WO2021217509A1 - Procédé et système d'imagerie de relaxation spin-réseau dans un système de coordonnées rotatif à résonance magnétique - Google Patents

Procédé et système d'imagerie de relaxation spin-réseau dans un système de coordonnées rotatif à résonance magnétique Download PDF

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WO2021217509A1
WO2021217509A1 PCT/CN2020/087847 CN2020087847W WO2021217509A1 WO 2021217509 A1 WO2021217509 A1 WO 2021217509A1 CN 2020087847 W CN2020087847 W CN 2020087847W WO 2021217509 A1 WO2021217509 A1 WO 2021217509A1
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spin
coordinate system
rotating coordinate
lattice relaxation
tsl
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PCT/CN2020/087847
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Chinese (zh)
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朱燕杰
刘元元
梁栋
王海峰
刘新
郑海荣
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深圳先进技术研究院
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    • 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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • 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

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  • the present invention relates to the technical field of magnetic resonance parametric imaging, and more specifically, to a spin-lattice relaxation imaging method and system under a magnetic resonance rotating coordinate system.
  • Magnetic resonance parametric imaging can characterize some inherent information of tissues, and has become an important, safe and effective diagnostic tool.
  • T 1 ⁇ a new parameter relaxation-spin-lattice relaxation in the rotating frame (T 1 ⁇ ) in the rotating frame of magnetic resonance has received more and more attention from researchers.
  • T 1 ⁇ imaging is an imaging method that explores the interaction of molecules in slow motion to cause relaxation, and has been used in the examination of many diseases.
  • T 1 ⁇ imaging locks the effective magnetic field in the horizontal axis direction to avoid disordered and spontaneous energy transfer between macromolecules by transverse relaxation, so that the magnetization or spin becomes orderly.
  • This technology can evaluate hydrogen atoms and large molecules in free water.
  • the low-frequency flow between molecules reflects the density of cells and detects changes in the metabolism and biochemical information of water-containing tissues at the molecular level. Therefore, it can provide screening and early warning information for early lesions and mild lesions before the morphological changes of the tissues, and provide a reliable basis for early detection and early treatment.
  • T 1 ⁇ has important application value in the preoperative grading of brain tumors, the research of progressive disease, Alzheimer's disease and Parkinson's disease.
  • T 1 ⁇ imaging uses a resonant and continuous spin-locked pulse to force the transverse magnetization vector to remain in the direction of the transverse magnetization vector for relaxation. At this time, the transverse magnetization vector relaxes in a new way.
  • the spin-locked magnetization vector is based on T The 1 ⁇ time constant relaxes the spin lattice in the rotating coordinate system.
  • TSL spin-locking times
  • T 1 ⁇ weighted signals of different intensities are collected, and a certain signal relaxation model is used to fit the signals to obtain the T 1 ⁇ diagram.
  • the T 1 ⁇ quantitative imaging sequence is usually realized by adding a T 1 ⁇ preparation pulse before the conventional fast spin echo or gradient echo sequence, and acquires images with different T 1 ⁇ weights by changing the spin lock time.
  • the traditional two-dimensional T 1 ⁇ quantitative imaging technology can only acquire one layer of images after each T 1 ⁇ preparation pulse.
  • the overall acquisition time is the time to acquire an image ⁇ the number of TSL ⁇ the number of acquisition layers.
  • In the published research work on the quantification of brain T 1 ⁇ usually only one layer is collected.
  • Three-dimensional T 1 ⁇ quantitative imaging faces similar problems, and the scanning time usually exceeds 30 minutes. Because the existing T 1 ⁇ quantitative imaging time is too long, the resolution and coverage of the image are limited.
  • the prior art is mainly carried out in the following three directions: 1) Reduce the number of TSLs. This method reduces the number of T 1 ⁇ - weighted images collected due to the reduction of TSL, so it is quantitative The accuracy is also reduced. 2) Adopt fast imaging sequence. Due to the limitation of hardware, the scanning speed will not be significantly improved in this way. 3) Adopt fast imaging technology.
  • the current commercial fast imaging technology is mainly parallel imaging technology (such as sensitivity coding (SENSE), generalized automatic calibration part parallel acquisition (GRAPPA), etc.), but this method is affected by parallel imaging array lines.
  • SENSE sensitivity coding
  • GRAPPA generalized automatic calibration part parallel acquisition
  • the limit of the circle the higher the acceleration factor, the lower the signal-to-noise ratio of the image obtained after imaging, so the scanning speed using this method can usually only reach 2-3 times.
  • the purpose of the present invention is to overcome the above-mentioned shortcomings of the prior art, and provide a spin-lattice relaxation imaging method and system in a magnetic resonance rotating coordinate system, which is a new method of rapid and wide-range magnetic resonance T 1 ⁇ quantitative imaging.
  • the technical solution can realize fast T 1 ⁇ quantitative imaging with multiple layers and high signal-to-noise ratio.
  • a spin-lattice relaxation imaging method in a magnetic resonance rotating coordinate system includes the following steps:
  • the spin-lattice relaxation weighted image data in the rotating coordinate system of the target image For different spin-locking times, configure the spin-lattice relaxation weighted image data in the rotating coordinate system of the target image to be collected twice, and set the recovery time between two consecutive acquisitions to obtain a two-dimensional multi-layer rotating coordinate system Down-spin lattice relaxation imaging data;
  • the acquired spin-lattice relaxation imaging data in the two-dimensional multilayer rotating coordinate system is reconstructed, and the final spin-lattice relaxation parameter map in the rotating coordinate system is fitted. .
  • the spin-lattice relaxation imaging data in a two-dimensional multilayer rotating coordinate system is obtained according to the following steps:
  • the last 90-degree pulse in the spin-lattice relaxation preparation pulse in the rotating coordinate system during the first acquisition is applied along the -x axis, and the longitudinal magnetization vector acquired for the first time is expressed as:
  • M 1 (TSL) M 0 +(M init e -TSL/T1 ⁇ -M 0 )e -Trec/T1 ;
  • the last 90-degree pulse in the spin-lattice relaxation preparation pulse in the rotating coordinate system during the second acquisition is applied along the x-axis direction, and the longitudinal magnetization vector acquired in the second acquisition is expressed as:
  • M init is the longitudinal magnetization vector before the spin-lattice relaxation preparation pulse is applied in the rotating coordinate system
  • M 0 is the longitudinal magnetization vector in the equilibrium state
  • T1 is the time constant of longitudinal relaxation
  • TSL represents the spin lock Time
  • T 1 ⁇ is the spin-lattice relaxation time in the rotating coordinate system
  • M(TSL) M 1 (TSL)-M 2 (TSL)
  • A 2M init e -Trec/T1
  • Trec is the first time Recovery time between acquisition and second acquisition.
  • the frequency encoding direction is fully collected, and in the phase encoding direction, the center part of the K-space adopts a uniform density under-sampling method.
  • the area outside the center of K-space adopts variable density under-sampling, and the sampling density decreases as the distance from the center of K-space increases.
  • reconstructing the acquired spin-lattice relaxation imaging data in the two-dimensional multilayer rotating coordinate system includes the following sub-steps:
  • ⁇ 1 represents the l 1 norm
  • C( ⁇ ) is an operation operator, which represents the pixel-level signal compensation of the image
  • X is the image sequence to be reconstructed
  • L is the image in the form of a matrix.
  • the low-rank part, S represents the residual of the image and the low-rank part L
  • E is the multi-channel coil coding matrix, which is equal to the product of the under-picked Fourier operator and the multi-channel coil sensitivity matrix
  • Rank(L) represents the matrix L
  • the rank of, d represents the under-collected K-space data.
  • the pixel-level signal compensation for the image is represented as multiplying each pixel in the image by a compensation coefficient.
  • the compensation coefficient is expressed as:
  • Coef represents the compensation coefficient
  • TSL k is the k-th spin lock time
  • T is the number of the spin lock time TSL.
  • a spin-lattice relaxation imaging system in a magnetic resonance rotating coordinate system includes:
  • Icon image acquisition unit For different spin locking times, configure the spin lattice relaxation weighted image data in the rotating coordinate system of the target image acquired in two times and set the recovery time between two consecutive acquisitions, Obtain spin-lattice relaxation imaging data in a two-dimensional multilayer rotating coordinate system;
  • Low-resolution image acquisition unit used to acquire low-resolution image data used to reconstruct the K-space center data and estimate the sensitivity matrix of the multi-channel coil;
  • Image reconstruction unit used to reconstruct the spin-lattice relaxation imaging data in the collected two-dimensional multi-layer rotating coordinate system in the rotating coordinate system based on the low-resolution image data, and fitting the final rotating coordinate The spin lattice relaxation parameter diagram under the system.
  • the present invention has the advantage that, in view of the existing T 1 ⁇ quantitative imaging time being too long, which limits the resolution and coverage of the image, the present invention provides a two-dimensional T 1 ⁇ capable of rapid multi-layer scanning. Quantitative imaging program. At the same time, in order to improve image acquisition efficiency and reduce scanning time, a two-dimensional under-sampling method with high acceleration multiples is proposed, and a low-rank and sparse decomposition model based on parallel imaging and signal compensation is used to reconstruct high quality from highly under-sampled under-sampled data. the parameter T 1 ⁇ weighted images to obtain a more accurate T 1 ⁇ FIG parameters, and by combining quantitative calculation undersampled variable density ultimately multidimensional, high SNR T 1 ⁇ rapid quantitative imaging.
  • FIG. 1 is a flowchart of a spin-lattice relaxation imaging method in a magnetic resonance rotating coordinate system according to an embodiment of the present invention
  • FIG. 2 is a schematic diagram of a two-dimensional multilayer T 1 ⁇ quantitative imaging sequence according to an embodiment of the present invention
  • Fig. 3 is a schematic diagram of under-sampling according to an embodiment of the present invention.
  • the present invention addresses the problems of traditional two-dimensional magnetic resonance T 1 ⁇ quantitative imaging T 1 ⁇ that can only acquire one image after preparing the pulse and the scanning time is long, and provides a two-dimensional T 1 ⁇ quantitative imaging scheme capable of multi-layer scanning and two-dimensional high acceleration multiples Under-sampling scheme, and based on signal compensation low-rank plus sparse decomposition model, from highly under-sampled under-sampling data to reconstruct high-quality T 1 ⁇ parameter weighted image, so as to obtain a more accurate T 1 ⁇ parameter map.
  • the spin-lattice relaxation imaging method in the magnetic resonance rotating coordinate system includes the following steps:
  • step S1000 for different spin locking times, it is configured to acquire T 1 ⁇ weighted image data of the target image in two times to obtain a T 1 ⁇ parameter relaxation model.
  • Figure 2 is a schematic diagram of a two-dimensional multilayer T 1 ⁇ quantitative imaging sequence
  • Figure 2 (a) is a schematic diagram of a two-dimensional multilayer T 1 ⁇ quantitative imaging sequence, taking two target images as an example
  • Figure 2 (b) is the first T 1 ⁇ acquisition times a schematic preparation pulses
  • FIG. 2 (c) is the second acquisition schematically T 1 ⁇ preparation pulses.
  • FIG. 1 ⁇ preparation pulses In the embodiment of FIG.
  • the longitudinal magnetization vector acquired for the first time is expressed as:
  • the longitudinal magnetization vector collected for the second time is expressed as:
  • M init is applied before the longitudinal magnetization vector preparation pulse time T 1 ⁇
  • M 0 is the equilibrium longitudinal magnetization vector
  • T 1 is the longitudinal relaxation time constant
  • TSL represents spin lock time
  • T 1 ⁇ is a rotating coordinate system The relaxation time of the spin lattice under.
  • a recovery time is introduced, and the acquisition is divided into two times, and the T 1 ⁇ preparation pulses of the two acquisitions are different.
  • step S2000 in the image acquisition process, a sampling method of full sampling in the frequency encoding direction and variable density under sampling in the phase encoding direction is adopted to obtain two-dimensional multi-layer T 1 ⁇ imaging data.
  • the present invention adopts a sampling method of full sampling in the frequency encoding direction and variable density under sampling in the phase encoding direction in image acquisition.
  • K x and K y direction see Fig. 3 and K y and K t is a schematic directions, wherein the direction of the whole mining K x, K y -K t in a plane, with conventional compression based on sparse sampling perception
  • the theoretical under-sampling method is different.
  • the central part of the K-space adopts the uniform under-sampling method, while the area outside the K-space center adopts the variable-density under-sampling method, and the sampling density is reduced according to the distance from the center of the K-space, for example ,
  • the higher sampling density is used when the distance is short, and the lower sampling density is used when the distance is short.
  • FIG. 3 (a) is a K x and K y direction of the matrix size of 256 ⁇ 256 sub-sampling is a schematic
  • FIG. 3 (b) K y and K t is the orientation matrix size of 256 ⁇ 5 undersampled schematically.
  • the original signal can be accurately reconstructed from the highly under-collected data. Therefore, using the two-dimensional multi-layer T 1 ⁇ imaging sequence of step S1000 and the under-sampling method of step S2000, the T 1 ⁇ weighted image data of different TSLs are collected in two times (the scanning parameters of the first acquisition and the second acquisition are exactly the same ) While improving the scanning efficiency, it ensures accurate parameter weighted images and parameter values.
  • variable-density under-sampling method can not only improve the scanning efficiency, but also ensure the quality of the reconstructed image.
  • Step S3000 collecting low-resolution image data for reconstruction of K-space center data and estimating the sensitivity matrix of the multi-channel coil.
  • a low-resolution data is collected for subsequent reconstruction of the K-space center data and estimation of the multi-channel coil sensitivity matrix.
  • the method for estimating the multi-channel coil sensitivity matrix can use the existing technology. This will not be repeated here.
  • step S4000 the two-dimensional multilayer T 1 ⁇ imaging data is reconstructed to obtain a reconstructed T 1 ⁇ parameter weighted image.
  • the under-collected two-dimensional multilayer T 1 ⁇ imaging data can be reconstructed in combination with the existing technology.
  • the reconstruction of the under-collected two-dimensional multi-layer T 1 ⁇ imaging data includes the following steps:
  • Step S141 firstly, using the VCC-GRAPPA method and the low-resolution image to reconstruct the central part of the K-space data.
  • VCC-GRAPPA method can refer to the existing literature ("Improving GRAPPA reconstruction using joint nonlinear kernel mapped and phase conjugated virtual coils", Physic in Medicine and Biology, 2019, 64, 14NT01 (10pp), DOI: 10.1088/1361-6560/ ab274d)
  • Step S142 using the reconstructed K-space central part data to estimate the sensitivity matrix of the multi-channel coil.
  • step S143 on the basis of step S141 and step S142, the T 1 ⁇ weighted image of each layer is reconstructed separately, and the solution model is expressed as:
  • ⁇ 1 represents the l 1 norm
  • C( ⁇ ) is an operation operator that represents pixel-level signal compensation for the image
  • X is the image sequence to be reconstructed, and its size is expressed as the number of voxels ⁇
  • a matrix of TSL numbers (T) (T)
  • L is the low-rank part of the image expressed in matrix form, S represents the residual of the image and the low-rank part L
  • E is the multi-channel coil coding matrix, which is equal to the under-picked Fourier operator The product of the sensitivity matrix of the coil
  • Rank(L) represents the rank of the matrix L
  • d represents the under-collected K-space data.
  • signal compensation can be specifically expressed as multiplying each pixel in the image by a compensation coefficient, which can be obtained by the following formula:
  • TSL k is the k-th spin-lock time
  • T is the number of spin-lock time (TSL).
  • the solution process of formula (5) includes the following steps:
  • Step S151 Transform the K-space center data reconstructed by VCC-GRAPPA into the image domain through Fourier transform, fit the image according to the T 1 ⁇ relaxation model of formula (4), and estimate the initial T 1 ⁇ parameters, And according to formula (6), the initial value of the compensation coefficient Coef 0 is obtained ;
  • Step S152-1 compensates the image according to the compensation coefficient, that is Where U represents the compensated image
  • SVT( ⁇ ) represents the singular value threshold operation operator, which is defined as:
  • U and V are the matrices of left and right singular value vectors
  • V H represents the conjugate transpose of V
  • ⁇ is the diagonal matrix composed of the singular values of M
  • ⁇ ⁇ ( ⁇ ) means to keep the largest singular value in ⁇ unchanged, and the others are all 0.
  • update S j is a soft threshold operator, defined as:
  • p is an element of the image matrix and v is the threshold.
  • Step S152-3 according to the X i obtained in step S152-2, combined with the parameter relaxation model in formula (4), update And update the compensation coefficient
  • Step S152-4 When the algorithm reaches the iteration termination condition (for example, the number of iterations is greater than the maximum number of iterations or the reconstruction error between two adjacent iterations is less than a preset value), the loop iteration is terminated, and the final reconstruction parameter weight is obtained Image X.
  • the iteration termination condition for example, the number of iterations is greater than the maximum number of iterations or the reconstruction error between two adjacent iterations is less than a preset value
  • step S5000 according to the reconstructed T 1 ⁇ parameter weighted image and the T 1 ⁇ parameter relaxation model, non-linear fitting is performed on all pixels in the image to fit the final T 1 ⁇ parameter map.
  • the image sequence is arranged into a space-parameter matrix according to the parameter direction, where each column of the matrix represents the magnetic resonance image collected at a certain TSL time, and then the space-parameter matrix (this matrix actually represents the image) is decomposed into Low-rank component (L) and sparse component (S).
  • L Low-rank component
  • S sparse component
  • each iteration will update the T 1 ⁇ parameter map according to the newly reconstructed T 1 ⁇ weighted image and the T 1 ⁇ parameter relaxation model, and use the updated T 1 ⁇ parameter map in the next iteration
  • the signal compensation is repeated in this way, until the algorithm reaches the iterative termination condition, and the reconstruction is stopped.
  • the T 1 ⁇ parameter relaxation model is used to fit the reconstructed parameter-weighted image to obtain the final T 1 ⁇ parameter map.
  • the present invention can realize multi-layer T 1 ⁇ quantitative imaging, and the designed variable density under-sampling method can greatly accelerate the data scanning speed and reduce the T 1 ⁇ quantitative imaging.
  • the imaging time, during image reconstruction, the present invention can accurately reconstruct a parameter-weighted image from highly under-collected data, and further improve the image signal-to-noise ratio through quantitative calculation.
  • the present invention may be a system, a method and/or a computer program product.
  • the computer program product may include a computer-readable storage medium loaded with computer-readable program instructions for enabling a processor to implement various aspects of the present invention.
  • the computer-readable storage medium may be a tangible device that can hold and store instructions used by the instruction execution device.
  • the computer-readable storage medium may be, for example, but not limited to, an electrical storage device, a magnetic storage device, an optical storage device, an electromagnetic storage device, a semiconductor storage device, or any suitable combination of the foregoing.
  • Non-exhaustive list of computer-readable storage media include: portable computer disks, hard disks, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM) Or flash memory), static random access memory (SRAM), portable compact disk read-only memory (CD-ROM), digital versatile disk (DVD), memory stick, floppy disk, mechanical encoding device, such as a printer with instructions stored thereon
  • RAM random access memory
  • ROM read-only memory
  • EPROM erasable programmable read-only memory
  • flash memory flash memory
  • SRAM static random access memory
  • CD-ROM compact disk read-only memory
  • DVD digital versatile disk
  • memory stick floppy disk
  • mechanical encoding device such as a printer with instructions stored thereon
  • the computer-readable storage medium used here is not interpreted as the instantaneous signal itself, such as radio waves or other freely propagating electromagnetic waves, electromagnetic waves propagating through waveguides or other transmission media (for example, light pulses through fiber optic cables), or through wires Transmission of electrical signals.
  • the computer-readable program instructions described herein can be downloaded from a computer-readable storage medium to various computing/processing devices, or downloaded to an external computer or external storage device via a network, such as the Internet, a local area network, a wide area network, and/or a wireless network.
  • the network may include copper transmission cables, optical fiber transmission, wireless transmission, routers, firewalls, switches, gateway computers, and/or edge servers.
  • the network adapter card or network interface in each computing/processing device receives computer-readable program instructions from the network, and forwards the computer-readable program instructions for storage in the computer-readable storage medium in each computing/processing device .
  • the computer program instructions used to perform the operations of the present invention may be assembly instructions, instruction set architecture (ISA) instructions, machine instructions, machine-related instructions, microcode, firmware instructions, status setting data, or in one or more programming languages.
  • Source code or object code written in any combination, the programming language includes object-oriented programming languages such as Smalltalk, C++, etc., and conventional procedural programming languages such as "C" language or similar programming languages.
  • Computer-readable program instructions can be executed entirely on the user's computer, partly on the user's computer, executed as a stand-alone software package, partly on the user's computer and partly executed on a remote computer, or entirely on the remote computer or server implement.
  • the remote computer can be connected to the user's computer through any kind of network-including a local area network (LAN) or a wide area network (WAN), or it can be connected to an external computer (for example, using an Internet service provider to connect to the user's computer) connect).
  • LAN local area network
  • WAN wide area network
  • an electronic circuit such as a programmable logic circuit, a field programmable gate array (FPGA), or a programmable logic array (PLA), can be customized by using the status information of the computer-readable program instructions.
  • the computer-readable program instructions are executed to implement various aspects of the present invention.
  • These computer-readable program instructions can be provided to the processor of a general-purpose computer, a special-purpose computer, or other programmable data processing device, thereby producing a machine that makes these instructions when executed by the processor of the computer or other programmable data processing device , A device that implements the functions/actions specified in one or more blocks in the flowcharts and/or block diagrams is produced. It is also possible to store these computer-readable program instructions in a computer-readable storage medium. These instructions make computers, programmable data processing apparatuses, and/or other devices work in a specific manner. Thus, the computer-readable medium storing the instructions includes An article of manufacture, which includes instructions for implementing various aspects of the functions/actions specified in one or more blocks in the flowcharts and/or block diagrams.
  • each block in the flowchart or block diagram may represent a module, program segment, or part of an instruction, and the module, program segment, or part of an instruction contains one or more components for realizing the specified logical function.
  • Executable instructions may also occur in a different order from the order marked in the drawings. For example, two consecutive blocks can actually be executed substantially in parallel, or they can sometimes be executed in the reverse order, depending on the functions involved.
  • each block in the block diagram and/or flowchart, and the combination of the blocks in the block diagram and/or flowchart can be implemented by a dedicated hardware-based system that performs the specified functions or actions Or it can be realized by a combination of dedicated hardware and computer instructions. It is well known to those skilled in the art that implementation through hardware, implementation through software, and implementation through a combination of software and hardware are all equivalent.

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Abstract

L'invention concerne un procédé et un système d'imagerie de relaxation spin-réseau dans un système de coordonnées rotatif à résonance magnétique. Le procédé comprend : par rapport à différents moments de blocage de spin, la configuration de ceux-ci en tant que données d'image pondérées de relaxation spin-réseau dans un système de coordonnées rotatif qui acquiert une image cible dans deux cas séparés, et la configuration d'un temps de récupération entre deux acquisitions consécutives, de façon à obtenir des données d'imagerie de relaxation spin-réseau dans un système de coordonnées rotatif multicouche bidimensionnel ; l'acquisition des données d'image à basse résolution pour reconstruire des données de centre d'espace K et estimer une matrice de sensibilité de bobine à canaux multiples ; et sur la base des données d'image à basse résolution, la reconstruction des données d'imagerie de relaxation spin-réseau acquises dans le système de coordonnées rotatif multicouche bidimensionnel, et l'ajustement d'un diagramme de paramètres de relaxation spin-réseau final dans le système de coordonnées rotatif. La présente invention peut réaliser une imagerie quantitative de relaxation spin-réseau dans un système de coordonnées rotatif à résonance magnétique rapide ayant de multiples couches et un rapport signal sur bruit élevé.
PCT/CN2020/087847 2020-04-29 2020-04-29 Procédé et système d'imagerie de relaxation spin-réseau dans un système de coordonnées rotatif à résonance magnétique WO2021217509A1 (fr)

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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090273343A1 (en) * 2006-10-17 2009-11-05 The Trustees Of The University Of Pennsylvania Reducing imaging-scan times for mri systems
US9285446B2 (en) * 2010-09-29 2016-03-15 Isis Innovation Limited Systems and methods for shortened look locker inversion recovery (Sh-MOLLI) cardiac gated mapping of T1
CN108175409A (zh) * 2018-01-05 2018-06-19 郜发宝 一种定量快速锁频磁共振成像方法
CN109658468A (zh) * 2018-12-12 2019-04-19 深圳先进技术研究院 磁共振参数成像方法、装置、设备及存储介质

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090273343A1 (en) * 2006-10-17 2009-11-05 The Trustees Of The University Of Pennsylvania Reducing imaging-scan times for mri systems
US9285446B2 (en) * 2010-09-29 2016-03-15 Isis Innovation Limited Systems and methods for shortened look locker inversion recovery (Sh-MOLLI) cardiac gated mapping of T1
CN108175409A (zh) * 2018-01-05 2018-06-19 郜发宝 一种定量快速锁频磁共振成像方法
CN109658468A (zh) * 2018-12-12 2019-04-19 深圳先进技术研究院 磁共振参数成像方法、装置、设备及存储介质

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