a plurality of groups of four-dimensional magnetic resonance data respectively corresponding to a plurality of phases in the cardiac cycles, each group of four-dimensional magnetic resonance data can be reconstructed to obtain a three-dimensional cardiac static image of one phase, and the three-dimensional cardiac static images of the plurality of phases are combined into a dynamic image according to the sequence of the phases, namely the three-dimensional cardiac cine image.
Fig. 3 is a schematic diagram of a four-dimensional magnetic resonance data segmentation of an embodiment of the present application, and fig. 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 a cardiac cycle is about 800ms, each rf excitation + magnetic field gradient encoding + acquisition takes about three milliseconds, and about 270 RO lines can be acquired in one cardiac cycle. If the cardiac cycle is divided into 30 segments with R-wave as the base point, each segment is called a time phase (abbreviated as phase). Then the 270 RO lines are filled into the three-dimensional K-space corresponding to each phase, respectively, which acquired 9 RO lines per cardiac cycle. After four-dimensional magnetic resonance data of about 20-30 cardiac cycles are acquired, about 300 RO lines are acquired in each three-dimensional K space, a time-phase three-dimensional cardiac static image can be reconstructed according to the magnetic resonance data in the three-dimensional K space, the time consumed for acquiring the magnetic resonance data is about 18-24 s, the acquisition of all four-dimensional magnetic resonance data required for reconstructing a three-dimensional cardiac cine image can be completed in one breath holding, and the acquisition time is greatly shortened.
In step S202, four-dimensional magnetic resonance data may be acquired based on an electrocardiographic gating technique. In this embodiment, a prospective cardiac gating technique, also called an ecg triggering technique, is mainly used, which is characterized in that after a peak of an ecg R wave is detected, a scan sequence is triggered and started after a delay into the end diastole, and then rf pulse excitation and signal acquisition are performed until the next systole. This ensures that the imaging signal acquisition is concentrated in the mid-to-late diastole, when the heart is relatively still, thus significantly reducing imaging cardiac motion artifacts.
In step S202 of this embodiment, after a preset time interval of R-waves in a current cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of body slices corresponding to a current horizon selection value is acquired until a preset number of magnetic resonance data lines are acquired or R-waves in a next cardiac cycle are detected; after a preset time interval of R-waves in the next cardiac cycle is detected, four-dimensional magnetic resonance data of a plurality of volume slices corresponding to the next horizon selection value is acquired until a preset number of magnetic resonance data lines are acquired or R-waves in the next cardiac cycle are detected, wherein the magnetic resonance data lines lie in a K-space plane determined by the phase encoding dimension and the readout dimension, i.e. RO lines. In the above manner, four-dimensional magnetic resonance data of a plurality of slice layers corresponding to one horizon selection value is acquired in each cardiac cycle, the horizon selection value being a dimension value in a horizon selection dimension, each horizon selection value corresponding to a plurality of slice layers of the cardiac region.
In the above embodiment, the preset number is determined based on an optimized value for the number of lines of magnetic resonance data acquired over a plurality of cardiac cycles, the optimized value comprising: average or minimum values. The respective preset number can be set for different scanning modes (magnetic resonance sequences, acquisition modes, etc.). For example, in the historical three-dimensional cardiac cine imaging, magnetic resonance data acquisition is performed on a cardiac region of a scanned object according to a certain scanning mode, the number of the 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 the R-wave of the next cardiac cycle is acquired directly when the magnetic resonance data is acquired, then: after a preset time interval of R waves in the current cardiac cycle is detected, acquiring four-dimensional magnetic resonance data of a plurality of body layers corresponding to the current horizon selection value until the R waves in the next cardiac cycle are detected; after a preset time interval of detecting R-waves in the next cardiac cycle, four-dimensional magnetic resonance data of a plurality of slice layers corresponding to the next horizon selection value is acquired until R-waves in the next cardiac cycle are detected. Then, since the time length of each cardiac cycle is not exactly the same, which will result in a difference in the number of lines of magnetic resonance data acquired in each cardiac cycle, in this case, the alignment of the number of lines of magnetic resonance data can be achieved by truncating the lines of magnetic resonance data acquired in each cardiac cycle to obtain a preset number of lines of magnetic resonance data acquired earlier in each cardiac cycle.
To further shorten the scan time, down-sampling may be performed in certain dimensions of the four-dimensional magnetic resonance data. In this embodiment, when acquiring four-dimensional magnetic resonance data, full acquisition is performed in both the slice selection dimension and the readout dimension, and down acquisition is performed in the phase encoding dimension. After the phase encoding dimension is acquired, the image can be reconstructed on the phase encoding dimension by using a magnetic resonance imaging technology based on sparse sampling. The magnetic resonance imaging technology based on sparse sampling is an imaging method provided based on an informatics theory, for example, a compressed sensing reconstruction algorithm is a reconstruction method provided based on redundancy sparsity of signal data, and the compressed sensing reconstruction algorithm can reconstruct an original signal with high probability only by acquiring limited and randomly and uniformly distributed data.
In some embodiments, about 60% of the magnetic resonance data can be acquired in the slice encoding direction, so that the non-scanned data in the K space is obtained based on the conjugate symmetry property of the K space data distribution by using the partial fourier imaging technology and the partial K space data scanning filling mode, so as to realize the reconstruction of the magnetic resonance image in the slice encoding direction.
In the compressed sensing reconstruction algorithm in this embodiment, when four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value is acquired in each cardiac cycle, sampling is performed by using a preset pseudorandom sampling trajectory. After the pseudo-random sampling trajectory is adopted to sample the four-dimensional magnetic resonance data and each group of four-dimensional magnetic resonance data is obtained by segmentation, each group of four-dimensional magnetic resonance data can be reconstructed based on the pseudo-random sampling trajectory to obtain a plurality of groups of reconstructed four-dimensional magnetic resonance data; then, image reconstruction is carried out on each group of reconstructed four-dimensional magnetic resonance data to obtain a three-dimensional cardiac cine image.
The pseudo-random sampling trajectory described above may be such that the sampling trajectory of the magnetic resonance data on the PE-SPE two-dimensional plane within each three-dimensional K-space may be elliptical or rectangular. Fig. 4 is a schematic diagram of ellipse acquisition in an embodiment of the present application, and as shown in fig. 4, by using the pseudorandom sampling trajectory sampling, magnetic resonance data is acquired and filled in a three-dimensional K space in rows, and after each row of magnetic resonance data is acquired and filled, the next row of magnetic resonance data is acquired and filled, and the whole scanning trajectory is in an elliptical shape, that is, magnetic resonance data at four corners of the three-dimensional K space is not acquired, so that time consumed for phase encoding is reduced by about 21%, and image resolution and quality of a magnetic resonance image obtained by three-dimensional K space reconstruction based on ellipse acquisition are not significantly reduced.
In order to further increase the magnetic resonance imaging speed, a magnetic resonance imaging technology based on parallel and sparse imaging theories may also be adopted in the present embodiment. The parallel magnetic resonance imaging technology adopts a multi-channel coil to simultaneously receive magnetic resonance signals, and accelerates the magnetic resonance imaging speed by utilizing the difference of spatial sensitivity information (namely coil sensitivity functions) of the multi-channel coil. For example, when performing image reconstruction on each set of four-dimensional magnetic resonance data, the coil sensitivity function for acquiring the four-dimensional magnetic resonance data may be estimated according to the magnetic resonance data of the 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, the down-sampling is generally performed in both the slice selection dimension and the phase encoding dimension, and the parallel magnetic resonance imaging technology is used for imaging. However, after down-sampling a dimension in which to estimate the coil sensitivity function required for parallel magnetic resonance imaging techniques, the field of view (FOV) in this direction needs to be larger than the scanned cardiac region. Therefore, the FOV in the slice selection dimension and the FOV in the phase encoding dimension in the related art are both selected to be sufficiently large. However, a large FOV reduces the spatial resolution, and especially selecting a sufficiently large FOV in the slice selection dimension results in a spatial resolution in the slice selection dimension that is too low to reconstruct a magnetic resonance image. In addition, a large FOV requires the skill of the operator, which is prone to unsuccessful reconstruction, and greatly reduces the robustness of the technique.
For this purpose, in the present exemplary embodiment, the field of view of the magnetic resonance system for acquiring four-dimensional magnetic resonance data in the phase encoding dimension is larger than the cardiac region, and the magnetic resonance system 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, in order to ensure a suitable 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 be able to improve the spatial resolution of images in dimensions such as the slice selection dimension, after reconstructing the three-dimensional cardiac static images corresponding to each set of four-dimensional magnetic resonance images, the image resolution in the slice selection dimension or other spatial dimensions may be super-resolution processed based on various super-resolution imaging techniques.
It should be noted that the steps illustrated in the above-described flow diagrams or in the 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 different than here.
The present embodiments also provide a magnetic resonance imaging system. Figure 5 is a schematic view 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 for the imaging field of view, which typically includes a magnetic resonance housing having a main magnet 101 therein, the main magnet 101 may be formed of superconducting coils for generating a main magnetic field, and in some cases, permanent magnets may be used. The main magnet 101 may be used to generate 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, an imaging subject 150 is carried by the patient couch 106, and as the couch plate moves, the imaging subject 150 is moved into the region 105 where the magnetic field distribution of the main magnetic field is relatively uniform. Generally 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 apparatus) is set to be the same as the axial direction of the gantry of the magnetic resonance imaging system, the length direction of the patient is generally kept consistent with the z direction for imaging, the horizontal plane of the magnetic resonance imaging system is set to be an 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 radio frequency pulse generating unit 116 to generate a radio frequency pulse, and the radio frequency pulse is amplified by the amplifier, passes through the switch control unit 117, and is finally emitted by the body coil 103 or the local coil 104 to perform radio frequency 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 subject 150 according to the excitation, the radio frequency signals may be received by the body coil 103 or the local coil 104, there may be a plurality of radio frequency receiving links, and after the radio frequency signals are sent to the radio frequency receiving unit 118, the radio frequency signals are further sent to the image reconstruction unit 121 for image reconstruction, so as to form a magnetic resonance image.
The magnetic resonance scanner also includes gradient coils 102 that can be used to spatially encode the radio frequency signals in magnetic resonance imaging. The pulse control unit 111 controls the gradient signal generating unit 112 to generate gradient signals, which are generally divided into three mutually orthogonal directions: gradient signals in the x, y and z directions, which are different from each other, are amplified by gradient amplifiers (113, 114, 115) and emitted from the gradient coil 102, thereby generating 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.
The processor 122 may be composed of one or more processors, may include a Central Processing Unit (CPU), or an Application Specific Integrated Circuit (ASIC), or may be configured to implement one or more Integrated circuits of the embodiments of the present Application.
The display unit 123 may be a display provided to a user for displaying an image.
The input/output device 124 may be a keyboard, a mouse, a control box, or other relevant devices, and supports inputting/outputting corresponding data streams.
Among other things, the communication port 126 may enable communication with other components such as: and the external equipment, the image acquisition equipment, the database, the external storage, the image processing workstation and the like are in data communication.
Wherein the communication bus 127 comprises hardware, software, or both, coupling the components of the training device of the beat artifact correction model to each other. By way of example, and not limitation, a bus 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 these. The communication bus 127 may include one or more buses, where appropriate. Although specific buses are described and shown in the embodiments of the application, any suitable buses or interconnects are contemplated by the application.
The processor 122 is configured to execute a computer program stored in the memory 125 to implement the three-dimensional cardiac cine imaging methods of the above-described embodiments.
In addition, in combination with the three-dimensional cardiac cine imaging method provided in the above embodiments, a storage medium may also be provided to implement in the present embodiment. The storage medium having stored thereon a computer program; 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 derived by a person skilled in the art from the examples provided herein without any inventive step, shall fall within the scope of protection of the present application.
It is obvious that the drawings are only examples or embodiments of the present application, and it is obvious to those skilled in the art that the present application can be applied to other similar cases according to the drawings without creative efforts. Moreover, it should be appreciated that in the development of any such actual implementation, as in any engineering or design project, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, which may vary from one implementation to another.
The term "embodiment" is used herein to mean that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the present 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 of other embodiments. It is to be expressly or implicitly understood by one of ordinary skill in the art that the embodiments described in this application may be combined with other embodiments without conflict.
The above-mentioned embodiments only express several embodiments of the present application, and the description thereof is more specific and detailed, but not construed as limiting the scope of the patent protection. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the concept of the present application, which falls within the scope of protection of the present application. Therefore, the protection scope of the present application shall be subject to the appended claims.
Claims (10)
1. A method of three-dimensional cardiac cine imaging comprising:
performing three-dimensional radio frequency excitation on a heart region;
acquiring four-dimensional magnetic resonance data of a plurality of body layers corresponding to one horizon selection value in each cardiac cycle to obtain four-dimensional magnetic resonance data acquired in the cardiac cycles, wherein the dimensions of the four-dimensional magnetic resonance data are a slice selection dimension, a phase encoding dimension, a reading dimension and a time dimension respectively;
segmenting the four-dimensional magnetic resonance data acquired in the plurality of cardiac cycles according to the time dimension to obtain a plurality of groups of four-dimensional magnetic resonance data respectively corresponding to the plurality of cardiac cycles;
and respectively carrying out image reconstruction on each group of the four-dimensional magnetic resonance data to obtain a three-dimensional cardiac cine image.
2. The three-dimensional cardiac cine imaging method of claim 1 wherein during acquisition of four-dimensional magnetic resonance data, both the slice selection dimension and the readout dimension are full acquired and down acquired in the phase encoding dimension.
3. The three-dimensional cardiac cine imaging method of claim 1, wherein acquiring four-dimensional magnetic resonance data of a plurality of slice 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, acquiring four-dimensional magnetic resonance data of a plurality of body layers corresponding to the current horizon selection value until a preset number of magnetic resonance data lines are acquired or R waves in the next cardiac cycle are detected;
acquiring four-dimensional magnetic resonance data of a plurality of body slices corresponding to a next horizon selection value after detecting the preset time interval of the R wave in a next cardiac cycle until acquiring the preset number of the magnetic resonance data lines or detecting the R wave in the next cardiac cycle;
wherein the magnetic resonance data lines lie in a K-space plane determined by the phase encoding dimension and the readout dimension.
4. The three-dimensional cardiac cine imaging method of claim 3, wherein the predetermined number is determined based on an optimization of a number of the lines of magnetic resonance data acquired over a plurality of cardiac cycles, the optimization comprising: average or minimum values.
5. The three-dimensional cardiac cine imaging method of claim 4, wherein when acquiring four-dimensional magnetic resonance data in each cardiac cycle is until an R-wave in a next cardiac cycle is detected, the method further comprises:
intercepting the magnetic resonance data lines acquired in each cardiac cycle to obtain 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 apparatus for acquiring four-dimensional magnetic resonance data in the phase encoding dimension is larger than the cardiac region.
7. The three-dimensional cardiac cine imaging method of claim 6, wherein the respective sets of four-dimensional magnetic resonance data are separately reconstructed to obtain three-dimensional cardiac cine images comprising:
estimating a coil sensitivity function for acquiring the four-dimensional magnetic resonance data from the magnetic resonance data of the phase encoding dimension in each set of the four-dimensional magnetic resonance data;
and respectively carrying out parallel imaging on each group of the four-dimensional magnetic resonance data based on the coil sensitivity function to obtain the three-dimensional cardiac cine images.
8. The three-dimensional cardiac cine imaging method of claim 2, wherein a predetermined pseudo-random sampling trajectory is used for sampling when four-dimensional magnetic resonance data of a plurality of slice layers corresponding to a horizon selection value is acquired in each cardiac cycle; wherein, respectively reconstructing images of each group of the four-dimensional magnetic resonance data to obtain a three-dimensional cardiac cine image comprises:
reconstructing each group of the four-dimensional magnetic resonance data based on the pseudo-random sampling trajectory to obtain a plurality of groups of reconstructed four-dimensional magnetic resonance data;
and respectively carrying out image reconstruction on each group of the reconstructed four-dimensional magnetic resonance data to obtain the three-dimensional cardiac cine images.
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 execute 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 of claims 1 to 8.
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