WO2018085969A1 - 磁共振血管壁成像方法和设备 - Google Patents

磁共振血管壁成像方法和设备 Download PDF

Info

Publication number
WO2018085969A1
WO2018085969A1 PCT/CN2016/104975 CN2016104975W WO2018085969A1 WO 2018085969 A1 WO2018085969 A1 WO 2018085969A1 CN 2016104975 W CN2016104975 W CN 2016104975W WO 2018085969 A1 WO2018085969 A1 WO 2018085969A1
Authority
WO
WIPO (PCT)
Prior art keywords
pulse
magnetic resonance
space
magnetization vector
relaxation time
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.)
Ceased
Application number
PCT/CN2016/104975
Other languages
English (en)
French (fr)
Inventor
张磊
钟耀祖
刘新
胡小情
郑海荣
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shenzhen Institute of Advanced Technology of CAS
Original Assignee
Shenzhen Institute of Advanced Technology of CAS
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Shenzhen Institute of Advanced Technology of CAS filed Critical Shenzhen Institute of Advanced Technology of CAS
Priority to PCT/CN2016/104975 priority Critical patent/WO2018085969A1/zh
Priority to CN201680022139.3A priority patent/CN107690309B/zh
Publication of WO2018085969A1 publication Critical patent/WO2018085969A1/zh
Priority to US15/986,462 priority patent/US10746833B2/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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
    • G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
    • G01R33/56509—Correction of image distortions, e.g. due to magnetic field inhomogeneities due to motion, displacement or flow, e.g. gradient moment nulling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033—Features or image-related aspects of imaging apparatus, e.g. for MRI, optical tomography or impedance tomography apparatus; Arrangements of imaging apparatus in a room
    • A61B5/004—Features or image-related aspects of imaging apparatus, e.g. for MRI, optical tomography or impedance tomography apparatus; Arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part
    • A61B5/0042—Features or image-related aspects of imaging apparatus, e.g. for MRI, optical tomography or impedance tomography apparatus; Arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part for the brain
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
    • 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
    • G01R33/50—NMR imaging systems based on the determination of relaxation times, e.g. T1 measurement by IR sequences; T2 measurement by multiple-echo sequences
    • 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
    • G01R33/5607—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reducing the NMR signal of a particular spin species, e.g. of a chemical species for fat suppression, or of a moving spin species for black-blood imaging
    • 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
    • G01R33/5608—Data processing and visualization specially adapted for MR, e.g. for feature analysis and pattern recognition on the basis of measured MR data, segmentation of measured MR data, edge contour detection on the basis of measured MR data, for enhancing measured MR data in terms of signal-to-noise ratio by means of noise filtering or apodization, for enhancing measured MR data in terms of resolution by means for deblurring, windowing, zero filling, or generation of gray-scaled images, colour-coded images or images displaying vectors instead of pixels
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T11/00—Two-dimensional [2D] image generation
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T12/00—Tomographic reconstruction from projections
    • G06T12/10—Image preprocessing, e.g. calibration, positioning of sources or scatter correction
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2576/00—Medical imaging apparatus involving image processing or analysis
    • A61B2576/02—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part
    • A61B2576/026—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part for the brain
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/03—Measuring fluid pressure within the body other than blood pressure, e.g. cerebral pressure ; Measuring pressure in body tissues or organs
    • A61B5/032—Spinal fluid pressure
    • 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
    • G01R33/563—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution of moving material, e.g. flow contrast angiography
    • G01R33/5635—Angiography, e.g. contrast-enhanced angiography [CE-MRA] or time-of-flight angiography [TOF-MRA]
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10072—Tomographic images
    • G06T2207/10088—Magnetic resonance imaging [MRI]
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2210/00—Indexing scheme for image generation or computer graphics
    • G06T2210/41—Medical
    • G—PHYSICS
    • G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H30/00—ICT specially adapted for the handling or processing of medical images
    • G16H30/40—ICT specially adapted for the handling or processing of medical images for processing medical images, e.g. editing

Definitions

  • the present invention relates to the field of magnetic resonance imaging technologies, and in particular, to a magnetic resonance blood vessel wall imaging method and apparatus.
  • stroke is mainly caused by ruptured plaque of atherosclerosis and thrombosis, which leads to occlusion of downstream blood vessels.
  • stroke is mainly caused by ischemic stroke, accounting for about 80%.
  • Ischemic stroke is mainly caused by lesions from the intracranial artery (46.6%) and the carotid artery (30%). Therefore, accurate identification of the carotid plaque structure and pathological characteristics is the key to early prevention and accurate treatment of stroke.
  • MR Vessel Wall Imaging is currently the only non-invasive, panoramic display of the head and neck combined with blood vessel walls and plaques. Magnetic resonance vascular wall imaging can non-invasively identify the components and inflammatory activities in the plaque, effectively evaluate the stability and vulnerability of plaque, and hope to bring new breakthroughs in the early warning and diagnosis of stroke.
  • SPACE itself also has motion-sensitive features, proton signals that can be scattered and moved, and are widely used for carotid vascular wall imaging.
  • SPACE's motion sensitivity is not strong, it is easy to produce blood flow artifacts at the carotid bifurcation. Therefore, other black blood modules need to be added to more effectively suppress blood flow signals.
  • Wang JN combined SPACE technology and DANTE (Delay Alternating with Nutation for Tailored Excitation) technology to suppress cerebrospinal fluid and blood flow signals to increase blood vessel wall and cerebrospinal fluid and lumen. Joint blood and cerebrospinal fluid suppression for intracranial vessel wall MRI, Magnetic resonance in medicine, 2015.
  • DANTE-prepared pulse trains a novel approach to motion-sensitized and motion-suppressed quantitative magnetic resonance imaging, Magnetic resonance in medicine, 2012, 5 issues, 68, p. ), the inhibition of carotid blood flow signals is significantly better than the previous black blood technology.
  • Simulation studies show that DANTE can attenuate the proton signal with motion speed greater than 0.2cm/s by 80%, and the flow velocity of cerebrospinal fluid is 0.1-2.0cm/s, which is just in the signal suppression range of DANTE.
  • DANTE can reduce the signal of cerebrospinal fluid, its inhibition of cerebrospinal fluid signal is not uniform.
  • DANTE is a motion-sensitive module that can reduce the signal intensity by more than 90% for tissues with a motion speed greater than 0.2 cm/s, but for tissues with motion speeds less than 0.2 cm/s. Basically unchanged. Cerebrospinal fluid is in a state of slow motion in the human brain, and its flow velocity is different in different regions. The velocity of motion is in the range of 0.1 to 2 cm/s (Velocity and pressure gradients of cerebrospinal fluid assessed with magnetic resonance imaging, J Neurosurg, 2014). , 120 issues in 1 period, page 218). Therefore, for cerebrospinal fluid in different regions of the brain, the signal suppression of DANTE is different, resulting in uneven signal of cerebrospinal fluid.
  • the present invention provides a magnetic resonance vascular wall imaging method and apparatus for uniformly and effectively suppressing signals of cerebrospinal fluid in a joint portion of a head and a neck, thereby improving imaging quality of a blood vessel wall.
  • the present invention provides a magnetic resonance vascular wall imaging method, comprising: applying a set radio frequency pulse sequence to an imaging region, wherein the set radio frequency pulse sequence comprises, in chronological order, a composite double band delay alternately Customizing the excitation occlusion DANTE pulse group, the variable flip angle chain of the three-dimensional fast spin echo SPACE, and a downward flipping RF pulse chain; acquiring magnetic resonance signals generated by the imaging region, and reconstructing the magnetic resonance signals according to the magnetic resonance signals Magnetic resonance image of the vessel wall in the imaging area.
  • the present invention also provides a magnetic resonance vascular wall imaging apparatus, comprising: a radio frequency pulse generating unit, configured to: apply a set radio frequency pulse sequence to an imaging area, wherein the set radio frequency pulse sequence is sequentially included in chronological order : a composite double-band delay alternation and a custom excitation nutretizing DANTE pulse group, a variable flip angle chain of a three-dimensional fast spin echo SPACE, and a downward flipping RF pulse chain; a magnetic resonance image generating unit for performing: acquiring the imaging region A magnetic resonance signal is generated and reconstructed from the magnetic resonance signal to obtain a magnetic resonance image of the blood vessel wall in the imaging region.
  • a radio frequency pulse generating unit configured to: apply a set radio frequency pulse sequence to an imaging area, wherein the set radio frequency pulse sequence is sequentially included in chronological order : a composite double-band delay alternation and a custom excitation nutretizing DANTE pulse group, a variable flip angle chain of a three-dimensional fast spin echo SPACE, and a downward flipping
  • the invention also provides a computer readable storage medium comprising computer readable instructions that, when executed, cause a processor to perform at least the above method.
  • the present invention also provides another apparatus comprising: a memory comprising computer readable instructions; and a processor, the method being performed when the computer readable instructions are executed.
  • the magnetic resonance blood vessel wall imaging method, device and computer readable storage medium provided by the invention can design a radio frequency pulse sequence and increase the downward flipping RF pulse chain after the variable flip angle chain of the three-dimensional fast spin echo SPACE. Effectively and uniformly further inhibit the cerebrospinal fluid signal of the whole brain, and make up for the shortcomings of DANTE technology that can not uniformly suppress the signal of cerebrospinal fluid. Based on the combination of existing DANTE and SPACE technology, the imaging quality of magnetic resonance vascular wall is further improved.
  • variable flip angle chain of the three-dimensional fast spin echo SPACE By adding a composite double-band delay alternation and a custom-actuated nutrient DANTE pulse group before the variable flip angle chain of the three-dimensional fast spin echo SPACE can preserve the advantages of DANTE, effectively suppress the blood flow signal, and contribute to the joint of the head and neck blood vessels. Wall imaging.
  • the signal to noise ratio of the magnetic resonance image can be further improved by optimizing the variable flip angle of SPACE.
  • FIG. 1 is a schematic flow chart of a magnetic resonance blood vessel wall imaging method according to an embodiment of the present invention
  • FIG. 2 is a schematic flow chart of a magnetic resonance blood vessel wall imaging method according to another embodiment of the present invention.
  • FIG. 3 is a schematic flow chart of a method for optimizing a variable flip angle chain of a SPACE according to an embodiment of the present invention
  • FIG. 4 is a schematic flow chart of a magnetic resonance blood vessel wall imaging method according to still another embodiment of the present invention.
  • FIG. 5 is a schematic flow chart of a magnetic resonance blood vessel wall imaging method according to still another embodiment of the present invention.
  • FIG. 6 is a schematic diagram of setting a radio frequency pulse sequence in an embodiment of the present invention.
  • FIG. 7 is a schematic diagram showing the evolution of a predetermined echo signal of SPACE in an embodiment of the present invention.
  • Figure 8 is a variable flip angle chain derived from the evolution of a given echo signal of SPACE shown in Figure 7;
  • Figure 9 is an actual signal evolution curve of different imaging tissues calculated from the variable flip angle chain shown in Figure 8.
  • FIG. 10 is a schematic diagram showing a comparison of results of cerebrospinal fluid signal simulation using a method according to an embodiment of the present invention and an existing SPACE;
  • FIG. 11 and FIG. 12 are magnetic resonance images of the same imaging region obtained by using the existing SPACE-DANTE and the method of the embodiment of the present invention, respectively;
  • FIG. 13 is a schematic diagram showing a comparison of evolution of a predetermined echo signal of SPACE when T1/T2 are respectively 940/100 ms and 1000/150 ms according to an embodiment of the present invention
  • Figure 14 is a comparison diagram of the variable flip angles derived from the evolution of the established echo signal shown in Figure 13;
  • Figure 15 is a schematic view showing a comparison of blood vessel wall signals calculated from the variable flip angle shown in Figure 14;
  • 16(a) and 16(b) are long-axis magnetic resonance images and cross-sectional magnetic resonance images of the blood vessel wall respectively obtained by using the variable flip angles at T1/T2 of FIG. 14 at 940/100 ms;
  • 17(a) and 17(b) are long-axis magnetic resonance images and cross-sectional magnetic resonance images of the blood vessel wall respectively obtained by using the variable flip angles at T1/T2 of FIG. 14 at 1000/150 ms;
  • FIG. 18 is a schematic structural view of a magnetic resonance blood vessel wall imaging apparatus according to an embodiment of the present invention.
  • FIG. 19 is a schematic structural view of a magnetic resonance blood vessel wall imaging apparatus according to another embodiment of the present invention.
  • 20 is a schematic structural diagram of a variable flip angle chain optimization unit according to an embodiment of the present invention.
  • FIG. 21 is a schematic structural view of a magnetic resonance blood vessel wall imaging apparatus according to still another embodiment of the present invention.
  • Figure 22 is a schematic structural view of a magnetic resonance blood vessel wall imaging apparatus according to still another embodiment of the present invention.
  • Figure 23 is a block diagram showing the structure of an apparatus in accordance with an embodiment of the present invention.
  • a magnetic resonance vascular wall imaging method which can suppress the cerebrospinal fluid signal more effectively and uniformly than the existing SPACE and DANTE technologies. At the same time, it can improve the signal to noise ratio of the organization.
  • the following embodiments illustrate the implementation and efficacy of the present invention by taking intracranial vascular wall magnetic resonance imaging, carotid vascular wall magnetic resonance imaging, and inhibition of cerebrospinal fluid signals as examples, and are not intended to limit the imaging of the present invention. Area and use.
  • FIG. 1 is a schematic flow chart of a magnetic resonance blood vessel wall imaging method according to an embodiment of the present invention. As shown in FIG. 1, the magnetic resonance blood vessel wall imaging method of the embodiment of the present invention may include the following steps:
  • S110 Applying a set radio frequency pulse sequence to the imaging area, wherein the set radio frequency pulse sequence comprises, in chronological order, a composite double band delay alternating and a custom excitation nutation DANTE pulse group, and a three-dimensional fast spin echo SPACE Variable flip angle chain and a downward flipping RF pulse chain;
  • S120 Acquire a magnetic resonance signal generated by the imaging region, and reconstruct a magnetic resonance image of a blood vessel wall in the imaging region according to the magnetic resonance signal.
  • the DANTE pulse group may be an existing DANTE pulse group, for example, a DANTE-prepared pulse trains: a novel approach to motion-sensitized and motion-suppressed quantitative magnetic Resonance imaging, Magnetic resonance in medicine, Volume 5, Volume 68, page 1423, 2012).
  • SPACE's variable flip angle chain can be the existing SPACE variable flip angle chain.
  • ISMRM Institute for Magnetic Resonance in Medicine
  • the DANTE pulse group may include a plurality of chronologically arranged pulse modules, each of the pulse modules including a rectangular pulse and a phase gradient, the rectangular pulse being a few A pulse of up to a dozen degrees, for example, may be a 2° to 20° pulse, such as a 10° pulse.
  • the amplitude of the scattered phase gradient can be set to the maximum value of the magnetic resonance system operation, for example, it can be set to 20 mT/m to 40 mT/m (mtes Tesla/m).
  • the duration of the pulse module can be about 1.5 ms, for example, 1 ms to 2 ms.
  • the number of repetitions of the pulse module can be adjusted depending on the application, and can be set, for example, from 50 to 500.
  • the DANTE pulse group can effectively inhibit blood flow artifacts at the carotid and intracranial arteries, increasing the contrast between the lumen of the blood vessel and the vessel wall.
  • Flip-down pulse can be an existing flip-down pulse, for example, Park et al. in "Optimized T1-weighted contrast for single-slab 3D turbo spin- Echo imaging with long echo trains: application to whole-brain imaging" (Magn Reson Med, 2007, 5 issues, 58 volumes, page 982) uses a flip-down RF pulse chain (Flip-down pulse).
  • the downward flipping radio frequency pulse chain may include, in chronological order, a first pulse, a second pulse, and a third pulse; wherein the first pulse and the second pulse
  • the time interval between pulses may be an echo pulse interval
  • the time interval between the second pulse and the third pulse may be half an echo pulse interval
  • the third pulse is a 90° pulse.
  • the echo pulse interval is preferably taken as small as possible, for example the minimum echo pulse interval allowed by the magnetic resonance system.
  • the first pulse is a 130° pulse and the second pulse is a 160° pulse. In other embodiments, the first pulse may be near 130° and the second pulse may be around 160°. For example, the first pulse is a 100° to 150° pulse and the second pulse is a 140° to 180° pulse.
  • the downward flip RF pulse chain in the embodiment of the present invention can be combined with "Optimized T1-weighted contrast for single-slab 3D turbo-echo imaging with long echo trains: application to whole-brain imaging" Magn Reson Med, 2007, 5 issues, 58 volumes, page 982)
  • the Flip-down pulse is the same, but the downward flipping RF pulse chain does not play a role in both.
  • the former is used to suppress cerebrospinal fluid signals, while the latter is used to increase the contrast of gray matter and white matter.
  • the set radio frequency pulse sequence may only include a DANTE burst, a variable flip angle chain of SPACE, and the above flipped RF pulse train, and the DANTE burst may be adjacent to the variable flip angle chain of SPACE, SPACE
  • the variable flip angle chain can generally be in close proximity to the flip-down RF pulse train described above.
  • the set RF pulse sequence may also include other pulses that are chronologically aligned with respect to the DANTE burst, the variable flip angle chain of SPACE, and the position of the flipped RF pulse train described above. Can be set as needed.
  • the set RF pulse sequence By causing the set RF pulse sequence to include, in chronological order, a composite double-band delay alternation and a custom excitation nutation DANTE pulse group, a three-dimensional fast spin echo SPACE variable flip angle chain, and a downward flip RF pulse chain, The RF pulse of the magnetic resonance imaging was designed.
  • the advantage of the DANTE burst can be preserved: the blood flow signal at the joint of the head and neck is suppressed.
  • the variable flip angle chain of SPACE in the set RF pulse sequence By setting the variable flip angle chain of SPACE in the set RF pulse sequence, the advantages of SPACE can be preserved: higher image acquisition efficiency, better contrast between blood vessel wall and cerebrospinal fluid, no need to prepare pulses to achieve black blood effect.
  • the magnetic resonance signals generated by the imaging region in the variable flip angle chain of SPACE and the downward flip RF pulse chain excitation are acquired.
  • the magnetic resonance signals described above can be acquired using existing or improved acquisition methods.
  • a magnetic resonance signal is obtained through a process such as radio frequency pulse, layer selection gradient, readout gradient, phase encoding, and the like.
  • Acquisition of Magnetic Resonance Signals Magnetic resonance images of the vessel walls in the imaged area can be obtained by, for example, a magnetic resonance image reconstruction algorithm.
  • a person skilled in the art can set a radio frequency pulse sequence or a prior art implementation according to an embodiment of the present invention, and therefore no further details are provided herein.
  • the magnetic resonance vascular wall imaging method of the embodiment of the present invention can be combined with the existing SPACE and DANTE technology by specifically involving a radio frequency pulse sequence including a DANTE pulse group, a variable flip angle chain of SPACE, and a downward flipping RF pulse chain. Further uniform suppression of cerebrospinal fluid signals on the basis of the invention can not only further improve the imaging quality of the intracranial vascular wall, but also help to image the blood vessel wall at the joint of the head and neck.
  • the magnetic resonance blood vessel wall imaging method shown in FIG. 1 may further include the steps before step S110, that is, before applying a set radio frequency pulse sequence to the imaging region.
  • variable flip angle chain of the SPACE can be optimized by adjusting one of the longitudinal magnetization vector relaxation time T1 and the transverse magnetization vector relaxation time T2 or both.
  • the longitudinal magnetization vector relaxation time T1 and/or the transverse magnetization vector relaxation time T2 can be adjusted to different values for different magnetic resonance system magnetic fields.
  • the transverse magnetization vector relaxation time T2 can be adjusted to be in the range of 150ms to 200ms, for example, the value of T2 can be set to 150ms, 165ms, 175ms; at the same time or alternatively,
  • the longitudinal magnetization vector relaxation time T1 is set in the range of 800 ms to 3000 ms, and for example, the value of T1 can be set to 1000 ms, 1500 ms, 2000 ms.
  • FIG. 3 is a schematic flow chart of a method for optimizing a variable flip angle chain of SPACE according to an embodiment of the present invention.
  • the method of optimizing the variable flip angle chain by adjusting the longitudinal magnetization vector relaxation time T1 and/or the transverse magnetization vector relaxation time T2 may include the following steps:
  • S133 Calculate an actual signal evolution curve of the plurality of imaging tissues according to the optimized variable flip angle, and determine whether to use the optimized variable flip angle as the variable flip angle according to the actual signal evolution curve. chain.
  • the established echo signal evolution curve of SPACE can be adjusted by adjusting one of the longitudinal magnetization vector relaxation time T1 and the transverse magnetization vector relaxation time T2 or both.
  • the predetermined echo signal evolution curve of SPACE can be adjusted for different magnetic resonance magnetic field adjustment longitudinal magnetization vector relaxation time T1 and/or transverse magnetization vector relaxation time T2.
  • the established echo signal evolution curve of SPACE can be adjusted for only one set of imaging tissue.
  • the magnetic resonance vascular wall imaging method is based on a 3T magnetic resonance system, and in the above step S131, the SPACE is adjusted by adjusting the longitudinal magnetization vector relaxation time T1 and/or the transverse magnetization vector relaxation time T2.
  • the method for the echo signal evolution curve may be: setting the longitudinal magnetization vector relaxation time T1 to 800ms to 3000ms and/or setting the transverse magnetization vector relaxation time T2 to 150ms to 200ms to set the SPACE's predetermined echo signal. Evolution curve.
  • the method for setting the evolution curve of the predetermined echo signal of SPACE by setting the longitudinal magnetization vector relaxation time T1 to 800 ms to 3000 ms and/or setting the transverse magnetization vector relaxation time T2 to 150 ms to 200 ms
  • the specific embodiment may be that the established echo signal evolution curve of SPACE is set by setting the longitudinal magnetization vector relaxation time T1 to 1000 ms and/or setting the transverse magnetization vector relaxation time T2 to 150 ms.
  • the plurality of imaging tissues may be a plurality of different tissues in the imaging region, or a plurality of different tissues in other regions, for example, tissues such as cerebrospinal fluid, gray matter, and white matter.
  • step S131 may be repeated to re-adjust the longitudinal magnetization vector relaxation time T1. And/or transversely magnetizing the vector relaxation time T2, and re-estimating the variable flip angle using step S132, and recalculating the actual signal of different imaging tissues according to the re-estimated variable flip angle by step S133 until the actual signal of the different imaging organization satisfies Set requirements.
  • variable flip angle chain of the existing SPACE is optimized by the above steps S131-S133, and the optimized flip angle chain of the SPACE is used for the above-mentioned set RF pulse sequence, and the blood vessel wall can be further improved. Contrast with cerebrospinal fluid enhances the imaging of existing SPACE.
  • the magnetic resonance blood vessel wall imaging method shown in FIG. 1 may further include the steps before step S110, that is, before applying a set radio frequency pulse sequence to the imaging region.
  • S140 Optimize the variable flip angle chain by adjusting a time ratio between the chronologically arranged first part, the second part and the third part in the SPACE's established echo signal evolution curve to improve magnetic resonance image quality.
  • the SPACE's established echo signal evolution curve may include the first part, the second part, and the third part, and has three parts.
  • the signal strength of the first portion decays exponentially with time as the initial attenuation portion; the signal strength of the second portion remains unchanged as the intermediate flat portion; the signal strength of the third portion continues to decrease over time as the final attenuation portion.
  • the first portion may be adjusted to have an echo of 2 to 5 SPACEs
  • the time of the second portion may be adjusted to account for 40% to 70% of the total time of the evolution curve of the predetermined echo signal. The rest of the time can be the time spent in the third part.
  • the different parts of the evolution of SPACE's established echo signals play different roles.
  • the initial attenuation portion can be used to drive the transverse magnetization vector to the steady state;
  • the echo signal of the intermediate flat portion can be used to fill the center of the K space, which is the most important part of the echo chain, and can directly determine the signal-to-noise ratio, contrast and individual of the image.
  • the point spread function of the pixel; the signal of the last attenuated part is mainly used to adjust the intensity of the intermediate signal, and the faster the attenuation, the larger the overall signal strength.
  • the time proportion of each part in the evolution curve of the predetermined echo signal of SPACE for example, adjusting the time of the first part to 2 to 5 SPACE echoes, adjusting the second part
  • the time occupies 40% to 70% of the total time of the evolution curve of the predetermined echo signal, and the evolution of the predetermined echo signal of the optimized SPACE can be obtained, and the variable flip angle chain of the SPACE can be optimized to improve the quality of the magnetic resonance image.
  • FIG. 5 is a schematic flow chart of a magnetic resonance blood vessel wall imaging method according to still another embodiment of the present invention.
  • the magnetic resonance vascular wall imaging method shown in FIG. 1 may further include steps before step S110, that is, before applying a set radio frequency pulse sequence to the imaging region.
  • the adjustment time TR of the adjustment SPACE is 800ms ⁇ 1200ms
  • the echo time TE of the adjustment SPACE is 5ms ⁇ 25ms
  • the echo chain length of the adjustment SPACE is 25 ⁇ 60.
  • the effect of the SPACE can be optimized, and the magnetic resonance image quality of the imaging region is further improved.
  • the set radio frequency pulse sequence includes a DANTE pulse train 340, a SPACE variable flip angle chain 320, and a downward flip RF pulse train 330.
  • the DANTE burst 340 can include a plurality of pulse modules, each of which can include a pulse a -X and a phase gradient G.
  • the pulse ⁇ -X can be a non-selected layer pulse, ⁇ -X ⁇ 10 °.
  • the amplitude of the phase gradient G can be set to the maximum value of the magnetic resonance system operation, and can be set, for example, to 20 mT/m to 40 mT/m.
  • the pulse module duration t D can be about 1.5 ms, for example, 1 ms to 2 ms.
  • the number of repetitions N of the pulse module can be adjusted depending on the application, and can be set, for example, from 50 to 500.
  • the DANTE pulse group 340 can refer to "T2-Weighted Intracranial Vessel Wall Imaging at 7 Tesla Using a DANTE-Prepared Variable Flip Angle Turbo Spin Echo Readout (DANTE-SPACE)" (Magnetic Resonance in Medicine, 2016), “Joint blood and cerebrospinal Fluid suppression for intracranial vessel wall MRI” (Magnetic resonance in medicine, 2015) or "DANTE-prepared pulse trains: a novel approach to motion-sensitized and motion-suppressed quantitative magnetic resonance imaging” (Magnetic resonance in medicine, 5 issues 68 DANTE Burst Design in Volume, page 1423, 2012).
  • the SPACE variable flip angle chain 320 may include pulses ⁇ 1, Y , pulses ⁇ 2, Y , pulses ⁇ 3, Y , ..., pulses ⁇ L-1, Y , pulses ⁇ L, Y , where L is greater than or An integer equal to 1, the pulse intervals being an echo pulse interval ESP.
  • the downward flipping of the RF pulse train 330 may include pulses ⁇ 1, Y , pulses ⁇ 2, Y and 90° pulses 90 3, X , wherein the interval between the pulses ⁇ 1, Y and the pulses ⁇ 2, Y is an echo pulse Interval ESP, pulse ⁇ 2, Y and 90° pulse 90 3, the interval between X is half echo pulse interval ESP/2.
  • FIG. 7 is a graph showing the evolution of a predetermined echo signal of SPACE in an embodiment of the present invention.
  • a predetermined echo signal evolution curve of SPACE is designed for a specific tissue, including a starting attenuation portion A, an intermediate flat portion B, and a final attenuation portion C.
  • the attenuation portion A can be 3 echo lengths
  • the intermediate flat portion B can occupy 65% of the time
  • the remaining portion is the last attenuation portion.
  • the longitudinal magnetization vector relaxation time T1 and the transverse magnetization vector relaxation time T2 can be 1000 ms and 150 ms, respectively.
  • Figure 8 is a diagram of a variable flip angle chain derived from the evolution of a given echo signal of SPACE shown in Figure 7.
  • Figure 9 is an actual signal evolution curve for different imaging tissues calculated from the variable flip angle chain shown in Figure 8.
  • the evolution of the predetermined echo signal of the SPACE designed in this embodiment can make the cerebrospinal fluid 301, the gray matter 302 and the white matter 303 be well separated, thereby illustrating the SPACE designed in this embodiment.
  • the evolution of the established echo signal optimizes the variable flip angle chain of SPACE.
  • FIG. 10 is a schematic diagram showing a comparison of results of cerebrospinal fluid signal simulation using the method of an embodiment of the present invention and the existing SPACE, respectively.
  • the intensity of the cerebrospinal fluid signal 312 produced by the combination of the inventive embodiment SPACE and the downward flipped RF pulse train is significantly reduced compared to the existing SPACE generated cerebrospinal fluid signal 311. This shows that The method of the embodiment of the present invention can effectively suppress the cerebrospinal fluid signal by increasing the downward flipping RF pulse chain after the variable flip angle chain of SPACE.
  • FIG. 11 and 12 are magnetic resonance images of the same imaging region obtained by the conventional SPACE-DANTE and the method of the embodiment of the present invention, respectively.
  • the magnetic resonance image shown in Fig. 11 was obtained according to the SPACE-DANTE method proposed by Wang JN et al. (Joint blood and cerebrospinal fluid suppression for intracranial vessel wall MRI, Magnetic resonance in medicine, 2015).
  • the (a) portion and the (c) portion are enlarged images of corresponding positions in the portion (b).
  • part (a) and part (c) are magnified images of corresponding positions in part (b).
  • Part (a) of Figure 11 and part (a) of Figure 12 show the inhibition of cerebrospinal fluid near the middle cerebral artery ring.
  • FIG. 13 is a schematic diagram showing the evolution of a predetermined echo signal of SPACE when T1/T2 is 940/100 ms and 1000/150 ms, respectively, according to an embodiment of the present invention.
  • the longitudinal magnetization vector relaxation time T1 and the transverse magnetization vector relaxation time T2 are set to 1000 ms and 150 ms, respectively, compared with the existing T1/T2 (commercial T1 and T2 are respectively 940ms and 100ms) can produce stronger signals.
  • Fig. 14 is a view showing the comparison of the variable flip angles derived from the evolution of the predetermined echo signal shown in Fig. 13. As shown in FIG.
  • a larger variable flip angle can be obtained by setting the longitudinal magnetization vector relaxation time T1 and the transverse magnetization vector relaxation time T2 to 1000 ms and 150 ms, respectively, as compared with the conventional T1/T2.
  • Fig. 15 is a view showing a comparison of blood vessel wall signals calculated based on the variable flip angle shown in Fig. 14.
  • the blood vessel wall signal intensity obtained by the optimized variable flip angle (T1/T2 is 1000/150 ms) is a blood vessel obtained by using the existing variable flip angle (T1/T2 is 940/100 ms).
  • the wall signal intensity is strong, and the signal intensity of the blood vessel wall is increased by 15.6%.
  • 16(a) and 16(b) are long-axis magnetic resonance images and cross-sectional magnetic resonance images of the blood vessel wall obtained by using the variable flip angles at T1/T2 of Fig. 14 at 940/100 ms, respectively.
  • the cross-sectional magnetic resonance image of the blood vessel wall shown in Fig. 16 (b) is a cross-sectional image of the blood vessel wall at the position of the broken line in Fig. 16 (a).
  • 17(a) and 17(b) are long-axis magnetic resonance images and cross-sectional magnetic resonance images of the blood vessel wall respectively obtained by using the variable flip angles at T1/T2 of Fig. 14 at 1000/150 ms.
  • Figure 17 (b) shows the blood
  • the cross-sectional magnetic resonance image of the tube wall is a cross-sectional image of the vessel wall at the position of the broken line in Fig. 17(a). Comparing Fig. 16 (a) with Fig. 17 (a), and comparing Fig. 16 (b) with Fig. 17 (b), it can be seen that compared with the variable flip angle when T1/T2 is 940/100 ms, The variable flip angle at T1/T2 of 1000/150 ms of the inventive embodiment is applied to the imaging of the blood vessel wall, and a stronger blood vessel wall signal can be obtained, so that the blood vessel wall in the imaging region can be more clearly distinguished.
  • the magnetic resonance blood vessel wall imaging method of the embodiment of the invention can effectively and uniformly further suppress the whole by effectively designing the radio frequency pulse sequence and increasing the downward flipping RF pulse chain after the variable flip angle chain of the three-dimensional fast spin echo SPACE.
  • the cerebrospinal fluid signal of the brain compensates for the shortcomings of the DANTE technique that can not uniformly suppress the signal of the cerebrospinal fluid. Based on the combination of the existing DANTE and SPACE technologies, the imaging quality of the magnetic resonance vessel wall is further improved.
  • variable flip angle chain of the three-dimensional fast spin echo SPACE By adding a composite double-band delay alternation and a custom-actuated nutrient DANTE pulse group before the variable flip angle chain of the three-dimensional fast spin echo SPACE can preserve the advantages of DANTE, effectively suppress the blood flow signal, and contribute to the joint of the head and neck blood vessels. Wall imaging. Further, optimizing SPACE by various methods, such as optimizing the variable flip angle chain of SPACE, better enhances the magnetic resonance imaging effect of the existing SPACE.
  • the embodiment of the present application also provides a magnetic resonance blood vessel wall imaging apparatus, as described in the following embodiments. Since the principle of solving the problem of the magnetic resonance vascular wall imaging apparatus is similar to that of the magnetic resonance vascular wall imaging method, the implementation of the magnetic resonance vascular wall imaging apparatus can be implemented by the implementation of the magnetic resonance vascular wall imaging method, and similar effects can be achieved. It will not be repeated here.
  • the term "unit” or “module” may implement a combination of software and/or hardware of a predetermined function.
  • Figure 18 is a schematic view showing the structure of a magnetic resonance blood vessel wall imaging apparatus according to an embodiment of the present invention.
  • the magnetic resonance blood vessel wall imaging apparatus of the embodiment of the present invention may include a radio frequency pulse generating unit 210 and a magnetic resonance image generating unit 220, which are connected to each other.
  • the radio frequency pulse generating unit 210 is configured to: apply a set radio frequency pulse sequence to the imaging area, wherein the set radio frequency pulse sequence comprises, in chronological order, a composite double band delay alternating and a custom excitation nutation DANTE pulse group
  • the three-dimensional fast spin echo SPACE has a variable flip angle chain and a downward flip RF pulse chain.
  • the magnetic resonance image generating unit 220 is configured to: acquire a magnetic resonance signal generated by the imaging region, and reconstruct a magnetic resonance image of the blood vessel wall in the imaging region according to the magnetic resonance signal.
  • the radio frequency pulse generating unit 210 is further configured to perform: the down-reversed radio frequency pulse chain includes a first pulse, a second pulse, and a third pulse in chronological order.
  • the first pulse and the The time interval between the second pulses is an echo pulse interval
  • the time interval between the second pulse and the third pulse is a half echo pulse interval
  • the third pulse is a 90 pulse.
  • the radio frequency pulse generating unit 210 is further configured to perform: the first pulse is a pulse of 100° to 150°, and the second pulse is a pulse of 140° to 180°.
  • the radio frequency pulse generating unit 210 is further configured to perform: the first pulse is a 130° pulse, and the second pulse is a 160° pulse.
  • the radio frequency pulse generating unit 210 is further configured to: the DANTE pulse group may include a plurality of chronological pulse modules, each of the pulse modules including a rectangular pulse and a phase gradient
  • the rectangular pulse may be a pulse of 2° to 20°.
  • the amplitude of the phase gradient can be set to the maximum value of the magnetic resonance system operation, for example, it can be set to 20 mT/m to 40 mT/m.
  • the duration of the pulse module may be about 1.5 ms, for example, 1 ms to 2 ms, for example, 1 ms to 2 ms.
  • the number of repetitions of the pulse module can be adjusted depending on the application, and can be set, for example, from 50 to 500.
  • Figure 19 is a schematic view showing the structure of a magnetic resonance blood vessel wall imaging apparatus according to another embodiment of the present invention.
  • the magnetic resonance blood vessel wall imaging apparatus shown in FIG. 18 may further include a variable flip angle chain optimization unit 230 connected to the radio frequency pulse generating unit 210.
  • variable flip angle chain optimization unit 230 is configured to: optimize the variable flip angle chain by adjusting the longitudinal magnetization vector relaxation time T1 and/or the transverse magnetization vector relaxation time T2 to improve magnetic resonance image quality.
  • variable flip angle chain optimization unit 230 may include: a predetermined echo signal evolution adjustment module 231, an optimized variable flip angle generation module 232, and a variable flip angle chain determination module 233. .
  • the predetermined echo signal evolution adjustment module 231 is configured to: adjust the evolution curve of the predetermined echo signal of the SPACE by adjusting the longitudinal magnetization vector relaxation time T1 and/or the transverse magnetization vector relaxation time T2.
  • the optimized flip angle generation module 232 is configured to: derive an optimized variable flip angle according to the established echo signal evolution curve.
  • variable flip angle chain determining module 233 is configured to: calculate an actual signal evolution curve of the plurality of imaging tissues according to the optimized variable flip angle, and determine, according to the actual signal evolution curve, whether the optimized A flip angle is used as the variable flip angle chain.
  • the device is based on a 3T magnetic resonance system
  • the predetermined echo signal evolution adjustment module 231 can include a magnetization vector relaxation time setting module.
  • a magnetization vector relaxation time setting module for performing: by setting the longitudinal magnetization vector relaxation time T1 to 800ms ⁇ 3000ms and / or set the transverse magnetization vector relaxation time T2 to 150ms ⁇ 200ms set SPACE's established echo signal evolution curve.
  • the magnetization vector relaxation time setting module 2311 includes a magnetization vector relaxation time determination module for performing: by setting the longitudinal magnetization vector relaxation time T1 to 1000 ms and/or The transverse magnetization vector relaxation time T2 is set to 150 ms to set the SPACE's established echo signal evolution curve.
  • Figure 21 is a schematic view showing the structure of a magnetic resonance blood vessel wall imaging apparatus according to still another embodiment of the present invention.
  • the magnetic resonance blood vessel wall imaging apparatus shown in FIG. 18 may further include: a predetermined echo signal evolution time ratio setting unit 240 connected to the radio frequency pulse generating unit 210.
  • the predetermined echo signal evolution time ratio setting unit 240 is configured to: optimize the time ratio between the first part, the second part, and the third part in the chronological order of the predetermined echo signal evolution curve of the SPACE Turn the corner chain to improve the quality of the magnetic resonance image.
  • the time for adjusting the first portion is an echo of 2 to 5 SPACEs, and the time for adjusting the second portion is 40% to 70% of the total time of the evolution curve of the predetermined echo signal.
  • FIG. 22 is a block diagram showing the structure of a magnetic resonance blood vessel wall imaging apparatus according to still another embodiment of the present invention.
  • the magnetic resonance blood vessel wall imaging apparatus shown in FIG. 18 may further include a SPACE parameter setting unit 250 connected to the radio frequency pulse generating unit 210.
  • the SPACE parameter setting unit 250 is configured to: optimize the magnetic resonance image by adjusting a plurality of parameters of the SPACE.
  • the adjustment time TR of the adjustment SPACE is 800ms ⁇ 1200ms
  • the echo time TE of the adjustment SPACE is 5ms ⁇ 25ms
  • the echo chain length of the adjustment SPACE is 25 ⁇ 60.
  • the magnetic resonance blood vessel wall imaging apparatus of the embodiment of the invention uniquely sets the radio frequency pulse sequence by the radio frequency pulse generating unit, and increases the downward flipping RF pulse chain after the variable flip angle chain of the three-dimensional fast spin echo SPACE, which can be effective and uniform It further inhibits the cerebrospinal fluid signal of the whole brain, and compensates for the shortcomings of DANTE technology that can not uniformly suppress the signal of cerebrospinal fluid. Based on the existing technology of DANTE and SPACE, the imaging quality of magnetic resonance vascular wall is further improved.
  • Adding composite double-band delay alternation and custom excitation nutretizing DANTE pulse group before the variable flip angle chain of three-dimensional fast spin echo SPACE by RF pulse generating unit can preserve the advantages of DANTE, effectively suppress blood flow signal, and help to Imaging of the vessel wall at the head and neck joint.
  • the SPACE is optimized by various units or modules, for example, by the established echo signal evolution time proportional setting unit, the variable flip angle chain optimization unit optimizes the variable flip angle chain of SPACE, and the SPACE parameter setting unit optimizes multiple SPACEs. Parameter, The magnetic resonance imaging effect of the existing SPACE is better improved.
  • Embodiments of the present invention also provide a computer readable storage medium comprising computer readable instructions that, when executed, cause a processor to perform at least one or more of the magnetic resonance vascular wall imaging methods of the various embodiments described above Steps.
  • FIG. 23 is a schematic structural diagram of the apparatus according to an embodiment of the invention.
  • an apparatus of an embodiment of the present invention may include a processor 410 and a memory 420, the memory 420 including computer readable instructions, and the processor 410 executing at least the magnetic resonance blood vessels of the above embodiments when the computer readable instructions are executed One or more steps in the wall imaging method.
  • the magnetic resonance blood vessel wall imaging method, device and computer readable storage medium increase the downward flipping of the three-dimensional fast spin echo SPACE after the variable flip angle chain by uniquely designing the radio frequency pulse sequence.
  • the RF pulse chain can effectively and uniformly inhibit the cerebrospinal fluid signal of the whole brain, and make up for the shortcomings of the DANTE technique that can not uniformly suppress the cerebrospinal fluid signal.
  • the magnetic resonance vascular wall imaging is further improved. quality.
  • variable flip angle chain of the three-dimensional fast spin echo SPACE By adding a composite double-band delay alternation and a custom-actuated nutrient DANTE pulse group before the variable flip angle chain of the three-dimensional fast spin echo SPACE can preserve the advantages of DANTE, effectively suppress the blood flow signal, and contribute to the joint of the head and neck blood vessels. Wall imaging. Further, optimizing SPACE by various methods, such as optimizing the variable flip angle chain of SPACE, better enhances the magnetic resonance imaging effect of the existing SPACE.
  • embodiments of the present invention can be provided as a method, system, or computer program product. Accordingly, the present invention may take the form of an entirely hardware embodiment, an entirely software embodiment, or a combination of software and hardware. Moreover, the invention can take the form of a computer program product embodied on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) including computer usable program code.
  • computer-usable storage media including but not limited to disk storage, CD-ROM, optical storage, etc.
  • the computer program instructions can also be stored in a computer readable memory that can direct a computer or other programmable data processing device to operate in a particular manner, such that the instructions stored in the computer readable memory produce an article of manufacture comprising the instruction device.
  • the apparatus implements the functions specified in one or more blocks of a flow or a flow and/or block diagram of the flowchart.
  • These computer program instructions can also be loaded onto a computer or other programmable data processing device such that a series of operational steps are performed on a computer or other programmable device to produce computer-implemented processing for execution on a computer or other programmable device.
  • the instructions provide steps for implementing the functions specified in one or more of the flow or in a block or blocks of a flow diagram.

Landscapes

  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • General Health & Medical Sciences (AREA)
  • Radiology & Medical Imaging (AREA)
  • Signal Processing (AREA)
  • Molecular Biology (AREA)
  • Public Health (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • High Energy & Nuclear Physics (AREA)
  • General Physics & Mathematics (AREA)
  • Condensed Matter Physics & Semiconductors (AREA)
  • Artificial Intelligence (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Physiology (AREA)
  • Theoretical Computer Science (AREA)
  • Psychiatry (AREA)
  • Neurology (AREA)
  • Vascular Medicine (AREA)
  • Cardiology (AREA)
  • Magnetic Resonance Imaging Apparatus (AREA)

Abstract

一种磁共振血管壁成像方法和设备，该方法包括：将一设定射频脉冲序列应用于成像区域，其中，设定射频脉冲序列按时间顺序依次包括：复合双带延迟交替与定制激励章动DANTE脉冲群、三维快速自旋回波SPACE的可变翻转角链及一向下翻转射频脉冲链（S110）；采集所述成像区域产生的磁共振信号，并根据磁共振信号重建得到所述成像区域中血管壁的磁共振图像（S120）。通过在三维快速自旋回波SPACE的可变翻转角链后增加向下翻转射频脉冲链，能够有效、均匀地进一步抑制全脑的脑脊液信号，同时利用DANTE脉冲群有助于头颈联合处的血管壁成像。

Description

磁共振血管壁成像方法和设备 技术领域
本发明涉及磁共振成像技术领域，尤其涉及一种磁共振血管壁成像方法和设备。
背景技术
脑卒中已成为中国死亡率和致残率最高的疾病。在中国14亿人口中，每年有1600万人因脑卒中死亡，死亡率为1.142％。脑卒中的医疗支出巨大，给中国带来沉重负担。2004年，中国脑卒中病人入院治疗的平均费用为6356元，为农乡居民年收入的2倍。目前，中国每年用于脑卒中病人治疗的费用达400亿人民币，是其他心血管疾病治疗费用总和的10倍。有鉴于此，早评估、早诊断、早预防脑卒中的病发尤为重要。
研究表明，脑卒中主要由动脉粥样硬化(atherosclerosis)易损斑块破裂，并形成血栓，导致下游血管闭塞所致。在中国，脑卒中以缺血性脑卒中为主，约占80％。缺血性脑卒中主要由来自颅内动脉(46.6％)和颈动脉(30％)的病变所致。所以，准确识别头颈动脉斑块结构和病理特性是早期预防和精确治疗脑卒中的关键。
磁共振血管壁成像(MR Vessel Wall Imaging)是目前唯一能够无创、全景显示头颈联合血管壁和斑块的手段。磁共振血管壁成像可以无创地精确识别斑块内的成分和炎症活动，有效评估斑块的稳定性和易损性，有望为脑中风的早期预警和诊断带来新的突破。
深圳先进技术研究院钟耀祖博士与约翰霍普金斯大学Wasserman团队合作，于2010年首次在国际医学磁共振学会(International Society for Magnetic Resonance in Medicine，ISMRM)年会上提出采用纵向磁化矢量弛豫时间T1加权的三维快速自旋回波技术(SPACE)实现颅内动脉三维血管壁成像(High Resolution 3D Intracranial Imaging at 3.0T，Proceedings of the 12th Annual Meeting of ISMRM，2010年，第2255页)。SPACE技术由快速自旋回波演化而来(Optimized three-dimensional fast-spin-echo MRI，Journal of magnetic resonance imaging，2014年，4期39卷，第745页)，其图像采集效率高，不需要准备脉冲也能实现黑血。钟耀祖博士采用T1加权对比以降低脑脊液信号，突出血管壁，再配合先进的32通道头部射频线圈提高信噪比，成功解决了进行颅内动脉三维磁共振成像中的多个关键问题。将该SPACE技术应用在西门子3T成像系统 上，进行T1权重颅内动脉三维磁共振血管壁成像，获得了0.5mm各向同性的高分辨三维黑血颅内动脉血管壁图像，扫描时间为10分钟。
SPACE本身还具有运动敏感的特性，能散相运动的质子的信号，被广泛用于颈动脉血管壁成像。但由于SPACE的运动敏感性不强，容易在颈动脉分叉处产生血流伪影，因此需要添加其他黑血模块来更有效地抑制血流信号。近期Wang JN将SPACE技术和DANTE(Delay Alternating with Nutation for Tailored Excitation，复合双带延迟交替与定制激励章动)技术相结合，同时抑制脑脊液和血流信号，以增加血管壁与脑脊液及管腔之间的对比度(Joint blood and cerebrospinal fluid suppression for intracranial vessel wall MRI，Magnetic resonance in medicine，2015年)。与单纯的SPACE技术相比，SPACE和DANTE相结合能够更好地对头颈联合部位的血管壁进行成像。DANTE是用于抑制运动质子信号的新方法(DANTE-prepared pulse trains:a novel approach to motion-sensitized and motion-suppressed quantitative magnetic resonance imaging，Magnetic resonance in medicine，2012年，5期68卷，第1423页)，对颈动脉血流信号的抑制效果明显优于以往的黑血技术。仿真研究表明，DANTE对运动速度大于0.2cm/s的质子信号的衰减可以达到80％，而脑脊液的流动速度为0.1～2.0cm/s，正好处于DANTE的信号抑制范围。
DANTE虽然能降低脑脊液信号，但其对脑脊液信号的抑制不均匀。DANTE导致脑脊液信号不均匀的原因在于：DANTE是一个运动敏感模块，其对运动速度大于0.2cm/s的组织可以降低90％以上的信号强度，但对运动速度小于0.2cm/s的组织其信号基本不变。脑脊液在人脑中是处于缓慢运动的状态，其流速在不同的区域是不同的，运动速度在0.1～2cm/s范围(Velocity and pressure gradients of cerebrospinal fluid assessed with magnetic resonance imaging，J Neurosurg，2014年，1期120卷，第218页)。因此，对于大脑不同区域内的脑脊液，DANTE的信号抑制程度不同，导致脑脊液信号不均匀。
脑脊液信号不均匀会大大影响对血管壁的精确分辨。因此，如何均匀有效地抑制脑脊液信号成为进一步提高血管壁成像质量的关键问题。
发明内容
本发明提供一种磁共振血管壁成像方法和设备，以均匀有效地抑制头颈联合部位的脑脊液的信号，从而提高血管壁的成像质量。
本发明提供一种磁共振血管壁成像方法，其中，包括：将一设定射频脉冲序列应用于成像区域，其中，所述设定射频脉冲序列按时间顺序依次包括：复合双带延迟交替与 定制激励章动DANTE脉冲群、三维快速自旋回波SPACE的可变翻转角链及一向下翻转射频脉冲链；采集所述成像区域产生的磁共振信号，并根据所述磁共振信号重建得到所述成像区域中血管壁的磁共振图像。
本发明还提供一种磁共振血管壁成像设备，包括：射频脉冲生成单元，用于执行：将一设定射频脉冲序列应用于成像区域，其中，所述设定射频脉冲序列按时间顺序依次包括：复合双带延迟交替与定制激励章动DANTE脉冲群、三维快速自旋回波SPACE的可变翻转角链及一向下翻转射频脉冲链；磁共振图像生成单元，用于执行：采集所述成像区域产生的磁共振信号，并根据所述磁共振信号重建得到所述成像区域中血管壁的磁共振图像。
本发明还提供一种包括计算机可读指令的计算机可读存储介质，所述计算机可读指令在被执行时使处理器至少执行上述方法。
本发明还提供另一种设备，包括：存储器，包括计算机可读指令；和处理器，在所述计算机可读指令被执行时执行上述方法。
本发明提供的磁共振血管壁成像方法、设备及计算机可读存储介质，通过独创地设计射频脉冲序列，在三维快速自旋回波SPACE的可变翻转角链后增加向下翻转射频脉冲链，能够有效、均匀地进一步抑制全脑的脑脊液信号，弥补了DANTE技术不能均匀抑制脑脊液信号的缺点，在现有DANTE和SPACE相结合的技术的基础上进一步提高了磁共振血管壁成像质量。通过在三维快速自旋回波SPACE的可变翻转角链之前增加复合双带延迟交替与定制激励章动DANTE脉冲群可以保留DANTE的优点，能够有效抑制血流信号，有助于对头颈联合处血管壁成像。在其他实施例中，通过优化SPACE的可变翻转角，能够进一步提高磁共振图像的信噪比。
附图说明
为了更清楚地说明本发明实施例或现有技术中的技术方案，下面将对实施例或现有技术描述中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图仅仅是本发明的一些实施例，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他的附图。在附图中：
图1是本发明实施例的磁共振血管壁成像方法的流程示意图；
图2是本发明另一实施例的磁共振血管壁成像方法的流程示意图；
图3是本发明一实施例中优化SPACE的可变翻转角链方法的流程示意图；
图4是本发明又一实施例的磁共振血管壁成像方法的流程示意图；
图5是本发明又一实施例的磁共振血管壁成像方法的流程示意图；
图6是本发明一实施例中设定射频脉冲序列示意图；
图7是本发明一实施例中SPACE的既定回波信号演化的曲线示意图；
图8是根据图7所示的SPACE的既定回波信号演化推算出的可变翻转角链；
图9是根据图8所示的可变翻转角链算出的不同成像组织的实际信号演化曲线；
图10是分别利用本发明一实施例的方法和现有SPACE进行脑脊液信号仿真的结果对比示意图；
图11和图12分别是利用现有SPACE-DANTE和本发明实施例方法得到的同一成像区域的磁共振图像；
图13是本发明一实施例中T1/T2分别为940/100ms和1000/150ms时SPACE的既定回波信号演化对比示意图；
图14是根据图13所示的既定回波信号演化推算得到的可变翻转角的对比示意图；
图15是根据图14所示的可变翻转角算出的血管壁信号对比示意图；
图16(a)和图16(b)是利用图14中T1/T2为940/100ms时的可变翻转角分别获得的血管壁的长轴磁共振图像和横断面磁共振图像；
图17(a)和图17(b)是利用图14中T1/T2为1000/150ms时的可变翻转角分别获得的血管壁的长轴磁共振图像和横断面磁共振图像；
图18是本发明实施例的磁共振血管壁成像设备的结构示意图；
图19是本发明另一实施例的磁共振血管壁成像设备的结构示意图；
图20是本发明一实施例中可变翻转角链优化单元的结构示意图；
图21是本发明又一实施例的磁共振血管壁成像设备的结构示意图；
图22是本发明再一实施例的磁共振血管壁成像设备的结构示意图；
图23是本发明一实施例的设备的结构示意图。
具体实施方式
为使本发明实施例的目的、技术方案和优点更加清楚明白，下面结合附图对本发明实施例做进一步详细说明。在此，本发明的示意性实施例及其说明用于解释本发明，但并不作为对本发明的限定。
基于现有SPACE和DANTE相结合的技术进行血管壁磁共振成像所遇到的问题，本 发明在重新设计用于磁共振成像的射频脉冲序列的基础上，提出了一种磁共振血管壁成像方法，与现有SPACE和DANTE相结合的技术相比能够更有效、更均匀地抑制脑脊液信号，同时能提高组织的信噪比。需要预先说明的是，下述各实施例以对颅内血管壁磁共振成像、颈动脉血管壁磁共振成像和抑制脑脊液信号为例说明本发明的实施与功效，并非用以限定本发明的成像区域和用途。本领域技术人员了解本发明各实施例的方法还可以用于对人体或动物其他部位的血管壁进行成像，同样地还可以抑制与脑脊液、颈动脉血流具有类似成像特性的其他体液信号，所以，本发明的保护范围当视权利要求的限定范围而定。
图1是本发明实施例的磁共振血管壁成像方法的流程示意图。如图1所示，本发明实施例的磁共振血管壁成像方法，可包括步骤：
S110：将一设定射频脉冲序列应用于成像区域，其中，所述设定射频脉冲序列按时间顺序依次包括：复合双带延迟交替与定制激励章动DANTE脉冲群、三维快速自旋回波SPACE的可变翻转角链及一向下翻转射频脉冲链；
S120：采集所述成像区域产生的磁共振信号，并根据所述磁共振信号重建得到所述成像区域中血管壁的磁共振图像。
在上述步骤S110中，DANTE脉冲群可以是现有的DANTE脉冲群，例如，Li LQ等人所采用的DANTE脉冲群(DANTE-prepared pulse trains:a novel approach to motion-sensitized and motion-suppressed quantitative magnetic resonance imaging，Magnetic resonance in medicine，5期68卷，第1423页，2012年)。SPACE的可变翻转角链可以是现有的SPACE的可变翻转角链，例如，深圳先进技术研究院钟耀祖博士与约翰霍普金斯大学Wasserman团队于2010年首次在国际医学磁共振学会(International Society for Magnetic Resonance in Medicine，ISMRM)年会上提出SPACE的可变翻转角链，或者可以是在现有的SPACE的可变翻转角链的基础上进行改进后的SPACE的可变翻转角链。
一些实施例中，在上述步骤S110中，所述DANTE脉冲群可包括多个按时间顺序排列的脉冲模块，每个所述脉冲模块包括一个矩形脉冲和一个散相梯度，所述矩形脉冲为几度至十几度的脉冲，例如可为2°～20°脉冲，例如为10°脉冲。散相梯度幅值大小可设为磁共振系统运行最大值，例如可设为20mT/m～40mT/m(毫特斯拉/米)。脉冲模块持续时间可为1.5ms左右，例如可为1ms～2ms。脉冲模块的重复次数可视应用情况进行调整，例如可设为50～500。DANTE脉冲群能有效抑制颈动脉和颅内动脉处的血流伪影，增加血管腔与血管壁之间的对比度。
向下翻转射频脉冲链(Flip-down pulse)可以是现有的向下翻转射频脉冲链(Flip-down pulse)，例如，Park等人在“Optimized T1-weighted contrast for single-slab 3D turbo spin-echo imaging with long echo trains:application to whole-brain imaging”(Magn Reson Med，2007年，5期58卷，第982页)中采用的向下翻转射频脉冲链(Flip-down pulse)。
一些实施例中，在上述步骤S110中，所述向下翻转射频脉冲链按时间顺序依次可包括：第一脉冲、第二脉冲及第三脉冲；其中，所述第一脉冲和所述第二脉冲之间的时间间隔可为一个回波脉冲间隔，所述第二脉冲和所述第三脉冲之间的时间间隔可为半个回波脉冲间隔，所述第三脉冲为90°脉冲。回波脉冲间隔较佳地取尽可能小的值，例如可为磁共振系统允许的最小回波脉冲间隔。
一些实施例中，所述第一脉冲为130°脉冲，所述第二脉冲为160°脉冲。其他实施例中，第一脉冲可以在130°附近，第二脉冲可以在160°附近。例如，所述第一脉冲为100°～150°脉冲，所述第二脉冲为140°～180°脉冲。
值得一提的是，虽然本发明实施例中的向下翻转射频脉冲链可以与“Optimized T1-weighted contrast for single-slab 3D turbo spin-echo imaging with long echo trains:application to whole-brain imaging”(Magn Reson Med，2007年，5期58卷，第982页)中的向下翻转射频脉冲链(Flip-down pulse)相同，但该向下翻转射频脉冲链在二者中所起的作用并不相同，前者是用于抑制脑脊液信号，而后者是用于增加灰质和白质的对比度。
一些实施例中，所述设定射频脉冲序列可以仅包含DANTE脉冲群、SPACE的可变翻转角链和上述向下翻转射频脉冲链，DANTE脉冲群可与SPACE的可变翻转角链紧邻，SPACE的可变翻转角链一般可与上述向下翻转射频脉冲链紧邻。另一些实施例中，所述设定射频脉冲序列还可以同时包含其他脉冲，该其他脉冲在时间顺序上相对于DANTE脉冲群、SPACE的可变翻转角链和上述向下翻转射频脉冲链的位置可以根据需要设定。
通过使所述设定射频脉冲序列按时间顺序依次包括复合双带延迟交替与定制激励章动DANTE脉冲群、三维快速自旋回波SPACE的可变翻转角链和一向下翻转射频脉冲链，对用于磁共振成像的射频脉冲进行设计。通过在设定射频脉冲序列中设置DANTE脉冲群可以保留DANTE脉冲群的优点：抑制头颈联合部位的血流信号。通过在设定射频脉冲序列中设置SPACE的可变翻转角链可以保留SPACE的优点：较高的图像采集效率，较好地血管壁与脑脊液间的对比度，不需要准备脉冲实现黑血效果等。再通过在 SPACE的可变翻转角链后面增加向下翻转射频脉冲链可以进一步均匀抑制脑脊液信号，可以弥补DANTE脉冲群对脑脊液信号抑制不均匀的缺点，提高脑脊液和血管壁之间的对比度和血管壁的辨识度。如此一来，不仅能够提高颅内血管壁成像，还有利于对头颈联合部位的血管壁成像。
在上述步骤S120中，将上述设定射频脉冲序列应用于成像区域后，采集所述成像区域先后在SPACE的可变翻转角链和向下翻转射频脉冲链激励下产生的磁共振信号。上述磁共振信号可以利用现有的或改进的采集方法进行采集。例如，经过射频脉冲、选层梯度、读出梯度、相位编码等过程实现得到磁共振信号。采集得到磁共振信号通过例如磁共振图像重建算法可以得到成像区域中血管壁的磁共振图像。对于该步骤，本领域技术人员可以根据本发明实施例设定射频脉冲序列或现有技术实现，故在此不再赘述。
本发明实施例的磁共振血管壁成像方法通过特别涉及射频脉冲序列，使其包含DANTE脉冲群、SPACE的可变翻转角链和向下翻转射频脉冲链，可以在现有SPACE和DANTE相结合技术基础上进一步均匀抑制脑脊液信号，从而不仅能够进一步提高颅内血管壁成像质量，还有助于对头颈联合处的血管壁成像。
图2是本发明另一实施例的磁共振血管壁成像方法的流程示意图。如图2所示，图1所示的磁共振血管壁成像方法，在步骤S110之前，即在将一设定射频脉冲序列应用于成像区域之前，还可包括步骤：
S130：通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2优化所述可变翻转角链，以提高磁共振图像质量。
在上述步骤S130中，可以通过调整纵向磁化矢量弛豫时间T1和横向磁化矢量弛豫时间T2中的一者或同时调整两者优化SPACE的可变翻转角链。较佳实施例中，可以针对不同的磁共振系统磁场将纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2调整为不同的值。一个实施例中，针对3T磁共振系统，可以将横向磁化矢量弛豫时间T2调整至150ms～200ms范围内，例如可将T2的值设置为150ms、165ms、175ms；同时或者可选地，可将纵向磁化矢量弛豫时间T1设置为800ms～3000ms范围内，例如可将T1的值设置为1000ms、1500ms、2000ms。
图3是本发明一实施例中优化SPACE的可变翻转角链方法的流程示意图。如图3所示，在上述步骤S130中，通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2优化所述可变翻转角链的方法，可包括步骤：
S131：通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2调整 SPACE的既定回波信号演化曲线；
S132：根据所述既定回波信号演化曲线推算得到优化的可变翻转角；
S133：根据所述优化的可变翻转角计算得到多种成像组织的实际信号演化曲线，并根据所述实际信号演化曲线判断是否将所述优化的可变翻转角用作所述可变翻转角链。
在上述步骤S131中，可以通过调整纵向磁化矢量弛豫时间T1和横向磁化矢量弛豫时间T2中的一者或同时调整两者调整SPACE的既定回波信号演化曲线。较佳地，可以针对不同的磁共振磁场调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2调整SPACE的既定回波信号演化曲线。一个实施例中，可仅针对一种设定成像组织调整SPACE的既定回波信号演化曲线。
一些实施例中，所述磁共振血管壁成像方法是基于3T磁共振系统的，在上述步骤S131中，通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2调整SPACE的既定回波信号演化曲线的方法具体实施方式可为：通过将纵向磁化矢量弛豫时间T1设置为800ms～3000ms和/或将横向磁化矢量弛豫时间T2设置为150ms～200ms设置SPACE的既定回波信号演化曲线。
一些实施例中，上述步骤中，通过将纵向磁化矢量弛豫时间T1设置为800ms～3000ms和/或将横向磁化矢量弛豫时间T2设置为150ms～200ms设置SPACE的既定回波信号演化曲线的方法具体实施方式可为：通过将纵向磁化矢量弛豫时间T1设置为1000ms和/或将横向磁化矢量弛豫时间T2设置为150ms设置SPACE的既定回波信号演化曲线。
在上述步骤S133中，所述的多种成像组织可以是上述成像区域中的多种不同组织，或者是其他区域的多种不同组织，例如可以是脑脊髓液、灰质、白质等组织。得到多种成像组织的实际信号演化曲线后，可以根据不同组织的实际信号演化曲线的区分程度决定是否将所述优化的可变翻转角用作SPACE的可变翻转角链。
一个实施例中，若不同组织的实际信号演化曲线不满足设定要求(例如，不同成像组织间的实际信号差值不满足设定范围)，可以重复步骤S131重新调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2，并利用步骤S132重新推算可变翻转角，利用步骤S133根据重新推算可变翻转角重新算出不同成像组织的实际信号，直到不同成像组织的实际信号满足设定要求。
本实施例中，通过上述步骤S131～S133优化现有的SPACE的可变翻转角链，并将优化后的SPACE的可变翻转角链用于上述设定射频脉冲序列，可以进一步提高血管壁 与脑脊液的对比度，增强了现有SPACE的成像效果。
图4是本发明又一实施例的磁共振血管壁成像方法的流程示意图。如图4所示，图1所示的磁共振血管壁成像方法，在步骤S110之前，即在将一设定射频脉冲序列应用于成像区域之前，还可包括步骤：
S140：通过调整SPACE的既定回波信号演化曲线中按时间顺序排列的第一部分、第二部分及第三部分之间的时间比例优化所述可变翻转角链，以提高磁共振图像质量。
一般SPACE的既定回波信号演化曲线可以包括上述第一部分、第二部分及第三部分，共三部分。通常，第一部分的信号强度随时间指数衰减，为起始衰减部分；第二部分的信号强度保持不变，为中间平坦部分；第三部分的信号强度随时间继续下降，为最后衰减部分。
一些实施例中，可以调整所述第一部分的时间为2～5个SPACE的回波，调整所述第二部分的时间占所述既定回波信号演化曲线的总时间的40％～70％。其余时间可以为第三部分所占时间。
SPACE的既定回波信号演化中的不同部分所起的作用各不相同。起始衰减部分可用于驱使横向磁化矢量到达稳态；中间平坦部分的回波信号可用于填充K空间中心，是回波链中最主要的部分，可直接决定图像的信噪比、对比度和单个像素的点扩散函数；最后衰减部分的信号主要用于调节中间信号的强度，其衰减越快整体信号强度越大。
本实施例中，通过合理调整SPACE的既定回波信号演化曲线中各部分的时间占比，例如，调整所述第一部分的时间为2～5个SPACE的回波，调整所述第二部分的时间占所述既定回波信号演化曲线的总时间的40％～70％，可以得到优化的SPACE的既定回波信号演化，进而可以优化SPACE的可变翻转角链以提高磁共振图像质量。
图5是本发明又一实施例的磁共振血管壁成像方法的流程示意图。如图5所示，图1所示的磁共振血管壁成像方法，在步骤S110之前，即在将一设定射频脉冲序列应用于成像区域之前，还可包括步骤：
S150：通过调整SPACE的多个参数优化磁共振图像。
其中，调整SPACE的重复时间TR为800ms～1200ms，调整SPACE的回波时间TE为5ms～25ms，以及调整SPACE的回波链长为25～60。
本实施例中，通过调节SPACE中的重复时间TR、回波时间TE及回波链长至各自的合理范围，可以优化SPACE的效果，进一步提高成像区域的磁共振图像质量。
图6是本发明一实施例中设定射频脉冲序列示意图。如图6所示，上述设定射频脉 冲序列包括DANTE脉冲群340、SPACE可变翻转角链320和向下翻转射频脉冲链330。DANTE脉冲群340可包括多个脉冲模块，每个脉冲模块可包括脉冲α-X和散相梯度G。该脉冲α-X可为非选层脉冲，α-X≈10°。散相梯度G的幅值大小可设为磁共振系统运行最大值，例如可设为20mT/m～40mT/m。脉冲模块持续时间tD可为1.5ms左右，例如可为1ms～2ms。脉冲模块的重复次数N可视应用情况进行调整，例如可设为50～500。DANTE脉冲群340可参照“T2-Weighted Intracranial Vessel Wall Imaging at 7 Tesla Using a DANTE-Prepared Variable Flip Angle Turbo Spin Echo Readout(DANTE-SPACE)”(Magnetic Resonance in Medicine，2016年)、“Joint blood and cerebrospinal fluid suppression for intracranial vessel wall MRI”(Magnetic resonance in medicine，2015年)或“DANTE-prepared pulse trains:a novel approach to motion-sensitized and motion-suppressed quantitative magnetic resonance imaging”(Magnetic resonance in medicine，5期68卷，第1423页，2012年)中的DANTE脉冲群设计。SPACE可变翻转角链320可包括脉冲α1,Y、脉冲α2,Y、脉冲α3,Y、……、脉冲αL-1,Y、脉冲αL,Y，其中，L为大于或等于1的整数，该些脉冲间隔为一个回波脉冲间隔ESP。向下翻转射频脉冲链330可包括脉冲β1,Y、脉冲β2,Y及90°脉冲903,X，其中，脉冲β1,Y和脉冲β2,Y之间间隔为一个回波脉冲间隔ESP，脉冲β2,Y和90°脉冲903,X之间间隔为半个回波脉冲间隔ESP/2。
图7是本发明一实施例中SPACE的既定回波信号演化的曲线示意图。如图7所示，针对一特定组织设计SPACE的既定回波信号演化曲线，包括起始衰减部分A、中间平坦部分B及最后衰减部分C三部分。其中，衰减部分A可为3个回波长度，中间平坦部分B所占时间比例可为65％，剩余部分时间为最后衰减部分三部分。基于3T磁共振系统，纵向磁化矢量弛豫时间T1和横向磁化矢量弛豫时间T2可分别为1000ms和150ms。图8是根据图7所示的SPACE的既定回波信号演化推算出的可变翻转角链。图9是根据图8所示的可变翻转角链算出的不同成像组织的实际信号演化曲线。如图9所示，本实施例中所设计的SPACE的既定回波信号演化能够使得脑脊髓液301、灰质302及白质303两两之间很好地区分开，由此说明本实施例设计的SPACE的既定回波信号演化优化了SPACE的可变翻转角链。
图10是分别利用本发明一实施例的方法和现有SPACE进行脑脊液信号仿真的结果对比示意图。如图10所示，与现有SPACE产生的脑脊液信号311相比，本发明实施例SPACE和向下翻转射频脉冲链结合产生的脑脊液信号312的强度显著降低。由此可见， 本发明实施例的方法通过在SPACE的可变翻转角链后增加向下翻转射频脉冲链，的确能够起到抑制脑脊液信号的作用。
图11和图12分别是利用现有SPACE-DANTE和本发明实施例方法得到的同一成像区域的磁共振图像。图11所示的磁共振图像是根据Wang JN等人提出的SPACE-DANTE方法获得(Joint blood and cerebrospinal fluid suppression for intracranial vessel wall MRI，Magnetic resonance in medicine，2015年)。如图11所示，其中的(a)部分和(c)部分为(b)部分中相应位置的放大图像。如图12所示，其中的(a)部分和(c)部分为(b)部分中相应位置的放大图像。图11中(a)部分和图12中(a)部分显示抑制大脑中动脉环附近的脑脊液情况，对比图11中(a)部分和图12中(a)部分灰度，可以看出，本发明实施例的方法采用DANTE脉冲群、SPACE和向下翻转射频脉冲链相结合的方法能够更均匀、更有效地抑制大脑中动脉环附近的脑脊液信号。图11中(c)部分和图12中(c)部分显示抑制大脑中动脉M2段的脑脊液的情况，对比图11中(c)部分和图12中(c)部分灰度，可以看出，本发明实施例的方法能够更均匀、更有效地抑制动脉M2段的脑脊液信号，颅内血管壁的外边界显示的更清楚。由此可见，与现有技术相比，本发明实施例的方法能够更均匀地抑制全脑的脑脊液信号，清楚的显示颅内血管壁的外边界。
图13是本发明一实施例中T1/T2分别为940/100ms和1000/150ms时SPACE的既定回波信号演化对比示意图。如图13所示，基于3T磁共振成像系统，将纵向磁化矢量弛豫时间T1和横向磁化矢量弛豫时间T2分别设置为1000ms和150ms比现有的T1/T2(商用的T1和T2分别为940ms和100ms)可以产生更强的信号。图14是根据图13所示的既定回波信号演化推算得到的可变翻转角的对比示意图。如图14所示，与现有的T1/T2相比，将纵向磁化矢量弛豫时间T1和横向磁化矢量弛豫时间T2分别设置为1000ms和150ms后可以获得更大的可变翻转角。图15是根据图14所示的可变翻转角算出的血管壁信号对比示意图。如图15所示，由优化后的可变翻转角(T1/T2为1000/150ms)得到的血管壁信号强度比利用现有的可变翻转角(T1/T2为940/100ms)得到的血管壁信号强度强，血管壁信号强度提高了15.6％。图16(a)和图16(b)是利用图14中T1/T2为940/100ms时的可变翻转角分别获得的血管壁的长轴磁共振图像和横断面磁共振图像。图16(b)所示血管壁横断面磁共振图像为图16(a)中虚线位置处的血管壁的横断面图像。图17(a)和图17(b)是利用图14中T1/T2为1000/150ms时的可变翻转角分别获得的血管壁的长轴磁共振图像和横断面磁共振图像。图17(b)所示血 管壁横断面磁共振图像为图17(a)中虚线位置处的血管壁的横断面图像。对比图16(a)和图17(a)，及对比图16(b)和图17(b)，可以看出，与T1/T2为940/100ms时的可变翻转角相比，将本发明实施例的T1/T2为1000/150ms时的可变翻转角应用于血管壁成像，可以获得更强的血管壁信号，从而可以更清楚地分辨出成像区域中的血管壁。
本发明实施例的磁共振血管壁成像方法，通过独创地设计射频脉冲序列，在三维快速自旋回波SPACE的可变翻转角链后增加向下翻转射频脉冲链，能够有效、均匀地进一步抑制全脑的脑脊液信号，弥补了DANTE技术不能均匀抑制脑脊液信号的缺点，在现有DANTE和SPACE相结合的技术的基础上进一步提高了磁共振血管壁成像质量。通过在三维快速自旋回波SPACE的可变翻转角链之前增加复合双带延迟交替与定制激励章动DANTE脉冲群可以保留DANTE的优点，能够有效抑制血流信号，有助于对头颈联合处血管壁成像。进一步，通过各种不同方法优化SPACE，例如优化SPACE的可变翻转角链，更佳地提升了现有SPACE的磁共振成像效果。
基于与图1所示的磁共振血管壁成像方法相同的发明构思，本申请实施例还提供了一种磁共振血管壁成像设备，如下面实施例所述。由于该磁共振血管壁成像设备解决问题的原理与磁共振血管壁成像方法相似，因此该磁共振血管壁成像设备的实施可以参见磁共振血管壁成像方法的实施，且可达到相似的功效，重复之处不再赘述。以下所使用的，术语“单元”或者“模块”可以实现预定功能的软件和/或硬件的组合。尽管以下实施例所描述的系统较佳地以软件来实现，但是硬件，或者软件和硬件的组合的实现也是可能并被构想的。
图18是本发明实施例的磁共振血管壁成像设备的结构示意图。如图18所示，本发明实施例的磁共振血管壁成像设备，可包括：射频脉冲生成单元210和磁共振图像生成单元220，二者相互连接。
射频脉冲生成单元210，用于执行：将一设定射频脉冲序列应用于成像区域，其中，所述设定射频脉冲序列按时间顺序依次包括：复合双带延迟交替与定制激励章动DANTE脉冲群、三维快速自旋回波SPACE的可变翻转角链及一向下翻转射频脉冲链。
磁共振图像生成单元220，用于执行：采集所述成像区域产生的磁共振信号，并根据所述磁共振信号重建得到所述成像区域中血管壁的磁共振图像。
一些实施例中，所述射频脉冲生成单元210，还可用于执行：所述向下翻转射频脉冲链按时间顺序依次包括：第一脉冲、第二脉冲及第三脉冲。其中，所述第一脉冲和所 述第二脉冲之间的时间间隔为一个回波脉冲间隔，所述第二脉冲和所述第三脉冲之间的时间间隔为半个回波脉冲间隔，所述第三脉冲为90°脉冲。
一些实施例中，所述射频脉冲生成单元210，还可用于执行：所述第一脉冲为100°～150°脉冲，所述第二脉冲为140°～180°脉冲。
一些实施例中，所述射频脉冲生成单元210，还可用于执行：所述第一脉冲为130°脉冲，所述第二脉冲为160°脉冲。
一些实施例中，所述射频脉冲生成单元210，还可用于执行：所述DANTE脉冲群可包括多个按时间顺序排列的脉冲模块，每个所述脉冲模块包括一个矩形脉冲和一个散相梯度，所述矩形脉冲可为2°～20°脉冲。散相梯度的幅值大小可设为磁共振系统运行最大值，例如可设为20mT/m～40mT/m。脉冲模块的持续时间可为1.5ms左右，例如可为1ms～2ms，例如可为1ms～2ms。脉冲模块的重复次数可视应用情况进行调整，例如可设为50～500。
图19是本发明另一实施例的磁共振血管壁成像设备的结构示意图。如图19所示，图18所示的磁共振血管壁成像设备，还可包括：可变翻转角链优化单元230，与射频脉冲生成单元210连接。
可变翻转角链优化单元230，用于执行：通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2优化所述可变翻转角链，以提高磁共振图像质量。
图20是本发明一实施例中可变翻转角链优化单元的结构示意图。如图20所示，可变翻转角链优化单元230，可包括：既定回波信号演化调整模块231、优化可变翻转角生成模块232及可变翻转角链确定模块233，上述各模块顺序连接。
既定回波信号演化调整模块231，用于执行：通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2调整SPACE的既定回波信号演化曲线。
优化可变翻转角生成模块232，用于执行：根据所述既定回波信号演化曲线推算得到优化的可变翻转角。
可变翻转角链确定模块233，用于执行：根据所述优化的可变翻转角计算得到多种成像组织的实际信号演化曲线，并根据所述实际信号演化曲线判断是否将所述优化的可变翻转角用作所述可变翻转角链。
一些实施例中，所述设备是基于3T磁共振系统，所述既定回波信号演化调整模块231，可包括：磁化矢量弛豫时间设置模块。
磁化矢量弛豫时间设置模块，用于执行：通过将纵向磁化矢量弛豫时间T1设置为 800ms～3000ms和/或将横向磁化矢量弛豫时间T2设置为150ms～200ms设置SPACE的既定回波信号演化曲线。
一些实施例中，磁化矢量弛豫时间设置模块2311包括磁化矢量弛豫时间确定模块，该磁化矢量弛豫时间确定模块用于执行：通过将纵向磁化矢量弛豫时间T1设置为1000ms和/或将横向磁化矢量弛豫时间T2设置为150ms设置SPACE的既定回波信号演化曲线。
图21是本发明又一实施例的磁共振血管壁成像设备的结构示意图。如图21所示，图18所示的磁共振血管壁成像设备，还可包括：既定回波信号演化时间比例设置单元240，与射频脉冲生成单元210连接。
既定回波信号演化时间比例设置单元240，用于执行：通过调整SPACE的既定回波信号演化曲线中按时间顺序排列的第一部分、第二部分及第三部分之间的时间比例优化所述可变翻转角链，以提高磁共振图像质量。
其中，调整所述第一部分的时间为2～5个SPACE的回波，调整所述第二部分的时间占所述既定回波信号演化曲线的总时间的40％～70％。
图22是本发明再一实施例的磁共振血管壁成像设备的结构示意图。如图22所示，图18所示的磁共振血管壁成像设备，还可包括：SPACE参数设置单元250，与射频脉冲生成单元210连接。
SPACE参数设置单元250，用于执行：通过调整SPACE的多个参数优化磁共振图像。
其中，调整SPACE的重复时间TR为800ms～1200ms，调整SPACE的回波时间TE为5ms～25ms，以及调整SPACE的回波链长为25～60。
本发明实施例的磁共振血管壁成像设备，通过射频脉冲生成单元独创地设置射频脉冲序列，在三维快速自旋回波SPACE的可变翻转角链后增加向下翻转射频脉冲链，能够有效、均匀地进一步抑制全脑的脑脊液信号，弥补了DANTE技术不能均匀抑制脑脊液信号的缺点，在现有DANTE和SPACE相结合的技术的基础上进一步提高了磁共振血管壁成像质量。通过射频脉冲生成单元在三维快速自旋回波SPACE的可变翻转角链之前增加复合双带延迟交替与定制激励章动DANTE脉冲群可以保留DANTE的优点，能够有效抑制血流信号，有助于对头颈联合处血管壁成像。进一步，通过各种不同单元或模块优化SPACE，例如通过既定回波信号演化时间比例设置单元、可变翻转角链优化单元优化SPACE的可变翻转角链，通过SPACE参数设置单元优化SPACE的多个参数， 更佳地提升了现有SPACE的磁共振成像效果。
本发明实施例还提供了一种包括计算机可读指令的计算机可读存储介质，该计算机可读指令在被执行时使处理器至少执行上述各实施例的磁共振血管壁成像方法中一个或多个步骤。
本发明实施例还提供了一种设备，图23是本发明一实施例的设备的结构示意图。如图23所示，本发明实施例的设备可包括处理器410和存储器420，存储器420包括计算机可读指令，处理器410在计算机可读指令被执行时至少执行上述各实施例的磁共振血管壁成像方法中一个或多个步骤。
综上所述，本发明提供的磁共振血管壁成像方法、设备及计算机可读存储介质，通过独创地设计射频脉冲序列，在三维快速自旋回波SPACE的可变翻转角链后增加向下翻转射频脉冲链，能够有效、均匀地进一步抑制全脑的脑脊液信号，弥补了DANTE技术不能均匀抑制脑脊液信号的缺点，在现有DANTE和SPACE相结合的技术的基础上进一步提高了磁共振血管壁成像质量。通过在三维快速自旋回波SPACE的可变翻转角链之前增加复合双带延迟交替与定制激励章动DANTE脉冲群可以保留DANTE的优点，能够有效抑制血流信号，有助于对头颈联合处血管壁成像。进一步，通过各种不同方法优化SPACE，例如优化SPACE的可变翻转角链，更佳地提升了现有SPACE的磁共振成像效果。
在本说明书的描述中，参考术语“一个实施例”、“一个具体实施例”、“一些实施例”、“例如”、“示例”、“具体示例”、或“一些示例”等的描述意指结合该实施例或示例描述的具体特征、结构、材料或者特点包含于本发明的至少一个实施例或示例中。在本说明书中，对上述术语的示意性表述不一定指的是相同的实施例或示例。而且，描述的具体特征、结构、材料或者特点可以在任何的一个或多个实施例或示例中以合适的方式结合。各实施例中涉及的步骤顺序用于示意性说明本发明的实施，其中的步骤顺序不作限定，可根据需要作适当调整。
本领域内的技术人员应明白，本发明的实施例可提供为方法、系统、或计算机程序产品。因此，本发明可采用完全硬件实施例、完全软件实施例、或结合软件和硬件方面的实施例的形式。而且，本发明可采用在一个或多个其中包含有计算机可用程序代码的计算机可用存储介质(包括但不限于磁盘存储器、CD-ROM、光学存储器等)上实施的计算机程序产品的形式。
本发明是参照根据本发明实施例的方法、设备(系统)、和计算机程序产品的流程图和/或方框图来描述的。应理解可由计算机程序指令实现流程图和/或方框图中的每一流程和/或方框、以及流程图和/或方框图中的流程和/或方框的结合。可提供这些计算机程序指令到通用计算机、专用计算机、嵌入式处理机或其他可编程数据处理设备的处理器以产生一个机器，使得通过计算机或其他可编程数据处理设备的处理器执行的指令产生用于实现在流程图一个流程或多个流程和/或方框图一个方框或多个方框中指定的功能的装置。
这些计算机程序指令也可存储在能引导计算机或其他可编程数据处理设备以特定方式工作的计算机可读存储器中，使得存储在该计算机可读存储器中的指令产生包括指令装置的制造品，该指令装置实现在流程图一个流程或多个流程和/或方框图一个方框或多个方框中指定的功能。
这些计算机程序指令也可装载到计算机或其他可编程数据处理设备上，使得在计算机或其他可编程设备上执行一系列操作步骤以产生计算机实现的处理，从而在计算机或其他可编程设备上执行的指令提供用于实现在流程图一个流程或多个流程和/或方框图一个方框或多个方框中指定的功能的步骤。
以上所述的具体实施例，对本发明的目的、技术方案和有益效果进行了进一步详细说明，所应理解的是，以上所述仅为本发明的具体实施例而已，并不用于限定本发明的保护范围，凡在本发明的精神和原则之内，所做的任何修改、等同替换、改进等，均应包含在本发明的保护范围之内。

Claims (13)

  1. 一种磁共振血管壁成像方法，其中，包括：
    将一设定射频脉冲序列应用于成像区域，其中，所述设定射频脉冲序列按时间顺序依次包括：复合双带延迟交替与定制激励章动DANTE脉冲群、三维快速自旋回波SPACE的可变翻转角链及一向下翻转射频脉冲链；
    采集所述成像区域产生的磁共振信号，并根据所述磁共振信号重建得到所述成像区域中血管壁的磁共振图像。
  2. 如权利要求1所述的方法，其中，将一设定射频脉冲序列应用于成像区域之前，还包括：
    通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2优化所述可变翻转角链，以提高磁共振图像质量。
  3. 如权利要求2所述的方法，其中，通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2优化所述可变翻转角链，包括：
    通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2调整SPACE的既定回波信号演化曲线；
    根据所述既定回波信号演化曲线推算得到优化的可变翻转角；
    根据所述优化的可变翻转角计算得到多种成像组织的实际信号演化曲线，并根据所述实际信号演化曲线判断是否将所述优化的可变翻转角用作所述可变翻转角链。
  4. 如权利要求3所述的方法，其中，所述方法是基于3T磁共振系统，通过调整纵向磁化矢量弛豫时间T1和/或横向磁化矢量弛豫时间T2调整SPACE的既定回波信号演化曲线，包括：
    通过将纵向磁化矢量弛豫时间T1设置为800ms～3000ms和/或将横向磁化矢量弛豫时间T2设置为150ms～200ms设置SPACE的既定回波信号演化曲线。
  5. 如权利要求4所述的方法，其中，通过将纵向磁化矢量弛豫时间T1设置为800ms～3000ms和/或将横向磁化矢量弛豫时间T2设置为150ms～200ms设置SPACE的既定回波信号演化曲线，包括：
    通过将纵向磁化矢量弛豫时间T1设置为1000ms和/或将横向磁化矢量弛豫时间T2设置为150ms设置SPACE的既定回波信号演化曲线。
  6. 如权利要求1所述的方法，其中，将一设定射频脉冲序列应用于成像区域之前，还包括：
    通过调整SPACE的既定回波信号演化曲线中按时间顺序排列的第一部分、第二部分及第三部分之间的时间比例优化所述可变翻转角链，以提高磁共振图像质量；
    其中，调整所述第一部分的时间为2～5个SPACE的回波，调整所述第二部分的时间占所述既定回波信号演化曲线的总时间的40％～70％。
  7. 如权利要求1所述的方法，其中，将一设定射频脉冲序列应用于成像区域之前，还包括：
    通过调整SPACE的多个参数优化磁共振图像；
    其中，调整SPACE的重复时间TR为800ms～1200ms，调整SPACE的回波时间TE为5ms～25ms，以及调整SPACE的回波链长为25～60。
  8. 如权利要求1所述的方法，其中，所述向下翻转射频脉冲链按时间顺序依次包括：第一脉冲、第二脉冲及第三脉冲；
    其中，所述第一脉冲和所述第二脉冲之间的时间间隔为一个回波脉冲间隔，所述第二脉冲和所述第三脉冲之间的时间间隔为半个回波脉冲间隔，所述第三脉冲为90°脉冲。
  9. 如权利要求8所述的方法，其中，所述第一脉冲为100°～150°脉冲，所述第二脉冲为140°～180°脉冲。
  10. 如权利要求9所述的方法，其中，所述第一脉冲为130°脉冲，所述第二脉冲为160°脉冲。
  11. 如权利要求1所述的方法，其中，所述DANTE脉冲群包括多个按时间顺序排列的脉冲模块，每个所述脉冲模块包括一个矩形脉冲和一个散相梯度，所述矩形脉冲为2°～20°脉冲，所述散相梯度的幅值大小为20mT/m～40mT/m，所述脉冲模块的持续时间为1ms～2ms，所述脉冲模块的重复次数为50～500。
  12. 一种包括计算机可读指令的计算机可读存储介质，其中，所述计算机可读指令在被执行时使处理器至少执行权利要求1至11中任一项所述的方法。
  13. 一种设备，其中，包括：
    存储器，包括计算机可读指令；和
    处理器，在所述计算机可读指令被执行时执行如权利要求1至11中任一项所述的方法。
PCT/CN2016/104975 2016-11-08 2016-11-08 磁共振血管壁成像方法和设备 Ceased WO2018085969A1 (zh)

Priority Applications (3)

Application Number Priority Date Filing Date Title
PCT/CN2016/104975 WO2018085969A1 (zh) 2016-11-08 2016-11-08 磁共振血管壁成像方法和设备
CN201680022139.3A CN107690309B (zh) 2016-11-08 2016-11-08 磁共振血管壁成像方法和设备
US15/986,462 US10746833B2 (en) 2016-11-08 2018-05-22 Magnetic resonance vessel wall imaging method and device

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2016/104975 WO2018085969A1 (zh) 2016-11-08 2016-11-08 磁共振血管壁成像方法和设备

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US15/986,462 Continuation US10746833B2 (en) 2016-11-08 2018-05-22 Magnetic resonance vessel wall imaging method and device

Publications (1)

Publication Number Publication Date
WO2018085969A1 true WO2018085969A1 (zh) 2018-05-17

Family

ID=61152329

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2016/104975 Ceased WO2018085969A1 (zh) 2016-11-08 2016-11-08 磁共振血管壁成像方法和设备

Country Status (3)

Country Link
US (1) US10746833B2 (zh)
CN (1) CN107690309B (zh)
WO (1) WO2018085969A1 (zh)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108765513A (zh) * 2018-06-05 2018-11-06 上海交通大学 一种心脏血池抑制弛豫参数成像方法
CN109085523A (zh) * 2018-07-23 2018-12-25 中国科学院深圳先进技术研究院 血管壁成像中脑脊液信号的抑制方法、装置、设备及介质

Families Citing this family (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108983133B (zh) * 2018-07-23 2020-06-12 中国科学院深圳先进技术研究院 磁共振血管壁成像方法、装置、设备及存储介质
CN111325808B (zh) * 2018-12-15 2021-02-26 深圳先进技术研究院 一种非线性梯度成像的图像重建方法及其相关设备
CN111202519B (zh) * 2020-01-17 2023-04-14 首都医科大学宣武医院 一种在体血栓软硬度检测的方法及其系统
WO2024108581A1 (zh) * 2022-11-25 2024-05-30 中国科学院深圳先进技术研究院 功能磁共振成像方法、装置、电子设备及存储介质
CN115770031B (zh) * 2022-11-25 2025-08-26 中国科学院深圳先进技术研究院 功能磁共振成像方法、装置、电子设备及存储介质
CN116077047A (zh) * 2023-01-13 2023-05-09 中国科学院深圳先进技术研究院 一种腹部血管壁成像方法和系统
WO2024148595A1 (zh) * 2023-01-13 2024-07-18 中国科学院深圳先进技术研究院 一种腹部血管壁成像方法和系统
CN116449276A (zh) * 2023-04-11 2023-07-18 广州医科大学 磁共振t1定量成像方法及设备

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5614826A (en) * 1995-08-18 1997-03-25 Emory University Methods for prepulsing in nuclear magnetic resonance pulse sequencing
CN102692612A (zh) * 2011-03-22 2012-09-26 株式会社东芝 磁共振成像系统以及方法
US20130314086A1 (en) * 2012-03-20 2013-11-28 Isis Innovation Ltd. Motion sensitized and motion suppressed imaging using dante prepared pulse trains
CN103930023A (zh) * 2012-05-11 2014-07-16 株式会社东芝 磁共振成像装置以及图像处理装置
US20160266223A1 (en) * 2015-03-12 2016-09-15 Siemens Healthcare Gmbh System And Method For Motion-Robust 3D Magnetic Resonance Imaging Of Vessel Walls

Family Cites Families (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP5433436B2 (ja) * 2009-09-30 2014-03-05 株式会社東芝 磁気共鳴イメージング装置、および、磁気共鳴イメージング方法
WO2012106574A2 (en) * 2011-02-03 2012-08-09 The Regents Of The University Of California Cardiac mri curvilinear tagging
US8248070B1 (en) 2011-03-22 2012-08-21 Kabushiki Kaisha Toshiba MRI using prep scan sequence producing phase-offset NMR signals from different NMR species
JP6218397B2 (ja) * 2012-04-04 2017-10-25 東芝メディカルシステムズ株式会社 磁気共鳴イメージング装置及び方法
JP5984258B2 (ja) * 2012-04-27 2016-09-06 東芝メディカルシステムズ株式会社 磁気共鳴イメージング装置及び画像処理装置
US10980492B2 (en) * 2012-05-11 2021-04-20 Toshiba Medical Systems Corporation Magnetic resonance imaging apparatus and image processing apparatus
RU2015114570A (ru) * 2012-09-20 2016-11-10 Конинклейке Филипс Н.В. Система обнаружения метаболитов и порядок ее действия
JP6176822B2 (ja) * 2013-02-08 2017-08-09 東芝メディカルシステムズ株式会社 画像処理装置及び磁気共鳴イメージング装置
JP6091989B2 (ja) * 2013-05-10 2017-03-08 東芝メディカルシステムズ株式会社 画像処理装置及び磁気共鳴イメージング装置
US20160139222A1 (en) * 2013-06-19 2016-05-19 Yeda Research And Development Co. Ltd. Methods for spatial and spectral selectivity in magnetic resonance imaging and spectroscopy
US10698053B2 (en) * 2014-02-07 2020-06-30 Regents Of The University Of Minnesota System and method for gradient-modulated sweep imaging with fourier transformation magnetic resonance imaging
US10557906B2 (en) * 2016-04-29 2020-02-11 The Chinese University Of Hong Kong Quantitative magnetic resonance imaging relaxometry with suppression of blood signal

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5614826A (en) * 1995-08-18 1997-03-25 Emory University Methods for prepulsing in nuclear magnetic resonance pulse sequencing
CN102692612A (zh) * 2011-03-22 2012-09-26 株式会社东芝 磁共振成像系统以及方法
US20130314086A1 (en) * 2012-03-20 2013-11-28 Isis Innovation Ltd. Motion sensitized and motion suppressed imaging using dante prepared pulse trains
CN103930023A (zh) * 2012-05-11 2014-07-16 株式会社东芝 磁共振成像装置以及图像处理装置
US20160266223A1 (en) * 2015-03-12 2016-09-15 Siemens Healthcare Gmbh System And Method For Motion-Robust 3D Magnetic Resonance Imaging Of Vessel Walls

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
PARK, J. ET AL.: "Optimized T1-Weighted Contrast for Single-Slab 3D Turbo Spin-Echo Imaging With Long Echo Trains: Application to Whole-Brain Imaging", MAGNETIC RESONANCE IN MEDICINE, vol. 58, no. 5, 30 November 2007 (2007-11-30), pages 985 and 987 - 988, XP055166898 *
VIESSMANN, O. ET AL.: "T2-Weighted Intracranial Vessel Wall Imaging at 7 Tesla Using a DANTE-Prepared Variable Flip Angle Turbo Spin Echo Readout (DANTE-SPACE)", WILEY ONLINE LIBRARY, vol. 77, no. 2, February 2017 (2017-02-01), pages 655 - 663, XP055483181 *

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108765513A (zh) * 2018-06-05 2018-11-06 上海交通大学 一种心脏血池抑制弛豫参数成像方法
CN108765513B (zh) * 2018-06-05 2022-06-28 上海交通大学 一种心脏血池抑制弛豫参数成像方法
CN109085523A (zh) * 2018-07-23 2018-12-25 中国科学院深圳先进技术研究院 血管壁成像中脑脊液信号的抑制方法、装置、设备及介质
CN109085523B (zh) * 2018-07-23 2020-05-22 中国科学院深圳先进技术研究院 血管壁成像中脑脊液信号的抑制方法、装置、设备及介质

Also Published As

Publication number Publication date
US20180267125A1 (en) 2018-09-20
CN107690309A (zh) 2018-02-13
CN107690309B (zh) 2019-03-22
US10746833B2 (en) 2020-08-18

Similar Documents

Publication Publication Date Title
WO2018085969A1 (zh) 磁共振血管壁成像方法和设备
Bammer et al. Time‐resolved 3D quantitative flow MRI of the major intracranial vessels: initial experience and comparative evaluation at 1.5 T and 3.0 T in combination with parallel imaging
US10470676B2 (en) Noninvasive 4-D time-resolved dynamic magnetic resonance angiography
JP5750452B2 (ja) 時間分解磁気共鳴血管造影と潅流画像のシステムと方法
JP6656826B2 (ja) 磁気共鳴イメージング装置
US9380960B2 (en) Method for non-contrast enhanced magnetic resonance angiography
US20110137146A1 (en) Method for Non-Contrast Enhanced Magnetic Resonance Angiography
US10405772B2 (en) Magnetic resonance angiography and venography
JP2008093418A (ja) 磁気共鳴画像診断装置およびその制御方法
US10901060B2 (en) Magnetic resonance imaging apparatus and magnetic resonance imaging method
JP6533571B2 (ja) 磁気共鳴イメージング装置及び画像作成方法
JP6625353B2 (ja) 磁気共鳴イメージング装置
Lethimonnier et al. Three-dimensional coronary artery MR imaging using prospective real-time respiratory navigator and linear phase shift processing: comparison with conventional coronary angiography
US10859658B2 (en) System and method for semi-projective quantitative flow imaging using accelerated arterial spin-labeled cine MRI
CN108377641B (zh) 磁共振血管壁成像方法和设备
US10845447B2 (en) System and method for fast interrupted steady-state (FISS) MRI
JP5159836B2 (ja) Ｍｒｉ装置
Radlbauer et al. Triggered non-contrast enhanced MR angiography of peripheral arteries: Optimization of systolic and diastolic time delays for electrocardiographic triggering
JP5380585B2 (ja) Ｍｒｉ装置
Tanaka et al. Noninvasive identification of peripheral vessels of oral and maxillofacial regions by using electrocardiography-triggered three-dimensional fast asymmetric spin-echo sequences
CN119916276A (zh) 磁共振成像方法、装置、医学成像设备及存储介质
JP5380469B2 (ja) 磁気共鳴イメージング装置および磁気共鳴イメージング方法
Daouk et al. Simultaneous assessment of respiration and heart beat on CSF and blood oscillations in near real-time imaging
Lin Noninvasive Imaging of Carotid Arterial Strain Using Displacement-Encoded MRI
Poutanen Cardiac Magnetic Resonance Imaging Techniques in the Assessment of Flow and Volumetry

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 16921380

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

32PN Ep: public notification in the ep bulletin as address of the adressee cannot be established

Free format text: NOTING OF LOSS OF RIGHTS PURSUANT TO RULE 112(1) EPC (EPO FORM 1205A DATED 20/08/2019)

122 Ep: pct application non-entry in european phase

Ref document number: 16921380

Country of ref document: EP

Kind code of ref document: A1