CN113030817B - Magnetic resonance imaging method, device and storage medium - Google Patents
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- 238000002595 magnetic resonance imaging Methods 0.000 title claims abstract description 45
- 238000000034 method Methods 0.000 title claims abstract description 44
- 238000000264 spin echo pulse sequence Methods 0.000 claims abstract description 33
- 210000001175 cerebrospinal fluid Anatomy 0.000 claims abstract description 32
- 230000005284 excitation Effects 0.000 claims abstract description 12
- 210000001519 tissue Anatomy 0.000 claims description 27
- 230000005415 magnetization Effects 0.000 claims description 16
- 239000013598 vector Substances 0.000 claims description 15
- 230000001629 suppression Effects 0.000 claims description 5
- 230000006378 damage Effects 0.000 claims description 3
- 238000002075 inversion recovery Methods 0.000 abstract description 4
- 238000003384 imaging method Methods 0.000 description 14
- 238000011084 recovery Methods 0.000 description 11
- 238000010586 diagram Methods 0.000 description 6
- 208000026911 Tuberous sclerosis complex Diseases 0.000 description 3
- 210000004556 brain Anatomy 0.000 description 3
- 208000009999 tuberous sclerosis Diseases 0.000 description 3
- 201000010099 disease Diseases 0.000 description 2
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 2
- 230000001360 synchronised effect Effects 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 1
- 210000005013 brain tissue Anatomy 0.000 description 1
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- JXSJBGJIGXNWCI-UHFFFAOYSA-N diethyl 2-[(dimethoxyphosphorothioyl)thio]succinate Chemical compound CCOC(=O)CC(SP(=S)(OC)OC)C(=O)OCC JXSJBGJIGXNWCI-UHFFFAOYSA-N 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 210000004884 grey matter Anatomy 0.000 description 1
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- 210000003625 skull Anatomy 0.000 description 1
- 230000003068 static effect Effects 0.000 description 1
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- 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
- G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
- G01R33/5615—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE]
- G01R33/5618—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE] using both RF and gradient refocusing, e.g. GRASE
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- 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
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- 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
- G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
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Abstract
The invention discloses a magnetic resonance imaging method, magnetic resonance imaging equipment and a storage medium. The method comprises the following steps: in each cycle: applying 180 DEG radio frequency pulses; applying a gradient echo sequence; applying a first fast spin echo sequence; wherein the repetition number of the cycle is not less than 1; and generating a T1 weighted image according to the data acquired by the gradient echo sequence, and generating a cerebrospinal fluid suppressed T2 weighted image according to the data acquired by the first fast spin echo sequence. The present invention shortens the magnetic resonance scan time for generating a T1-weighted image and a cerebrospinal fluid suppressed T2-weighted image by acquiring T1-weighted image data with the idle time that exists between the inversion recovery pulse and the excitation pulse that is required in generating a cerebrospinal fluid suppressed T2-weighted image by applying a gradient echo sequence after applying a 180 ° radio frequency pulse and before applying the first fast spin echo sequence.
Description
Technical Field
The present invention relates to the field of magnetic resonance technology, and in particular, to a magnetic resonance imaging method, apparatus, and storage medium.
Background
The magnetic resonance sequence is often used to scan and image the focus clinically, and for some diseases, such as TSC (Tuberous Sclerosis), a clearer display is needed, and in order to clearly display the focus, the clinical scan has high selected intralayer resolution, the data size needs to be large, the scanning time is long, and the long scanning time causes discomfort to the patient.
Thus, there is a need for improvements and enhancements in the art.
Disclosure of Invention
In view of the above-mentioned drawbacks of the prior art, a magnetic resonance imaging method, a magnetic resonance imaging apparatus, and a storage medium are provided to solve the problem of long scanning time in the prior art.
In a first aspect of the invention, a magnetic resonance imaging method is provided, including:
in each cycle:
applying 180 DEG radio frequency pulses;
applying a gradient echo sequence;
applying a first fast spin echo sequence;
wherein the repetition number of the cycle is not less than 1;
and generating a T1 weighted image according to the data acquired by the gradient echo sequence, and generating a cerebrospinal fluid suppressed T2 weighted image according to the data acquired by the first fast spin echo sequence.
The magnetic resonance imaging method, wherein after the applying of the 180 ° radio frequency pulse, further comprises:
and respectively applying damage gradients along the layer selection direction, the reading direction and the phase direction.
The magnetic resonance imaging method is characterized in that the phase direction of the gradient echo sequence and the acquisition time of the zero-encoding line in the slice selection direction are determined according to T1 values of a first preset tissue and a second preset tissue.
The magnetic resonance imaging method, wherein the time interval between the acquisition time of the zero-encoding line in the phase direction and the slice selection direction of the gradient recovery sequence and the application time of the 180 ° radio frequency pulse is:
wherein, TI1For said time interval, M0，tissue1And T1，tissue1Respectively, the initial magnetization vector of the first predetermined tissue and the value T1, M0，tissue2And T1，tissue2The initial magnetization vector and the value of T1 of the second preset tissue are respectively, and T is a time variable.
The magnetic resonance imaging method, wherein the application time of the excitation radio frequency pulse of the first fast spin echo sequence is determined according to the T1 value of cerebrospinal fluid.
The magnetic resonance imaging method, wherein the time interval between the application time of the excitation radio frequency pulse of the first fast spin echo sequence and the application time of the 180 ° radio frequency pulse is:
TI2＝T1，CSF；
wherein, TI2For said time interval, T1，CSFT1 value for cerebrospinal fluid.
The magnetic resonance imaging method, wherein after the applying the first fast spin echo sequence in each of the periods, further comprising:
a second fast spin echo sequence is applied.
The magnetic resonance imaging method further comprises the following steps:
generating a T2 weighted image from data acquired by the second fast spin echo sequence.
In a second aspect of the present invention, there is provided a magnetic resonance imaging apparatus comprising: the magnetic resonance imaging system comprises a processor and a storage medium which is in communication connection with the processor, wherein the storage medium is suitable for storing a plurality of instructions, and the processor is suitable for calling the instructions in the storage medium to execute the steps for realizing the magnetic resonance imaging method.
In a third aspect of the invention, a storage medium is provided, wherein the storage medium stores one or more programs, which are executable by one or more processors to implement the steps of the magnetic resonance imaging method according to any one of the above.
Has the advantages that: in contrast to the prior art, the present invention provides a magnetic resonance imaging method, apparatus and storage medium, which shortens the magnetic resonance scan time for generating a T1-weighted image and a cerebrospinal fluid suppressed T2-weighted image by acquiring T1-weighted image data using the idle time existing between the inversion recovery pulse and the excitation pulse required in generating a cerebrospinal fluid suppressed T2-weighted image by applying a gradient echo sequence after applying a 180 ° radio frequency pulse and before applying a first fast spin echo sequence.
Drawings
Figure 1 is a flow chart of a single cycle in an embodiment of a magnetic resonance imaging method provided by the invention;
FIG. 2 is a sequence structure diagram of each period in an embodiment of a magnetic resonance imaging method provided by the present invention;
FIG. 3 is a sequence diagram of each period in the magnetic resonance imaging method provided by the present invention;
figure 4 is a schematic diagram of the application of 180 ° radio frequency pulses in an embodiment of the magnetic resonance imaging method provided by the present invention;
figure 5 is a schematic illustration of the application of a gradient echo sequence in an embodiment of a magnetic resonance imaging method provided by the invention;
figure 6 is a schematic illustration of the application of a first fast spin echo sequence in an embodiment of a magnetic resonance imaging method provided by the invention;
figure 7 is a schematic illustration of the application of a second fast spin echo sequence in an embodiment of the magnetic resonance imaging method provided by the invention;
fig. 8 is a schematic structural diagram of an embodiment of a magnetic resonance multi-contrast imaging apparatus provided by the present invention.
Detailed Description
In order to make the objects, technical solutions and effects of the present invention clearer and clearer, the present invention is further described in detail below with reference to the accompanying drawings and examples. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
The inventor finds that in the prior art, different contrast imaging is often performed by using a plurality of separate sequences, such as a Magnetization-Prepared fast Gradient Echo sequence (T1 MP-RAGE, T1 Magnetization Prepared-RApid Gradient Echo) of a T1 weighted image, a cerebrospinal Fluid compression Inversion Recovery sequence (T2 FLAIR, T2Fluid anchored Recovery) of a T2 weighted image, and the like, aiming at diseases such as tuberous sclerosis, and the like, the focus is often imaged by brain Magnetic Resonance Imaging (MRI) in the prior clinic, and surgical treatment is guided thereby. Thus, a large amount of space time exists in the scanning process, the scanning efficiency is not high, and the scanning time is long.
The magnetic resonance imaging method provided by the invention can be applied to a magnetic resonance imaging device, and is executed by the magnetic resonance imaging device.
Example one
The magnetic resonance imaging method provided by the invention periodically applies an imaging sequence, the repetition number of the period is not less than 1, as shown in figure 1, and in each period, the method comprises the following steps:
s100, applying 180-degree radio frequency pulse;
s200, applying a gradient echo sequence;
and S300, applying a first fast spin echo sequence.
And generating a T1 weighted image according to the data acquired by the gradient echo sequence, and generating a cerebrospinal fluid suppressed T2 weighted image according to the data acquired by the first fast spin echo sequence. Specifically, as shown in fig. 2, the magnetic resonance imaging apparatus periodically applies an imaging sequence, each periodic imaging sequence comprises a flip recovery module, a T1 weighted imaging module and a cerebrospinal fluid suppression T2 weighted module, sequence diagrams of each module are shown in fig. 4-6, and the sequences of the modules are connected end to form a sequence in a single period as shown in fig. 3.
The flipping recovery module comprises 180 ° radio frequency pulses, that is, in each period, the device applies 180 ° radio frequency pulses first, and the 180 ° radio frequency pulses flip the longitudinal magnetization vector by 180 °, without loss of generality, and assuming that the initial longitudinal magnetization vector is arranged along the + z-axis direction, the 180 ° radio frequency pulses flip the longitudinal magnetization vector to the-z-axis direction, so that it performs T1 recovery along the z-axis. Thus, different tissues are restored along the z-axis + z direction according to respective T1 parameters, and due to the difference in T1 parameters between different tissues, the magnitude of the longitudinal magnetization vector of different tissues will differ during restoration, and this difference will reflect the difference in T1 values between different tissues, and thus, it will be beneficial to acquire T1 weighted image data. While the longitudinal magnetization vector of the tissue has a zero crossing during the recovery along the z-axis, i.e., the time when the longitudinal magnetization vector is zero, the tissue will not generate a signal if the excitation RF pulse is applied, and thus the signal of the cerebrospinal fluid can be suppressed to generate a T2 weighted image of cerebrospinal fluid suppression. While a great deal of idle time exists between the turning of the longitudinal magnetization vector of the tissue from the beginning to the zero crossing point, a turning recovery pulse is applied and then an excitation pulse is applied for data acquisition in the conventional cerebrospinal fluid suppressed T2 weighted imaging sequence, a great deal of idle time exists between the turning recovery pulse and the excitation pulse, which is usually 2000-2500ms, in the present embodiment, after a 180 ° radio frequency pulse is applied to realize the turning of the longitudinal magnetization vector, a gradient echo sequence is applied to acquire a T1 weighted image between the application of a first fast spin echo sequence to acquire a cerebrospinal fluid suppressed T2 weighted image, that is, the idle time in the cerebrospinal fluid suppressed T2 weighted imaging sequence is utilized to acquire a T1 weighted image, so that the total duration of acquiring the T1 weighted image and the cerebrospinal fluid suppressed T2 weighted image can be shortened, and the scanning time can be shortened.
Further, in practical applications, there may be residual transverse magnetization vectors due to imperfections of the rf pulse and energy decay of the rf during propagation, so in this embodiment, after applying the 180 ° rf pulse, a destruction gradient is applied in the layer selection direction, the readout direction and the phase direction, respectively, as shown in fig. 4.
The gradient echo sequence is used for acquiring a T1 weighted image, further, the radio frequency pulses in the gradient echo sequence are all small flip angle radio frequency pulses, for example, the flip angle of the radio frequency pulses in the gradient echo sequence may be 5 ° -12 °, although the above is only an example, and according to the imaging requirement of an actual T1 weighted image, a person skilled in the art may define the flip angle of the radio frequency pulses in the gradient echo sequence by himself.
The contrast of the image imaged by magnetic resonance is mainly determined by the magnetic resonance K-space central data, i.e. by the zero-encoding lines in the phase direction and the slice selection direction. The phase direction of the gradient echo sequence for acquiring the T1 weighted image and the acquisition time of the zero-encoding line in the slice selection direction are determined according to T1 values of a first predetermined tissue and a second predetermined tissue, specifically, the first predetermined tissue and the second predetermined tissue are predetermined human tissues, and the first predetermined tissue and the second predetermined tissue may be selected from brain tissues, for example, from: two tissues such as the gray matter of brain, the white matter of brain, the vascular wall, the skull are selected as the first preset tissue and the second preset tissue respectively, and the time interval between the acquisition time of the zero encoding line in the phase direction and the layer selection direction of the gradient recovery sequence and the application time of the 180-degree radio frequency pulse is as follows:
wherein, TI1For said time interval, M0，tissue1And T1，tissue1Respectively, the initial magnetization vector of the first predetermined tissue and the value T1, M0，tissue2And T1，tissue2Respectively the initial magnetization vector of the second predetermined tissue and the value of T1, T being a time variable。
The application instant of the excitation radio frequency pulse of the first fast spin echo sequence for acquiring a T2 weighted image of cerebrospinal fluid suppression is determined from the T1 value of cerebrospinal fluid, in particular the time interval between the application instant of the excitation radio frequency pulse of the first fast spin echo sequence and the application instant of the 180 ° radio frequency pulse is:
TI2＝T1，CSF；
wherein, TI2For said time interval, TI2＝T1，CSFT1 value for cerebrospinal fluid.
In order to further realize the scanning time of multi-contrast imaging, in the present embodiment, after applying the first fast spin echo sequence in each period, a second fast spin echo sequence is also applied, the second fast spin echo sequence is used for acquiring a T2 weighted image, specifically, the repetition time of the T2 weighted imaging sequence based on fast spin echo is long, so that a long time is needed to wait for signal recovery after the current signal acquisition in the T2 weighted imaging sequence of cerebrospinal fluid suppression is completed, a 180 ° radio frequency pulse is reapplied for a new round of data acquisition of T2 weighted imaging, in the present embodiment, the T2 weighted image is acquired by using the time, specifically, as shown in fig. 2-3 and fig. 7, the sequence in each period further includes a T2 weighting module, the T2 weighting module includes a second spin echo sequence, the second spin echo sequence, which may be a unitary connection, is identical to the first spin echo sequence. It can be seen that the second spin echo sequence is added in the period, the signal recovery time of the cerebrospinal fluid suppressed T2 weighted image acquisition sequence can be fully utilized, the scanning efficiency is further improved, imaging of the T1 weighted image, the cerebrospinal fluid suppressed T2 weighted image and the T2 weighted image can be completed in a shorter time, and the scanning time is shortened.
In summary, the present embodiment provides a magnetic resonance imaging method for shortening the time of a magnetic resonance scan for generating a T1-weighted image and a cerebrospinal fluid suppressed T2-weighted image by acquiring T1-weighted image data using the idle time existing between the inversion recovery pulse and the excitation pulse required in generating a cerebrospinal fluid suppressed T2-weighted image by applying a gradient echo sequence after applying a 180-radio frequency pulse and before applying a first fast spin echo sequence.
It should be understood that, although the steps in the flowcharts shown in the figures of the present specification are shown in order as indicated by the arrows, the steps are not necessarily performed in order as indicated by the arrows. The steps of the present invention are not limited to being performed in the exact order disclosed, and may be performed in other orders, unless explicitly stated otherwise. Moreover, at least a portion of the steps of the present invention may include multiple sub-steps or multiple stages, which are not necessarily performed at the same time, but may be performed at different times, and the order of performing the sub-steps or stages is not necessarily sequential, but may be performed alternately or alternately with other steps or at least a portion of the sub-steps or stages of other steps.
It will be understood by those skilled in the art that all or part of the processes of the methods of the embodiments described above can be implemented by hardware instructions of a computer program, which can be stored in a non-volatile computer-readable storage medium, and when executed, can include the processes of the embodiments of the methods described above. Any reference to memory, storage, databases, or other media used in embodiments provided herein may include non-volatile and/or volatile memory. Non-volatile memory can include read-only memory (ROM), Programmable ROM (PROM), Electrically Programmable ROM (EPROM), Electrically Erasable Programmable ROM (EEPROM), or flash memory. Volatile memory can include Random Access Memory (RAM) or external cache memory. By way of illustration and not limitation, RAM is available in a variety of forms such as Static RAM (SRAM), Dynamic RAM (DRAM), Synchronous DRAM (SDRAM), Double Data Rate SDRAM (DDRSDRAM), Enhanced SDRAM (ESDRAM), Synchronous Link DRAM (SLDRAM), Rambus Direct RAM (RDRAM), direct bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM).
Example two
Based on the above embodiments, the present invention further provides a magnetic resonance imaging apparatus, and a functional block diagram thereof may be as shown in fig. 8. The device comprises a processor 10 and a memory 20. It is to be understood that fig. 8 only shows some of the components of the terminal, but it is to be understood that not all of the shown components are required to be implemented, and that more or fewer components may be implemented instead.
The memory 20 may in some embodiments be an internal storage unit of the terminal, such as a hard disk or a memory of the terminal. The memory 20 may also be an external storage device of the terminal in other embodiments, such as a plug-in hard disk, a Smart Media Card (SMC), a Secure Digital (SD) Card, a Flash memory Card (Flash Card), and the like provided on the terminal. Further, the memory 20 may also include both an internal storage unit and an external storage device of the terminal. The memory 20 is used for storing application software installed in the terminal and various data. The memory 20 may also be used to temporarily store data that has been output or is to be output. In one embodiment, the memory 20 stores a magnetic resonance imaging program 30, and the magnetic resonance imaging program 30 is executable by the processor 10 to implement the magnetic resonance imaging method of the present application.
The processor 10 may be, in some embodiments, a Central Processing Unit (CPU), microprocessor or other chip for executing program codes stored in the memory 20 or Processing data, such as performing the magnetic resonance imaging method.
EXAMPLE III
The present invention also provides a storage medium storing one or more programs executable by one or more processors to implement the steps of the magnetic resonance imaging method described in the above embodiments.
Finally, it should be noted that: the above examples are only intended to illustrate the technical solution of the present invention, but not to limit it; although the present invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some technical features may be equivalently replaced; and such modifications or substitutions do not depart from the spirit and scope of the corresponding technical solutions of the embodiments of the present invention.
Claims (6)
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| CN114332947A (en) * | 2021-12-31 | 2022-04-12 | 深圳市儿童医院 | Image classification system and terminal equipment |
| CN114460513A (en) * | 2022-01-12 | 2022-05-10 | 浙江大学 | A kind of fast in vivo imaging method, calculation method and system of blood T1 and T2 |
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