CN116125350A - Magnetic resonance image generation method, device, computer equipment and storage medium - Google Patents
Magnetic resonance image generation method, device, computer equipment and storage medium Download PDFInfo
- Publication number
- CN116125350A CN116125350A CN202111348619.8A CN202111348619A CN116125350A CN 116125350 A CN116125350 A CN 116125350A CN 202111348619 A CN202111348619 A CN 202111348619A CN 116125350 A CN116125350 A CN 116125350A
- Authority
- CN
- China
- Prior art keywords
- magnetic resonance
- target
- vector
- detection object
- image
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
Images
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
- G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
Landscapes
- Health & Medical Sciences (AREA)
- Physics & Mathematics (AREA)
- Life Sciences & Earth Sciences (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- General Health & Medical Sciences (AREA)
- Radiology & Medical Imaging (AREA)
- Engineering & Computer Science (AREA)
- High Energy & Nuclear Physics (AREA)
- Signal Processing (AREA)
- Medical Informatics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- General Physics & Mathematics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
The application relates to a magnetic resonance image generation method, a magnetic resonance image generation device, a computer device and a storage medium. The method comprises the following steps: in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value; applying a reverse recovery pulse in response to reaching a vector recovery time after the preparation module applies; acquiring magnetic resonance data of the detection object with the target imaging sequence in response to reaching a reversal recovery time after application of the reversal recovery pulse; reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object. By adopting the method, before the reverse recovery pulse is applied at the interval of vector recovery time, the longitudinal magnetization vectors corresponding to the detection objects are recovered from the first vector value to the signal intensity of the vector recovery time, so that the longitudinal magnetization vectors corresponding to the detection objects are identical, and the quality of the magnetic resonance image is improved.
Description
Technical Field
The present invention relates to the field of image processing technologies, and in particular, to a magnetic resonance image generating method, apparatus, computer device, and storage medium.
Background
The magnetic resonance heart delay enhancement imaging technology generally adopts a rapid gradient echo imaging sequence under the conditions of electrocardiographic gating and breath-hold after injecting contrast agent for 10 minutes, and utilizes nonselective reversal recovery pulse to selectively inhibit normal myocardial signals and highlight enhanced infarcted myocardial tissues.
The traditional magnetic resonance cardiac delay enhanced imaging method comprises the following steps: and applying inversion recovery pulse after a certain delay time of each electrocardio R wave, applying a rapid imaging sequence when the TI time after the application of the inversion recovery pulse is reached, acquiring magnetic resonance imaging data based on a longitudinal magnetization vector corresponding to the current heart, and reconstructing a magnetic resonance image based on the magnetic resonance imaging data.
However, with conventional techniques, the quality of the magnetic resonance image is low because the corresponding longitudinal magnetization vector of the heart may not be fully recovered during the magnetic resonance imaging, resulting in artifacts in the imaging.
Disclosure of Invention
In view of the foregoing, it is desirable to provide a magnetic resonance image generation method, apparatus, computer device, and storage medium capable of improving image quality.
A magnetic resonance image generation method, the method comprising:
in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value;
applying a magnetization preparation pulse to the detection object, and acquiring magnetic resonance data of the detection object after the magnetization preparation pulse is excited;
reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
In one embodiment, the applying a magnetization preparation pulse to the detection object includes:
applying a reverse recovery pulse in response to reaching a vector recovery time after application by the preparation module;
a target scan sequence is applied to the detection object in response to reaching a reversal recovery time after the reversal recovery pulse is applied.
In one embodiment, the applying a magnetization preparation pulse to the detection object includes:
and applying a target scanning sequence to the detection object in response to reaching a set time after the application of the preparation module.
In one embodiment, the method further comprises:
In a reference cardiac cycle, responding to preset waiting time after receiving an electrocardio trigger signal, and acquiring a reference signal by using a reference imaging sequence;
reconstructing the reference signal to obtain a reference image;
and obtaining a phase sensitive real part image according to the target magnetic resonance image and the reference image.
In one embodiment, obtaining a phase sensitive real part image from the target magnetic resonance image and the reference image includes:
registering the target magnetic resonance image and the reference image;
and carrying out phase-sensitive inversion recovery reconstruction on the registered target magnetic resonance image and the reference image to obtain a phase-sensitive real part image.
In one embodiment, the detecting object is a heart in a reference cardiac cycle, and the acquiring the reference signal by using the reference imaging sequence in response to a preset waiting time after receiving the electrocardiographic trigger signal in the reference cardiac cycle includes:
applying a preparation module in response to receiving an electrocardiographic trigger signal during a reference cardiac cycle to flip a second initial longitudinal magnetization vector corresponding to the heart into a second transverse magnetization vector, and to de-phase into a second vector value;
A reference signal is acquired using the reference imaging sequence in response to reaching a vector recovery time after application by the preparation module.
In one embodiment, the target magnetic resonance image has a resolution that is greater than the resolution of the reference image.
In one embodiment, the target imaging sequence comprises radio frequency pulses of a target flip angle, and the reference imaging sequence comprises radio frequency pulses of a reference flip angle, the reference flip angle being less than or equal to the target flip angle.
In one embodiment, the first K-space data corresponding to the target magnetic resonance image is obtained by filling magnetic resonance data in a plurality of adjacent target cardiac cycles.
A magnetic resonance image generation apparatus, the apparatus comprising:
the preparation module application module is used for applying the preparation module in response to receiving the electrocardio trigger signal in a target cardiac cycle so as to turn over a first initial longitudinal magnetization vector corresponding to the detection object into a first transverse magnetization vector, and the phase dispersion is a first vector value;
the magnetic resonance data acquisition module is used for applying magnetization preparation pulses to the detection object and acquiring magnetic resonance data of the detection object after the magnetization preparation pulses are excited;
And the magnetic resonance image generation module is used for reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
A computer device comprising a memory storing a computer program and a processor which when executing the computer program performs the steps of:
in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value;
applying a magnetization preparation pulse to the detection object, and acquiring magnetic resonance data of the detection object after the magnetization preparation pulse is excited;
reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
A computer readable storage medium having stored thereon a computer program which when executed by a processor performs the steps of:
in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value;
Applying a magnetization preparation pulse to the detection object, and acquiring magnetic resonance data of the detection object after the magnetization preparation pulse is excited;
reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
According to the magnetic resonance image generation method, the device, the computer equipment and the storage medium, after the electrocardio trigger signal is received in the target cardiac cycle, the preparation module is applied, so that the first initial longitudinal magnetization vector corresponding to the detection object is turned over to be the first transverse magnetization vector, and the phase dispersion is the first vector value, for example zero, so that the signal intensity that the longitudinal magnetization vector corresponding to the detection object is recovered from the first vector value to the vector recovery time before the reverse recovery pulse is applied at the interval vector recovery time can be ensured, the longitudinal magnetization vectors corresponding to different cardiac cycles of the detection object are identical, and the generation of artifacts of the magnetic resonance image caused by the inconsistency of the longitudinal magnetization vectors before the reverse recovery pulse is applied in a plurality of target cardiac cycles is avoided, and the improvement of the quality of the magnetic resonance image is facilitated.
Drawings
FIG. 1 is a flow chart of a method of generating magnetic resonance images in one embodiment;
Figure 2 is a schematic diagram of pulse application of a magnetic resonance image generation method in one embodiment;
figure 2A is a schematic diagram of a preparation module of a magnetic resonance image generation method in one embodiment;
FIG. 3 is a schematic diagram of pulse application of a magnetic resonance image generation method in another embodiment;
figure 4 is a schematic diagram of pulse application of a magnetic resonance image generation method in yet another embodiment;
figure 5 is a schematic diagram of pulse application for generating a magnetic resonance image of a subject in one embodiment;
figure 6 is a schematic illustration of the pulse application for generating a magnetic resonance image of a subject in another embodiment;
FIG. 7 is a block diagram of a magnetic resonance image generation apparatus in one embodiment;
fig. 8 is an internal structural diagram of a computer device in one embodiment.
Detailed Description
In order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be further described in detail with reference to the accompanying drawings and examples. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the present application.
The application provides a magnetic resonance image generation method, which comprises the following steps: in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value; applying a magnetization preparation pulse to the detection object, and acquiring magnetic resonance data of the detection object after excitation of the magnetization preparation pulse; reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
Alternatively, the preparation module may include a radio frequency saturation pulse and a dephasing gradient pulse. The radio frequency saturation pulse is used for realizing that a longitudinal magnetization vector corresponding to a detection object is overturned into a transverse magnetization vector; the dephasing gradient pulses are used to achieve dephasing of the transverse magnetization vector.
Alternatively, the application of the magnetization preparation pulse to the detection object may be a T2 preparation pulse or an inversion recovery pulse. For example, in response to reaching a vector recovery time after the preparation module applies, applying a reverse recovery pulse; and applying a target scan sequence to the test object in response to reaching a reverse recovery time after application of the reverse recovery pulse to acquire magnetic resonance data of the test object. For another example, in response to the set time after the preparation module application being reached, a T2 preparation pulse is applied to the detection object; a target scan sequence is applied to the subject to acquire magnetic resonance data of the subject.
In an embodiment, as shown in fig. 1, a magnetic resonance image generating method is provided, where the method is applied to a terminal to illustrate the method, it is understood that the method may also be applied to a server, and may also be applied to a system including the terminal and the server, and implemented through interaction between the terminal and the server. In this embodiment, the method includes the steps of:
Step S102, in response to receiving the electrocardio trigger signal, a preparation module is applied to flip a first initial longitudinal magnetization vector corresponding to the detection object into a first transverse magnetization vector and the phase dispersion is a first vector value in the target cardiac cycle. The object of examination may be, for example, a heart, and the physiological movement cycle/cardiac cycle of the heart is monitored during the examination using an external Electrocardiogram (ECG) device.
Wherein, the cardiac cycle refers to the heart contracting and relaxing once to form a mechanical activity cycle. The electrocardiographic trigger signal may be a signal of an electrocardiograph wave. The electrocardiographic waves may be R waves, P waves, T waves, and the like. The longitudinal magnetization vector refers to the sum of magnetic moment vectors in the direction of the static magnetic field. The transverse magnetization vector refers to the sum of magnetic moment vectors in a plane perpendicular to the direction of the static magnetic field.
Specifically, as shown in fig. 2, in the magnetic resonance cardiac delay enhanced imaging, in a target cardiac cycle, after the terminal receives an electrocardiographic trigger signal, the terminal applies a preparation module (SR after R wave of the electrocardiographic trigger signal) after waiting for a trigger delay Time (TD) greater than or equal to 0 ms. The preparation module is used for reversing a first initial longitudinal magnetization vector corresponding to the heart into a first transverse magnetization vector and dephasing the first transverse magnetization vector into a first vector value. Alternatively, the first vector value may be 0,1, or other value.
Fig. 2A is a schematic timing diagram of a preparation module according to an embodiment of the disclosure. The SR consists of a plurality of saturation pulses and a dephasing gradient, and in this implementation, the SR specifically includes a plurality of 90 ° saturation pulses (selective gradient in slice direction is not shown), while the dephasing gradient may be applied in the phase encoding direction (Gpe), in the frequency encoding direction (Gro) or in the slice selecting direction (Gss) after each 90 ° saturation pulse, each 90 ° frequency selective pulse having the same half-width, and the interval between every two adjacent 90 ° frequency selective pulses is the same. It will be appreciated that the type, number, half-width and spacing between adjacent pulses of the preparation modules contained in the SR may be set according to the heart tissue of different examination objects. In this embodiment of the present application, through setting the SR to a plurality of preparation modules in advance, the method can be applicable to the situation that the main magnetic field of the magnetic resonance system is inhomogeneous, the radio frequency emission field is inhomogeneous, i.e. is insensitive to the main magnetic field inhomogeneity and the radio frequency field inhomogeneity, and especially to the superhigh field (5 tesla and above) environment can improve the dephasing effect after the preparation module is applyed in the target cardiac cycle.
In step S104, an inversion recovery pulse is applied in response to reaching the vector recovery time after the application of the preparation module.
Specifically, after the preparation module applies a vector recovery time T, the terminal applies an inversion recovery pulse (IR in the figure) to invert the longitudinal magnetization vector for the recovery T time to the negative direction.
Step S106, in response to reaching the inversion recovery time after the application of the inversion recovery pulse, acquiring magnetic resonance data of the detection object using the target imaging sequence.
Specifically, a target imaging sequence (IMG in the figure) is excited to acquire magnetic resonance data at the present time at an interval of reverse recovery time T1 after application of the reverse recovery pulse. In this embodiment, the target imaging sequence is excited after TT (trigger time) times of each cardiac cycle. Depending on the inversion recovery time T1, TT corresponding to different cardiac cycles is also different.
Step S108, reconstructing magnetic resonance data to obtain a target magnetic resonance image of the detection object.
Specifically, the terminal reconstructs magnetic resonance data corresponding to the target imaging sequence to obtain a target magnetic resonance image. Optionally, the terminal performs imaging according to magnetic resonance data corresponding to a target rapid imaging sequence (IMG) to obtain a target magnetic resonance image. Alternatively, the target rapid imaging sequence may be a gradient echo (gradient recalled echo, GRE) sequence, or a GRE-based equilibrium steady state free precession (balanced steady state free precession, bSSFP) sequence.
Optionally, the terminal fills magnetic resonance data corresponding to the target imaging sequence in the K space, and then carries out Fourier reconstruction on the data filled in the K space to obtain a target magnetic resonance image. It can be understood that the terminal acquires a part of K-space data of K-space of delay enhancement data in each target cardiac cycle, wherein magnetic resonance data acquired after the last IR and the previous IR are filled in different phase encoding positions of the K-space until the whole K-space is filled completely, and performs magnetic resonance image reconstruction on the magnetic resonance data in the whole K-space to obtain a target magnetic resonance image.
In the magnetic resonance image generation method, after the electrocardiographic trigger signal is received in the target cardiac cycle, the preparation module is applied to enable the first initial longitudinal magnetization vector corresponding to the detection object to be turned over to be the first transverse magnetization vector, and the phase dispersion is the first vector value such as zero, so that the signal intensity of the longitudinal magnetization vector corresponding to the detection object recovered from the first vector value to the vector recovery time before the reverse recovery pulse is applied at the interval vector recovery time can be ensured, the longitudinal magnetization vectors corresponding to different cardiac cycles of the detection object are identical, and the generation of artifacts of the magnetic resonance image caused by the fact that the longitudinal magnetization vectors before the reverse recovery pulses are applied in a plurality of target cardiac cycles are avoided, and the quality of the magnetic resonance image is improved.
In one embodiment, the method further comprises the steps of:
step S112, in a reference cardiac cycle, when a preset waiting time after receiving an electrocardio trigger signal is responded, a reference signal is acquired by using a reference imaging sequence;
step S114, reconstructing a reference signal to obtain a reference image;
step S116, obtaining a real part image of phase sensitivity according to the target magnetic resonance image and the reference image. Optionally, registering the target magnetic resonance image and the reference image; and carrying out phase-sensitive inversion recovery reconstruction on the registered target magnetic resonance image and the reference image to obtain a phase-sensitive real part image.
Wherein the reference cardiac cycle may be the next cardiac cycle adjacent to the target cardiac cycle.
The phase sensitive inversion recovery (phase sensitive inversion recovery, PSIR) uses two inversion recovery pre-pulses, and the first step is to rapidly acquire different inversion Time (TI) magnetic resonance images through segmental or single excitation pulses to determine different TI values, so as to maximize the tissue contrast of delay enhancement; the second step acquires corresponding TI weighted images at the selected TI using a segmental inversion recovery pre-pulse to evaluate the characteristic cardiac magnetic resonance pulse of myocardial activity.
Specifically, during the reference cardiac cycle, the inversion recovery pulse may not be applied. After receiving the electrocardiographic trigger signal, the terminal acquires a reference signal by using a reference imaging sequence (Ref in the figure) at intervals of preset waiting time. And then, reconstructing the reference signal by the terminal to obtain a reference image. Wherein the reference imaging sequence is a reference imaging sequence in phase-sensitive inversion recovery. And finally, the terminal carries out phase-sensitive inversion recovery algorithm processing on the target magnetic resonance image and the reference image to obtain a phase-sensitive real part image.
Optionally, the terminal fills reference signals corresponding to the reference imaging sequences in the K space, and then performs Fourier reconstruction on the reference signals corresponding to the reference imaging sequences in the K space to obtain the reference image. It can be understood that the terminal collects a part of K-space data of K-space of delay enhancement data in each reference cardiac cycle until the whole K-space is filled completely, and reconstructs the data in the whole K-space to obtain a reference image.
In this embodiment, the reference image is acquired, and then the phase-sensitive inversion recovery processing is performed, so that the acquisition of the real part image sensitive to the phase can be realized.
In one embodiment, the step S112 "is related to a possible implementation of acquiring the reference signal during the reference cardiac cycle by using the reference imaging sequence in response to a preset waiting time after receiving the electrocardiographic trigger signal". On the basis of the above embodiment, step S112 may be specifically implemented by the following steps:
Step S1122, in response to receiving the electrocardiograph trigger signal, applying a preparation module to flip a second initial longitudinal magnetization vector corresponding to the heart into a second transverse magnetization vector and to de-phase into a second vector value in the reference cardiac cycle;
in step S1124, a reference signal is acquired using the reference imaging sequence in response to reaching the vector recovery time after the application of the preparation module.
The preset waiting time comprises a preparation module application time and a vector recovery time.
Specifically, as shown in fig. 3, in the reference cardiac cycle, after the terminal receives the electrocardiographic trigger signal, the terminal applies the preparation module (SR in the figure) after waiting for a trigger delay time TD greater than or equal to 0 ms. The preparation module is used for reversing a second initial longitudinal magnetization vector corresponding to the heart into a second transverse magnetization vector and dephasing the second transverse magnetization vector into a second vector value. Alternatively, the second vector value may be 0,1 or other value. Then, a reference signal is acquired using the reference imaging sequence at intervals of vector recovery time after application by the preparation module.
In this embodiment, after receiving the electrocardiographic trigger signal in the reference cardiac cycle, the preparation module is applied to cause the second initial longitudinal magnetization vector corresponding to the heart to be inverted into the second transverse magnetization vector, and the dephasing is the second vector value, for example, zero, so that it can be ensured that the longitudinal magnetization vectors corresponding to the heart are all restored to the signal intensity of the vector restoration time from the second vector value before the imaging of the reference image, so that the longitudinal magnetization vectors corresponding to the heart are all the same, and the generation of artifacts in the reference image due to the inconsistency of the longitudinal magnetization vectors before the imaging of the reference image in a plurality of reference cardiac cycles is avoided, which is beneficial to improving the quality of the reference image.
As shown in fig. 4, in one embodiment, the magnetic resonance data of the detected object may be collected uniformly in the first several target cardiac cycles, so as to obtain a completed K-space data, and then the target magnetic resonance image is reconstructed. Similarly, in the latter reference cardiac cycles, the reference data are collected together and reconstructed to obtain a reference image. In the embodiment, the integrity and the accuracy of the magnetic resonance data can be ensured by continuously acquiring and obtaining complete K space data, so that the quality of the subsequently generated magnetic resonance image can be improved.
Optionally, in one embodiment, applying a magnetization preparation pulse to the test object and acquiring magnetic resonance data of the test object after excitation of the magnetization preparation pulse includes: applying a T2 preparation pulse to the detection object in response to reaching the set time after the application of the preparation module; a target scan sequence is applied to the subject to acquire magnetic resonance data of the subject. Illustratively, after detecting an electrocardiographic trigger signal, a saturation pulse is used to turn the longitudinal magnetization vector to the transverse direction, then a dephasing gradient is used to dephas the transverse magnetization vector to 0, then a certain time is waited, a T2 preparation pulse is used, and then data acquisition is performed, so that the influence of initial Mz inconsistency caused by severe cardiac cycle change can be eliminated, and the scanning time can be reduced. The embodiment can be collected before the medicine is sprayed, or can be collected after the medicine is sprayed.
As shown in fig. 5, in the first cardiac cycle, after detecting the electrocardiographic trigger signal, the longitudinal magnetization vector is flipped to the transverse direction using a preparation module SR including a saturation pulse and a dephasing gradient, and then dephased using the dephasing gradient; then waiting a first time (application interval TT of SR and IMG), executing an IMG sequence for first group data acquisition; separating two cardiac cycles, in the second cardiac cycle, after detecting an electrocardiograph trigger signal, turning over a longitudinal magnetization vector to the transverse direction by using a preparation module SR comprising a saturation pulse and a dephasing gradient, and then carrying out dephasing by using the dephasing gradient; then waiting a second time (SR is the same interval as the application of IMG TT), performing a second set of data acquisitions by the IMG sequence using a T2 preparation pulse (T2 pre 1); in a third cardiac cycle, after an electrocardiographic trigger signal is detected, a preparation module SR comprising a saturation pulse and a dephasing gradient is used for overturning a longitudinal magnetization vector to a transverse direction, and then the dephasing gradient is used for dephasing; then waiting a third time (SR is the same interval as the application of IMG TT), performing a third set of data acquisitions by the IMG sequence using the T2 preparation pulse (T2 pre 2); and reconstructing the first group of data, the second group of data and the third group of data to obtain a T2Mapping image of the detection object. The embodiment of the application provides a rapid cardiac T2Mapping (transverse relaxation time) imaging method, which is characterized in that on the basis of a traditional T2Mapping imaging sequence, saturation pulses are added, then T2Mapping imaging is carried out for a certain time, so that initial longitudinal magnetization vectors are consistent every time, recovery of the longitudinal magnetization vectors does not need to be waited, and each cardiac cycle is acquired, thereby greatly saving scanning time, reducing breath-holding time of a patient, increasing scanning efficiency, and overcoming the severe influence of cardiac cycle change.
To shorten the scan time, acquisitions can be made every cardiac cycle, to increase the amount of data acquired, to provide accuracy of the T2 fit, without changing the scan time, multiple T2 preparation times are still used:
referring to fig. 6, in a first cardiac cycle, after detecting an electrocardiographic trigger signal, a preparation module SR including a saturation pulse and a dephasing gradient is used to flip the longitudinal magnetization vector to the transverse direction, and then the dephasing gradient is used to perform dephasing; then waiting a first time (application interval TT of SR and IMG), executing an IMG sequence for first group data acquisition; adjacent to the first cardiac cycle, in the second cardiac cycle, after detecting the electrocardiographic trigger signal, using a preparation module SR comprising a saturation pulse and a dephasing gradient to turn the longitudinal magnetization vector to the transverse direction, and then using the dephasing gradient to perform dephasing; then waiting a second time (SR is the same interval as the application of IMG TT), performing a second set of data acquisitions by the IMG sequence using a T2 preparation pulse (T2 pre 1); adjacent to the second cardiac cycle, in the third cardiac cycle, after detecting the electrocardiographic trigger signal, using a preparation module SR comprising a saturation pulse and a dephasing gradient to turn the longitudinal magnetization vector to the transverse direction, and then using the dephasing gradient to perform dephasing; then waiting a third time (SR is the same interval as the application of IMG TT), performing a third set of data acquisitions by the IMG sequence using the T2 preparation pulse (T2 pre 2); and reconstructing the first group of data, the second group of data and the third group of data to obtain a T2Mapping image of the detection object.
In one embodiment, the above step S108 "reconstructing magnetic resonance data to obtain a target magnetic resonance image of the detection subject" is referred to. On the basis of the above embodiment, step S108 may be specifically implemented by the following steps:
step S1082, imaging with the target resolution associated with the target imaging sequence according to the magnetic resonance data corresponding to the target imaging sequence, to obtain a target magnetic resonance image.
Further, one possible implementation of the step S114 "reconstructing the reference signal to obtain the reference image" is referred to. On the basis of the above embodiment, step S114 may be specifically implemented by the following steps:
step S1142, imaging with the reference resolution associated with the reference imaging sequence according to the reference signal corresponding to the reference imaging sequence, to obtain a reference image.
Wherein the reference resolution is less than the target resolution.
Specifically, the terminal images with the target resolution associated with the target imaging sequence according to the magnetic resonance data corresponding to the target imaging sequence, and generates a high-resolution target magnetic resonance image. And the terminal images with the reference resolution associated with the reference imaging sequence according to the reference signal corresponding to the reference imaging sequence to obtain a low-resolution reference image.
In this embodiment, a low resolution reference image is acquired, which is beneficial to reduce the magnetic resonance image generation time.
In one embodiment, the above step S108 "reconstructing magnetic resonance data to obtain a target magnetic resonance image of the detection subject" is referred to. On the basis of the above embodiment, step S108 may be specifically implemented by the following steps:
step S108a, imaging is carried out according to the magnetic resonance data corresponding to the target imaging sequence and the target flip angle associated with the target imaging sequence, so as to obtain a target magnetic resonance image.
Further, one possible implementation of the step S112 "acquire a reference signal using a reference imaging sequence" described above is referred to. On the basis of the above embodiment, step S112 may be specifically implemented by the following steps:
in step S112a, parameters of a reference imaging sequence are set, wherein a flip angle of the radio frequency pulse in the reference imaging sequence is set as a reference flip angle.
Wherein the flip angle of the radio frequency pulses in the target imaging sequence is set to the target flip angle. The reference flip angle is less than or equal to the target flip angle.
In this embodiment, the reference image is acquired using the same reference flip angle as the target flip angle, which is beneficial to improving the signal-to-noise ratio of the reference image.
Optionally, before the reconstructing of the reference image and the target magnetic resonance image, it may further comprise: acquiring a physiological motion curve of a detection object; and screening magnetic resonance data corresponding to the target imaging sequence and reference signals corresponding to the reference imaging sequence according to the physiological motion curve. In one embodiment, a set threshold is provided, only the data acquired by the cardiac phase with the signal intensity within the set threshold on the physiological motion curve is reserved, and the magnetic resonance data corresponding to the target imaging sequence and the reference signal corresponding to the reference imaging sequence acquired by the cardiac phase beyond the set threshold are not used in the reconstruction process. Or, the magnetic resonance data corresponding to the target imaging sequence acquired in the target cardiac cycle and with the cardiac phase exceeding the set threshold range are acquired again. In the embodiment of the application, the method and the device can be suitable for detecting objects with uneven heart rate, and when a certain cardiac cycle is detected to be too short or too large, the data acquired in the cardiac cycle are abandoned and acquired again, so that the influence on the image quality caused by the non-ideal data acquisition in a single cycle is avoided; the screening process is performed in real time, so that the re-acquisition of the whole target imaging sequence caused by arrhythmia of individual cardiac cycles is avoided, and the efficiency of cardiac scanning is improved.
It should be understood that, although the steps in the flowchart of fig. 1 are shown in sequence as indicated by the arrows, the steps are not necessarily performed in sequence as indicated by the arrows. The steps are not strictly limited to the order of execution unless explicitly recited herein, and the steps may be executed in other orders. Moreover, at least a portion of the steps in fig. 1 may include a plurality of steps or stages, which are not necessarily performed at the same time, but may be performed at different times, and the order of the steps or stages is not necessarily sequential, but may be performed in rotation or alternatively with at least a portion of the steps or stages in other steps or other steps.
In one embodiment, as shown in fig. 7, there is provided a magnetic resonance image generating apparatus including: a preparation module application module 202, a magnetic resonance data acquisition module 204, and a magnetic resonance image generation module 206, wherein:
the preparation module applying module 202 is configured to apply the preparation module in response to receiving the electrocardiographic trigger signal in the target cardiac cycle, so as to flip the first initial longitudinal magnetization vector corresponding to the detection object into the first transverse magnetization vector, and the dephasing is the first vector value.
The magnetic resonance data acquisition module 204 is configured to apply a magnetization preparation pulse to the detection object, and acquire magnetic resonance data of the detection object after the magnetization preparation pulse is excited.
A magnetic resonance image generation module 206 for reconstructing magnetic resonance data to obtain a target magnetic resonance image of the detection subject.
In the magnetic resonance image generating device, after the electrocardiographic trigger signal is received in the target cardiac cycle, the preparation module is applied to enable the first initial longitudinal magnetization vector corresponding to the detection object to be turned over to be the first transverse magnetization vector, and the phase dispersion is the first vector value, for example zero, so that the signal intensity of the longitudinal magnetization vector corresponding to the detection object recovered from the first vector value to the vector recovery time before the inversion recovery pulse is applied at the interval vector recovery time can be ensured, the longitudinal magnetization vectors corresponding to different cardiac cycles of the detection object are identical, and the generation of artifacts of the magnetic resonance image caused by the fact that the longitudinal magnetization vectors before the inversion recovery pulses are applied in a plurality of target cardiac cycles are avoided, and the quality of the magnetic resonance image is improved.
In one embodiment, the magnetic resonance data acquisition module 204 is specifically configured to apply a reverse recovery pulse in response to reaching a vector recovery time after the preparation module applies; in response to reaching the inversion recovery time after the application of the inversion recovery pulse, a target scan sequence is applied to the detection subject to acquire magnetic resonance data of the detection subject.
In one embodiment, the magnetic resonance data acquisition module 204 is specifically configured to apply a T2 preparation pulse to the test subject in response to reaching a set time after the preparation module applies; a target scan sequence is applied to the subject to acquire magnetic resonance data of the subject.
In one embodiment, the apparatus further comprises: the system comprises a signal acquisition module, a signal reconstruction module and a magnetic resonance image processing module, wherein:
and the signal acquisition module is used for acquiring a reference signal by using a reference imaging sequence in response to the preset waiting time after the electrocardio trigger signal is received in the reference cardiac cycle.
And the signal reconstruction module is used for reconstructing the reference signal to obtain a reference image.
And the magnetic resonance image processing module is used for obtaining a phase sensitive real part image according to the target magnetic resonance image and the reference image.
In one embodiment, the magnetic resonance image processing module is specifically configured to perform a registration operation on the target magnetic resonance image and the reference image; and carrying out phase-sensitive inversion recovery reconstruction on the registered target magnetic resonance image and the reference image to obtain a phase-sensitive real part image.
In one embodiment, the test object is a heart; the signal acquisition module is specifically used for applying the preparation module after responding to the received electrocardio trigger signal in a reference cardiac cycle so as to turn over a second initial longitudinal magnetization vector corresponding to the heart into a second transverse magnetization vector, and the dephasing is a second vector value; the reference signal is acquired using the reference imaging sequence in response to reaching the vector recovery time after the preparation module applies.
For specific limitations of the magnetic resonance image generation apparatus, reference may be made to the above limitations of the magnetic resonance image generation method, and no further description is given here. The respective modules in the magnetic resonance image generation apparatus described above may be implemented in whole or in part by software, hardware, or a combination thereof. The above modules may be embedded in hardware or may be independent of a processor in the computer device, or may be stored in software in a memory in the computer device, so that the processor may call and execute operations corresponding to the above modules.
In one embodiment, a computer device is provided, which may be a terminal, and the internal structure thereof may be as shown in fig. 8. The computer device includes a processor, a memory, a communication interface, a display screen, and an input device connected by a system bus. Wherein the processor of the computer device is configured to provide computing and control capabilities. The memory of the computer device includes a non-volatile storage medium and an internal memory. The non-volatile storage medium stores an operating system and a computer program. The internal memory provides an environment for the operation of the operating system and computer programs in the non-volatile storage media. The communication interface of the computer device is used for carrying out wired or wireless communication with an external terminal, and the wireless mode can be realized through WIFI, an operator network, NFC (near field communication) or other technologies. The computer program is executed by a processor to implement a magnetic resonance image generation method. The display screen of the computer equipment can be a liquid crystal display screen or an electronic ink display screen, and the input device of the computer equipment can be a touch layer covered on the display screen, can also be keys, a track ball or a touch pad arranged on the shell of the computer equipment, and can also be an external keyboard, a touch pad or a mouse and the like.
It will be appreciated by those skilled in the art that the structure shown in fig. 8 is merely a block diagram of some of the structures associated with the present application and is not limiting of the computer device to which the present application may be applied, and that a particular computer device may include more or fewer components than shown, or may combine certain components, or have a different arrangement of components.
In one embodiment, a computer device is provided comprising a memory and a processor, the memory having stored therein a computer program, the processor when executing the computer program performing the steps of:
in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value;
applying a magnetization preparation pulse to the detection object, and acquiring magnetic resonance data of the detection object after excitation of the magnetization preparation pulse;
reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
In the computer device, after the electrocardiographic trigger signal is received in the target cardiac cycle, the preparation module is applied to enable the first initial longitudinal magnetization vector corresponding to the detection object to be turned over to be the first transverse magnetization vector, and the phase dispersion is the first vector value, for example zero, so that the signal intensity of the longitudinal magnetization vector corresponding to the detection object recovered from the first vector value to the vector recovery time before the inversion recovery pulse is applied at the interval vector recovery time can be ensured, the longitudinal magnetization vectors corresponding to different cardiac cycles of the detection object are identical, and the occurrence of artifacts of the magnetic resonance image caused by the fact that the longitudinal magnetization vectors before the inversion recovery pulses are applied in a plurality of target cardiac cycles is avoided, and the quality of the magnetic resonance image is improved.
In one embodiment, the processor when executing the computer program further performs the steps of:
applying a reverse recovery pulse in response to reaching a vector recovery time after the preparation module applies; in response to reaching the inversion recovery time after the application of the inversion recovery pulse, a target scan sequence is applied to the detection subject to acquire magnetic resonance data of the detection subject.
In one embodiment, the processor when executing the computer program further performs the steps of:
applying a T2 preparation pulse to the detection object in response to reaching the set time after the application of the preparation module; a target scan sequence is applied to the subject to acquire magnetic resonance data of the subject.
In one embodiment, the processor when executing the computer program further performs the steps of:
in a reference cardiac cycle, responding to preset waiting time after receiving an electrocardio trigger signal, and acquiring a reference signal by using a reference imaging sequence; reconstructing a reference signal to obtain a reference image; and obtaining a real part image of phase sensitivity according to the target magnetic resonance image and the reference image.
In one embodiment, the processor when executing the computer program further performs the steps of:
registering the target magnetic resonance image and the reference image; and carrying out phase-sensitive inversion recovery reconstruction on the registered target magnetic resonance image and the reference image to obtain a phase-sensitive real part image.
In one embodiment, the processor when executing the computer program further performs the steps of:
applying a preparation module in response to receiving an electrocardiographic trigger signal during a reference cardiac cycle to flip a corresponding second initial longitudinal magnetization vector of the heart to a second transverse magnetization vector, and to de-phase the second vector value; the reference signal is acquired using the reference imaging sequence in response to reaching the vector recovery time after the preparation module applies.
In one embodiment, a computer readable storage medium is provided having a computer program stored thereon, which when executed by a processor, performs the steps of:
in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value;
applying a magnetization preparation pulse to the detection object, and acquiring magnetic resonance data of the detection object after excitation of the magnetization preparation pulse;
reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
In the computer readable storage medium, after the electrocardiographic trigger signal is received in the target cardiac cycle, the preparation module is applied to enable the first initial longitudinal magnetization vector corresponding to the detection object to be turned over to be the first transverse magnetization vector, and the phase dispersion is the first vector value, for example zero, so that the signal intensity of the longitudinal magnetization vector corresponding to the detection object recovered from the first vector value to the vector recovery time before the inversion recovery pulse is applied in the interval vector recovery time can be ensured, the longitudinal magnetization vectors corresponding to different cardiac cycles of the detection object are identical, and the generation of artifacts of the magnetic resonance image caused by the inconsistency of the longitudinal magnetization vectors before the inversion recovery pulses are applied in the multiple target cardiac cycles is avoided, thereby being beneficial to improving the quality of the magnetic resonance image.
In one embodiment, the computer program when executed by the processor further performs the steps of:
applying a reverse recovery pulse in response to reaching a vector recovery time after the preparation module applies; in response to reaching the inversion recovery time after the application of the inversion recovery pulse, a target scan sequence is applied to the detection subject to acquire magnetic resonance data of the detection subject.
In one embodiment, the computer program when executed by the processor further performs the steps of:
applying a T2 preparation pulse to the detection object in response to reaching the set time after the application of the preparation module; a target scan sequence is applied to the subject to acquire magnetic resonance data of the subject.
In one embodiment, the computer program when executed by the processor further performs the steps of:
in a reference cardiac cycle, responding to preset waiting time after receiving an electrocardio trigger signal, and acquiring a reference signal by using a reference imaging sequence; reconstructing a reference signal to obtain a reference image; and obtaining a real part image of phase sensitivity according to the target magnetic resonance image and the reference image.
In one embodiment, the computer program when executed by the processor further performs the steps of:
registering the target magnetic resonance image and the reference image; and carrying out phase-sensitive inversion recovery reconstruction on the registered target magnetic resonance image and the reference image to obtain a phase-sensitive real part image.
In one embodiment, the computer program when executed by the processor further performs the steps of:
applying a preparation module in response to receiving an electrocardiographic trigger signal during a reference cardiac cycle to flip a corresponding second initial longitudinal magnetization vector of the heart to a second transverse magnetization vector, and to de-phase the second vector value; the reference signal is acquired using the reference imaging sequence in response to reaching the vector recovery time after the preparation module applies.
Those skilled in the art will appreciate that implementing all or part of the above described methods may be accomplished by way of a computer program stored on a non-transitory computer readable storage medium, which when executed, may comprise the steps of the embodiments of the methods described above. Any reference to memory, storage, database, or other medium used in embodiments provided herein may include at least one of non-volatile and volatile memory. The nonvolatile Memory may include Read-Only Memory (ROM), magnetic tape, floppy disk, flash Memory, optical Memory, or the like. Volatile memory can include random access memory (Random Access Memory, RAM) or external cache memory. By way of illustration, and not limitation, RAM can be in the form of a variety of forms, such as static random access memory (Static Random Access Memory, SRAM) or dynamic random access memory (Dynamic Random Access Memory, DRAM), and the like.
The technical features of the above embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.
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 invention. It should be noted that it would be apparent to those skilled in the art that various modifications and improvements could be made without departing from the spirit of the present application, which would be within the scope of the present application. Accordingly, the scope of protection of the present application is to be determined by the claims appended hereto.
Claims (10)
1. A method of magnetic resonance image generation, the method comprising:
in a target cardiac cycle, a preparation module is applied in response to receiving an electrocardiograph trigger signal so as to turn a first initial longitudinal magnetization vector corresponding to a detection object into a first transverse magnetization vector, and the open phase is a first vector value;
applying a magnetization preparation pulse to the detection object, and acquiring magnetic resonance data of the detection object after the magnetization preparation pulse is excited;
Reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
2. The method of claim 1, wherein applying a magnetization preparation pulse to the test object and acquiring magnetic resonance data of the test object after the magnetization preparation pulse is excited comprises:
applying a reverse recovery pulse in response to reaching a vector recovery time after application by the preparation module;
and applying a target scanning sequence to the detection object to acquire magnetic resonance data of the detection object in response to reaching the inversion recovery time after the application of the inversion recovery pulse.
3. The method of claim 1, wherein applying a magnetization preparation pulse to the test object and acquiring magnetic resonance data of the test object after the magnetization preparation pulse is excited comprises:
applying a T2 preparation pulse to the detection object in response to reaching a set time after the preparation module applies;
a target scan sequence is applied to the subject to acquire magnetic resonance data of the subject.
4. The method according to claim 2, wherein the method further comprises:
in a reference cardiac cycle, responding to preset waiting time after receiving an electrocardio trigger signal, and acquiring a reference signal by using a reference imaging sequence;
Reconstructing the reference signal to obtain a reference image;
and obtaining a phase sensitive real part image according to the target magnetic resonance image and the reference image.
5. The method of claim 4, wherein deriving a phase-sensitive real image from the target magnetic resonance image and the reference image comprises:
registering the target magnetic resonance image and the reference image;
and carrying out phase-sensitive inversion recovery reconstruction on the registered target magnetic resonance image and the reference image to obtain a phase-sensitive real part image.
6. The method of claim 4, wherein the test object is a heart; the step of acquiring a reference signal by using a reference imaging sequence in response to a preset waiting time after receiving an electrocardio trigger signal in a reference cardiac cycle comprises the following steps:
applying a preparation module in response to receiving an electrocardiographic trigger signal during a reference cardiac cycle to flip a second initial longitudinal magnetization vector corresponding to the heart into a second transverse magnetization vector, and to de-phase into a second vector value;
a reference signal is acquired using the reference imaging sequence in response to reaching a vector recovery time after application by the preparation module.
7. The method of claim 5, wherein the first K-space data corresponding to the target magnetic resonance image is obtained for filling magnetic resonance data in a plurality of adjacent target cardiac cycles.
8. A magnetic resonance image generation apparatus, the apparatus comprising:
the preparation module application module is used for applying the preparation module in response to receiving the electrocardio trigger signal in a target cardiac cycle so as to turn over a first initial longitudinal magnetization vector corresponding to the detection object into a first transverse magnetization vector, and the phase dispersion is a first vector value;
the magnetic resonance data acquisition module is used for applying magnetization preparation pulses to the detection object and acquiring magnetic resonance data of the detection object after the magnetization preparation pulses are excited;
and the magnetic resonance image generation module is used for reconstructing the magnetic resonance data to obtain a target magnetic resonance image of the detection object.
9. A computer device comprising a memory and a processor, the memory storing a computer program, characterized in that the processor implements the steps of the method of any of claims 1 to 7 when the computer program is executed.
10. A computer readable storage medium, on which a computer program is stored, characterized in that the computer program, when being executed by a processor, implements the steps of the method of any of claims 1 to 7.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111348619.8A CN116125350A (en) | 2021-11-15 | 2021-11-15 | Magnetic resonance image generation method, device, computer equipment and storage medium |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111348619.8A CN116125350A (en) | 2021-11-15 | 2021-11-15 | Magnetic resonance image generation method, device, computer equipment and storage medium |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN116125350A true CN116125350A (en) | 2023-05-16 |
Family
ID=86310556
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202111348619.8A Pending CN116125350A (en) | 2021-11-15 | 2021-11-15 | Magnetic resonance image generation method, device, computer equipment and storage medium |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN116125350A (en) |
-
2021
- 2021-11-15 CN CN202111348619.8A patent/CN116125350A/en active Pending
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US9835705B2 (en) | System and method for free-breathing volumetric imaging of cardiac tissue | |
| US8581583B2 (en) | Method and apparatus for magnetic resonance imaging to create T1 maps | |
| WO2020019412A1 (en) | Magnetic resonance imaging method and apparatus, and device and storage medium | |
| CN107510458B (en) | Magnetic resonance imaging method and equipment | |
| US5474067A (en) | Method for time-resolved MR-imaging | |
| JP2016502927A (en) | System and method for improved cardiac imaging of subjects with adverse cardiac conditions | |
| Tan et al. | Dynamic water/fat separation and inhomogeneity mapping—joint estimation using undersampled triple‐echo multi‐spoke radial FLASH | |
| US10670684B2 (en) | Free-breathing non-contrast MR angiography | |
| CN115639510A (en) | Magnetic resonance imaging method, spectroscopic imaging method, apparatus, device, and storage medium | |
| CN111257810B (en) | Magnetic resonance signal acquisition system and method | |
| Moeller et al. | Multi-scale locally low-rank noise reduction for high-resolution dynamic quantitative cardiac MRI | |
| WO2018144573A1 (en) | System and method for producing temporally resolved images depicting late-gadolinium enhancement with magnetic resonance imaging | |
| US10420512B2 (en) | Dynamic magnetic resonance imaging with variable contrast | |
| US10948559B2 (en) | Method of processing MR images to estimate a longitudinal relaxation time constant | |
| Kim et al. | Improved cine displacement‐encoded MRI using balanced steady‐state free precession and time‐adaptive sensitivity encoding parallel imaging at 3 T | |
| CN116125350A (en) | Magnetic resonance image generation method, device, computer equipment and storage medium | |
| US20190064294A1 (en) | Method of performing magnetic resonance imaging and a magnetic resonance apparatus | |
| US11980457B2 (en) | Systems and methods for simultaneous multi-slice multitasking imaging | |
| US11547317B2 (en) | TI scout for inversion recovery sequence | |
| US11150316B2 (en) | Hybrid perfusion-interleaved diffusion imaging | |
| CN116973823B (en) | Line scanning magnetic resonance imaging method and system based on full steady-state balance precession | |
| Morita et al. | Saturation recovery myocardial T1 mapping with a composite radiofrequency pulse on a 3T MR imaging system | |
| JP2023541775A (en) | Method and apparatus for acquiring and reconstructing a sequence of diffusion-weighted magnetic resonance images covering a volume | |
| CN111009020A (en) | Image reconstruction method and device, computer equipment and storage medium | |
| CN112986878B (en) | Coronary artery imaging method and magnetic resonance imaging system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |