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WO2018085970A1 - Procédé et dispositif d'imagerie par résonance magnétique de paroi vasculaire - Google Patents

Procédé et dispositif d'imagerie par résonance magnétique de paroi vasculaire Download PDF

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Publication number
WO2018085970A1
WO2018085970A1 PCT/CN2016/104976 CN2016104976W WO2018085970A1 WO 2018085970 A1 WO2018085970 A1 WO 2018085970A1 CN 2016104976 W CN2016104976 W CN 2016104976W WO 2018085970 A1 WO2018085970 A1 WO 2018085970A1
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Prior art keywords
pulse
magnetic resonance
space
magnetization vector
relaxation time
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Chinese (zh)
Inventor
张磊
钟耀祖
刘新
胡小情
郑海荣
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Shenzhen Institute of Advanced Technology of CAS
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Shenzhen Institute of Advanced Technology of CAS
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Priority to PCT/CN2016/104976 priority Critical patent/WO2018085970A1/fr
Priority to CN201680022140.6A priority patent/CN108377641B/zh
Publication of WO2018085970A1 publication Critical patent/WO2018085970A1/fr
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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
    • 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

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%). Therefore, accurate identification of cerebral arterial 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 intracranial 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.
  • Two-dimensional magnetic resonance vascular wall imaging has the following advantages: high resolution and clear tissue details; multi-contrast images can be used to obtain plaque components, which can help determine the composition and characteristics of plaques; Technology that reduces blood flow artifacts and bright blood interference with images. But at the same time, it has shortcomings: long scanning time, more than 30 minutes; small imaging range, can only cover a single blood vessel at a time; blood pressure effect is not ideal, blood flow artifacts are easy to occur; interlayer resolution is low, only up to 2mm, Partial volume effects are prone to occur, resulting in large errors in measuring plaque size.
  • Dr. Zhong Yaozu used T1 weighted contrast to reduce cerebrospinal fluid signal, highlight the vessel wall, and improved the signal-to-noise ratio with the advanced 32-channel head RF coil, successfully solving several key problems in intracranial artery 3D magnetic resonance imaging.
  • the SPACE technology to the Siemens 3T imaging system, the T1 weight intracranial artery three-dimensional magnetic resonance vascular wall imaging was performed, and a 0.5 mm isotropic high-resolution three-dimensional black blood intracranial artery blood vessel wall image was obtained.
  • the scanning time was 10 minutes. .
  • the invention provides a magnetic resonance blood vessel wall imaging method and device for better suppressing the signal of intracranial cerebrospinal fluid, thereby improving the imaging quality of the blood vessel wall.
  • the invention provides a magnetic resonance blood vessel wall imaging method, comprising: applying a set radio frequency pulse sequence to an imaging area, wherein the set radio frequency pulse sequence comprises, in chronological order, a variable of a three-dimensional fast spin echo SPACE Flipping the angular chain and flipping the RF pulse chain; acquiring a magnetic resonance signal generated by the imaging region, and reconstructing a magnetic resonance image of the blood vessel wall in the imaging region according to the magnetic resonance signal.
  • 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 variable flip angle chain of a three-dimensional fast spin echo SPACE and a downward flip RF pulse chain; a magnetic resonance image generating unit configured to: acquire a magnetic resonance signal generated by the imaging region, and reconstruct according to the magnetic resonance signal A magnetic resonance image of the vessel wall in the imaging region is obtained.
  • 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 variable flip angle chain of a three-dimensional fast spin echo SPACE and a downward flip RF pulse chain
  • a magnetic resonance image generating unit configured to: acquire a magnetic resonance signal generated by the imaging region, and reconstruct according to the magnetic resonance signal A magnetic resonance image of the vessel wall in the imaging region is obtained.
  • 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. Evenly suppressing the cerebrospinal fluid signal of the whole brain, the quality of magnetic resonance vascular wall imaging is further improved on the basis of the existing SPACE. In other embodiments, by optimizing the variable flip angle of SPACE, further Signal to noise ratio of high magnetic resonance images.
  • 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 the existing SPACE 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.
  • the present invention proposes a magnetic resonance vascular wall imaging method based on the redesign of the radio frequency pulse sequence for magnetic resonance imaging, and the existing SPACE Compared with the cerebrospinal fluid signal, it can increase the signal-to-noise ratio of the tissue more effectively and uniformly. It is to be noted that the following embodiments illustrate the implementation and efficacy of the present invention by taking magnetic resonance imaging of the intracranial vessel wall and suppressing the cerebrospinal fluid signal as an example, and are not intended to limit the imaging area and use of the present invention.
  • 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 variable flip angle chain of the three-dimensional fast spin echo SPACE and a downward flip 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.
  • variable flip angle chain of SPACE can be the variable flip angle chain of the existing SPACE.
  • ISMRM International Society for Magnetic Resonance in Medicine
  • Flip-down pulse can be an existing flip-down RF pulse chain, for example, Park et al.
  • 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 RF pulse sequence may comprise only a variable flip angle chain of SPACE and the flipped RF pulse train described above, and the variable flip angle chain of SPACE may generally be in close proximity to the flipped RF pulse train described above.
  • the set radio frequency pulse sequence may also include other pulses, and the positions of the other pulses in chronological order relative to the SPACE variable flip angle chain and the downward flip RF pulse chain may be set as needed. set.
  • the RF pulses for magnetic resonance imaging are designed by sequentially arranging the set RF pulse sequence including a variable flip angle chain of a three-dimensional fast spin echo SPACE and a flipped RF pulse chain in chronological order.
  • 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 cerebrospinal fluid signal can be further suppressed, the contrast between the cerebrospinal fluid and the blood vessel wall can be improved, and the intracranial blood vessel wall imaging is beneficial.
  • 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. For example, after RF pulse, layer selection Gradient, readout gradient, phase encoding, etc., achieve magnetic resonance signals. 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 further uniformly suppress the cerebrospinal fluid signal based on the existing SPACE by specifically involving the radio frequency pulse sequence, including the variable flip angle chain of SPACE and the downward flipping RF pulse chain. Further improve the imaging quality of the blood vessel wall.
  • 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:
  • S131 adjusting a predetermined echo signal evolution curve of the SPACE by adjusting a longitudinal magnetization vector relaxation time T1 and/or a transverse magnetization vector relaxation time T2;
  • 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 imaging tissue adjustment can be set for only one type SPACE's established echo signal evolution curve.
  • 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 radio frequency pulse sequence, which can further improve the blood vessel wall and The contrast of 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 intensity of the first part decays exponentially with time, which is the initial attenuation part; the second part
  • the signal strength of the fraction remains unchanged as the intermediate flat portion; the signal strength of the third portion continues to decrease with time as the final attenuation portion.
  • the echo of the first portion may be adjusted to a time of 2 to 5 SPACEs, and the time of the second portion may be 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 RF pulse sequence described above includes a SPACE variable flip angle chain 320 and a downward flip RF pulse train 330.
  • 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.
  • the established echo signal evolution curve of SPACE is designed for a specific tissue, including the initial attenuation part A, the middle level Tan part B and finally decay part C three parts.
  • 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. It can be seen that the method of the embodiment of the present invention can effectively suppress the signal of the cerebrospinal fluid 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 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 method proposed by Zhong Yaozu et al. (High Resolution 3D Intracranial Imaging at 3.0T, Proceedings of the 12th Annual Meeting of ISMRM, 2010, p. 2255).
  • 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 inhibition of cerebrospinal fluid in the left half of the brain.
  • Part (c) of Figure 11 and part (c) of Figure 12 show inhibition of cerebrospinal fluid in the right half of the brain.
  • Comparing part (c) of Figure 11 with part (g) of Figure 12 it can be seen that The method of the embodiments of the invention is capable of suppressing cerebrospinal fluid signals in the right half of the brain more uniformly and more effectively.
  • the method of the embodiment of the present invention not only has a better cerebrospinal fluid signal suppression effect, but also more uniformly suppresses the cerebrospinal fluid signal of the whole brain.
  • FIG. 13 is a schematic diagram showing the evolution of a predetermined echo signal of SPACE when T1/T2 are 1000/150 ms and 940/100 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.
  • Figure 14 is according to Figure 13 A comparison diagram of the variable flip angles derived from the evolution of a given echo signal. 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.
  • FIG. 17 (b) is a cross-sectional image of the blood 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 further improves the quality of magnetic resonance vascular wall imaging based on the existing SPACE.
  • 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 region, wherein the set radio frequency pulse sequence comprises, in chronological order, a variable flip angle chain of the three-dimensional fast spin echo SPACE Flip the RF pulse chain down.
  • 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.
  • a time interval between the first pulse and the second pulse is an echo pulse interval
  • a 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.
  • 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: setting a predetermined echo signal evolution of SPACE by setting a longitudinal magnetization vector relaxation time T1 to 800 ms to 3000 ms and/or setting a transverse magnetization vector relaxation time T2 to 150 ms to 200 ms 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 Further suppressing the cerebrospinal fluid signal of the whole brain, and further improving the imaging quality of the magnetic resonance blood vessel wall based on the existing SPACE.
  • 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. The parameters better enhance the MRI of existing SPACE.
  • Embodiments of the present invention also provide a computer readable storage medium including computer readable instructions, the computer The readable instructions, when executed, cause the processor to perform at least one or more of the steps of the magnetic resonance vascular wall imaging methods of the various embodiments described above.
  • 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 further improves the imaging quality of the magnetic resonance vessel wall based on the existing SPACE.
  • 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.

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Abstract

La présente invention concerne un procédé et un dispositif d'imagerie par résonance magnétique de paroi vasculaire. Le procédé consiste à : appliquer une séquence d'impulsions à haute fréquence définie sur une région d'imagerie, la séquence d'impulsions à haute fréquence définie comprenant dans l'ordre, selon un ordre chronologique, une chaîne angulaire de retournement variable (320) d'un écho de spin rapide tridimensionnel SPACE et une chaîne d'impulsions à haute fréquence de retournement vers le bas (330) (S110); et collecter un signal de résonance magnétique généré dans la région d'imagerie, et effectuer une reconstruction en fonction du signal de résonance magnétique de sorte à obtenir une image de résonance magnétique d'une paroi vasculaire dans la région d'imagerie (S120). En ajoutant d'abord les chaînes d'impulsions à haute fréquence de retournement vers le bas après les chaînes angulaires de retournement variable d'échos de spin rapide tridimensionnels SPACE, les signaux du liquide cérébro-spinal du cerveau entier peuvent en outre être supprimés de manière efficace et uniforme.
PCT/CN2016/104976 2016-11-08 2016-11-08 Procédé et dispositif d'imagerie par résonance magnétique de paroi vasculaire Ceased WO2018085970A1 (fr)

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CN201680022140.6A CN108377641B (zh) 2016-11-08 2016-11-08 磁共振血管壁成像方法和设备

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