WO2023122919A1 - 心脏磁共振弥散张量成像方法、装置、设备及存储介质 - Google Patents

心脏磁共振弥散张量成像方法、装置、设备及存储介质 Download PDF

Info

Publication number
WO2023122919A1
WO2023122919A1 PCT/CN2021/141815 CN2021141815W WO2023122919A1 WO 2023122919 A1 WO2023122919 A1 WO 2023122919A1 CN 2021141815 W CN2021141815 W CN 2021141815W WO 2023122919 A1 WO2023122919 A1 WO 2023122919A1
Authority
WO
WIPO (PCT)
Prior art keywords
detection sequence
diastolic
myocardium
imaging
systolic
Prior art date
Application number
PCT/CN2021/141815
Other languages
English (en)
French (fr)
Inventor
朱燕杰
徐溪
梁栋
刘新
郑海荣
Original Assignee
中国科学院深圳先进技术研究院
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 中国科学院深圳先进技术研究院 filed Critical 中国科学院深圳先进技术研究院
Priority to PCT/CN2021/141815 priority Critical patent/WO2023122919A1/zh
Publication of WO2023122919A1 publication Critical patent/WO2023122919A1/zh

Links

Images

Classifications

    • 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

Definitions

  • the present invention relates to the field of magnetic resonance technology, in particular to a cardiac magnetic resonance diffusion tensor imaging method, device, equipment and storage medium.
  • Cardiac diffusion tensor imaging technology can characterize early changes in myocardial microstructure, and changes in characteristic parameters during systole and diastole can reflect changes in myocardial activity. important.
  • each layer of myocardium needs to collect multiple (generally more than 6, usually 10) images of different diffusion coding directions and a reference image without applying a diffusion coding gradient to perform tensor simulation. Summing up and solving for quantitative parameters.
  • the current cardiac diffusion tensor imaging method usually uses a stimulus echo sequence imaging method or a spin echo-echo planar sequence imaging method to collect diffusion signals of the myocardium layer by layer and in a single phase.
  • the stimulation echo sequence imaging method is less affected by cardiac motion, and usually requires breath-hold acquisition, and in order to ensure the recovery of single-layer signals during imaging, the signal-to-noise ratio of the imaging image is low, and it needs to go through two cardiac cycles (one cardiac cycle). cycle consists of a systole and a diastole) to acquire an image.
  • the spin echo-planar echo sequence imaging method can complete single-layer, single-direction, and single-phase imaging within one cardiac cycle, and does not require the subject to hold his or her breath during the imaging process, in order to ensure single-layer, single-phase imaging during imaging
  • one image is usually collected at intervals of one cardiac cycle, so that the acquisition of a single image requires 2 cardiac cycles.
  • the imaging time required for each diffusion-weighted direction is the number of layers * the number of phases *Single image acquisition time (2 cardiac cycles), resulting in a long overall time for cardiac magnetic resonance diffusion tensor imaging, which limits the clinical application of this technique.
  • Embodiments of the present invention provide a cardiac magnetic resonance diffusion tensor imaging method, device, equipment, and storage medium, which can realize the contraction of each cardiac cycle under the premise of ensuring a good signal-to-noise ratio of cardiac magnetic resonance diffusion tensor imaging images.
  • a single imaging is performed on a single target myocardium during phase and diastole respectively, which improves the efficiency of magnetic resonance diffusion tensor imaging of the heart.
  • An embodiment of the present invention provides a cardiac magnetic resonance diffusion tensor imaging method, comprising:
  • each of the systolic phase and each of the diastolic phases performs a single imaging on a single target myocardium, and the time interval between the systolic imaging and the diastolic imaging of the same target myocardium is N Cardiac cycle; N is an integer and greater than or equal to 2.
  • the magnetic resonance diffusion is respectively performed on each of the target myocardium in the systolic phase and the diastolic phase of multiple continuous cardiac cycles of the subject to be detected.
  • Tensor imaging detection including:
  • the interval between systolic imaging and diastolic imaging of the same target myocardium in the same diffusion weighted gradient direction is N cardiac cycles.
  • the magnetic resonance diffusion dilation is performed on each target myocardium in sequence based on the systolic phase detection sequence and the diastolic phase detection sequence in the systolic phase and diastolic phase of multiple cardiac cycles of the subject to be detected.
  • Quantitative imaging inspection including:
  • the first preset time and the second preset time are preset according to the heart cine image of the subject to be detected.
  • the magnetic resonance diffusion dilation is performed on each target myocardium in sequence based on the systolic phase detection sequence and the diastolic phase detection sequence in the systolic phase and diastolic phase of multiple cardiac cycles of the subject to be detected.
  • Quantitative imaging inspection including:
  • Excitation imaging is performed on the current target myocardium to be imaged based on the adjusted excitation position of the slice.
  • the adjustment of the layer excitation position of the target myocardium to be imaged based on the respiratory navigation information of the subject under free breathing state includes:
  • the excitation position of the reference layer of the current target myocardium to be imaged obtained in the standard state is adjusted based on the cardiac displacement.
  • the standard state is a breath-hold state at the end of expiration.
  • the acquisition of the systolic detection sequence and the diastolic detection sequence of multiple target myocardium of the person to be detected includes:
  • the target myocardium of each odd-numbered layer is arranged first, and then the target myocardium of an even-numbered layer is arranged.
  • the target myocardium of each even-numbered layer is arranged first, and then the target myocardium of each odd-numbered layer is arranged;
  • the target myocardium of each odd-numbered layer is first arranged and then the target myocardium of each even-numbered layer is arranged; In the other of the systolic phase detection sequence and the diastolic phase detection sequence, the target myocardium of one odd-numbered layer is arranged first, then the target myocardium of each even-numbered layer is arranged, and finally the target myocardium of the remaining odd-numbered layers is arranged.
  • Another embodiment of the present invention provides a cardiac magnetic resonance diffusion tensor imaging device, including:
  • Myocardium detection sequence acquisition module used to obtain the systolic detection sequence and diastolic detection sequence of multiple target myocardium of the person to be detected;
  • the diffusion tensor imaging detection module is used to, based on the systolic phase detection sequence and the diastolic phase detection sequence, sequentially perform magnetic field tests on each of the target myocardium in the systolic phase and diastolic phase of multiple continuous cardiac cycles of the subject to be detected.
  • Resonant diffusion tensor imaging detection
  • each of the systolic phase and each of the diastolic phases performs a single imaging on a single target myocardium, and the time interval between the systolic imaging and the diastolic imaging of the same target myocardium is N Cardiac cycle; N is an integer and greater than or equal to 2.
  • Another embodiment of the present invention provides a storage medium, the computer-readable storage medium includes a stored computer program, wherein when the computer program is running, the device where the computer-readable storage medium is located is controlled to execute the above-mentioned embodiment of the invention
  • the cardiac magnetic resonance diffusion tensor imaging method is also provided.
  • each of the target myocardium is sequentially detected by magnetic resonance diffusion tensor imaging in the systolic phase and the diastolic phase of multiple continuous cardiac cycles of the subject to be detected, wherein , performing a single imaging on a single target myocardium in each systole and each diastole, so that the imaging efficiency is doubled compared with the prior art, and the systole of the same target myocardium
  • the time interval between imaging and diastolic imaging is at least 2 cardiac cycles, which can ensure a good signal-to-noise ratio of cardiac magnetic resonance diffusion tensor imaging images. It can be seen that the embodiments of the present invention can improve the efficiency of magnetic resonance diffusion tensor imaging of the heart on the premise of ensuring a good signal-to-noise ratio of the cardiac magnetic resonance diffusion tensor imaging image.
  • Fig. 1 is a schematic flow chart of a cardiac magnetic resonance diffusion tensor imaging method provided by an embodiment of the present invention
  • FIG. 2 is a schematic diagram of triggering systolic and diastolic imaging of the target myocardium in an embodiment of the present invention
  • Fig. 3 is a schematic diagram of the imaging sequence of each target myocardium imaging in different diffusion weighted gradient directions in different cardiac cycles in an embodiment of the present invention
  • Fig. 4 is an imaging diagram of each target myocardium in systole and diastole in one of the diffusion weighted gradient directions in one embodiment of the present invention
  • Fig. 5 is a schematic structural diagram of a cardiac magnetic resonance diffusion tensor imaging device provided by an embodiment of the present invention.
  • Fig. 6 is a schematic structural diagram of a cardiac magnetic resonance diffusion tensor imaging device provided by an embodiment of the present invention.
  • FIG. 1 it is a schematic flowchart of a cardiac magnetic resonance diffusion tensor imaging method provided by an embodiment of the present invention.
  • the execution body of the method is a cardiac magnetic resonance diffusion tensor imaging device, and the method includes steps S10 to S11:
  • each of the systolic phase and each of the diastolic phases is respectively imaged on a single target myocardium, and the time interval between systolic imaging and diastolic imaging of the same target myocardium is N cardiac cycles ; N is an integer and greater than or equal to 2.
  • the imaging of all the target myocardium can be continuously completed in the direction of the same diffusion weighted gradient; wherein, the same target myocardium in the direction of the same diffusion weighted gradient
  • the interval between imaging is N cardiac cycles. It can be understood that, after completing the imaging of all target myocardium in each cardiac cycle under the diffusion weighted gradient direction of the first target, the above process can be repeated until the imaging of all target myocardium in each cardiac cycle under the diffusion weighted gradient direction of all targets is completed. periodic imaging.
  • magnetic resonance is performed on each of the target myocardium in sequence in the systolic phase and the diastolic phase of multiple consecutive cardiac cycles of the subject to be detected.
  • Diffusion tensor imaging detection wherein a single imaging is performed on a single target myocardium in each systolic period and each diastolic period, so that the imaging efficiency is doubled compared with the prior art, and the same institute
  • the time interval between systolic imaging and diastolic imaging of the target myocardium is at least 2 cardiac cycles, which can ensure a good signal-to-noise ratio of cardiac magnetic resonance diffusion tensor imaging images. It can be seen that the embodiment of the present invention can improve the efficiency of magnetic resonance diffusion tensor imaging of the heart under the premise of ensuring a good signal-to-noise ratio of the cardiac magnetic resonance diffusion tensor imaging image.
  • step S11 includes step S110 to step S111:
  • the existing electrocardiographic trigger acquisition technology may be used to detect the current electrocardiographic signal of the subject to be detected.
  • the first preset time and the second preset time are preset according to the heart movie image of the person to be detected.
  • the specified waveform is the R wave of the ECG signal.
  • the systolic phase of the target myocardium begins to enter the target myocardium at the first preset time TD1 after the R wave is detected each time (the systolic phase is generally 0.1-0.3 seconds, and the timing of the systolic phase is different for different people to be detected) , starting to trigger systolic imaging of the target myocardium at this time.
  • the diastolic period (generally 0.5-0.7 seconds, different diastolic moments of different people to be detected) that begins to enter the target myocardium at the second preset time TD2 after detecting the R wave each time is the diastolic period, at this time Diastolic imaging of the target myocardium is initiated.
  • relevant imaging can be realized by a single excitation echo-planar technique: after 90° pulse excitation is performed at the excitation position, a preset diffusion weighted gradient is applied Pulse, followed by a 180° pulse to perform phase refocusing on the initial diffused signal; apply a preset diffusion-weighted gradient pulse to the phase-refocused signal to obtain a diffusion-weighted myocardial signal; The diffusion-weighted myocardial signal is collected, and finally the diffusion-weighted image of the currently selected myocardium under the current diffusion-weighted gradient direction is obtained after reconstruction.
  • the process of setting the first preset time and the second preset time according to the cardiac cine image of the subject to be detected can refer to the existing cardiac cine image analysis technology, which will not be repeated here.
  • step S11 includes step S110' to step S111':
  • step S110' includes step S1100' to step S1100':
  • the subject to be tested in the process of magnetic resonance diffusion tensor imaging of the heart of the subject to be tested, the subject to be tested does not need to hold his breath, so that the subject to be tested does not need to have a high degree of compliance, and the subject's ability to be tested is improved. comfort.
  • the heart-diaphragm displacement correlation coefficient is 0.6. It can be understood that the heart-diaphragm displacement correlation coefficient can also be calculated by means of personalized fitting calculation, so that the heart-diaphragm displacement correlation coefficient is more in line with the current subject to be detected.
  • the standard state is a breath-hold state at the end of expiration.
  • the step S10 includes:
  • the target myocardium of each odd-numbered layer is arranged first, and then the target myocardium of an even-numbered layer is arranged.
  • the target myocardium of each even-numbered layer is arranged first, and then the target myocardium of each odd-numbered layer is arranged;
  • the target myocardium of each odd-numbered layer is first arranged and then the target myocardium of each even-numbered layer is arranged; In the other of the systolic phase detection sequence and the diastolic phase detection sequence, the target myocardium of one odd-numbered layer is arranged first, then the target myocardium of each even-numbered layer is arranged, and finally the target myocardium of the remaining odd-numbered layers is arranged.
  • the systolic detection sequence and diastolic detection sequence of each target myocardium are shown in Table 1, which can ensure that the diffusion signal of the myocardial diffusion tensor imaging has a recovery time of at least 2 cardiac cycles , so as to ensure a good signal-to-noise ratio of the cardiac magnetic resonance diffusion tensor imaging image.
  • Table 1 in the case that the number of the target myocardium is 6 layers, in the systolic detection sequence, the odd-numbered layers of the myocardium 1, 5, and 3 are first arranged, and then the even-numbered layers of the myocardium 6 are arranged. . There is a recovery time of 2 cardiac cycles.
  • the 6, 2, and 4 of the even-numbered layers can also be arranged first, and then the 1, 5, and 3 of the odd-numbered layers;
  • the odd-numbered myocardium 1, 5, and 3 may be arranged first, and then the even-numbered myocardium 6, 2, and 4 may be arranged.
  • the number of target myocardium that requires diffusion tensor imaging is 5 layers as an example, it is necessary to image the target myocardium in each diffusion weighted gradient direction through 5 cardiac cycles, for example, the first diffusion
  • the number of cardiac cycles under the weighted gradient direction (D1) is the first 5 cardiac cycles in Fig. 3 .
  • the magnetic resonance diffusion tensor imaging detection of each target myocardium during the systolic and diastolic periods of each cardiac cycle can refer to the above process.
  • FIG. 5 it is a schematic structural diagram of a cardiac magnetic resonance diffusion tensor imaging device provided by an embodiment of the present invention.
  • the devices include:
  • Myocardium detection sequence acquisition module 10 used to obtain the systolic detection sequence and diastolic detection sequence of multiple target myocardium of the person to be detected;
  • the diffusion tensor imaging detection module 11 is configured to, based on the systolic phase detection sequence and the diastolic phase detection sequence, sequentially detect each of the target myocardium in the systolic phase and the diastolic phase of a plurality of consecutive cardiac cycles of the subject to be detected. Magnetic resonance diffusion tensor imaging detection;
  • each of the systolic phase and each of the diastolic phases performs a single imaging on a single target myocardium, and the time interval between the systolic imaging and the diastolic imaging of the same target myocardium is N Cardiac cycle; N is an integer and greater than or equal to 2.
  • magnetic resonance is performed on each of the target myocardium in sequence in the systolic phase and the diastolic phase of multiple consecutive cardiac cycles of the subject to be detected.
  • Diffusion tensor imaging detection wherein a single imaging is performed on a single target myocardium in each systolic period and each diastolic period, so that the imaging efficiency is doubled compared with the prior art, and the same institute
  • the time interval between systolic imaging and diastolic imaging of the target myocardium is at least 2 cardiac cycles, which can ensure a good signal-to-noise ratio of cardiac magnetic resonance diffusion tensor imaging images. It can be seen that the embodiments of the present invention can improve the efficiency of magnetic resonance diffusion tensor imaging of the heart on the premise of ensuring a good signal-to-noise ratio of the cardiac magnetic resonance diffusion tensor imaging image.
  • the diffusion tensor imaging detection module 11 is specifically used for:
  • the interval between systolic imaging and diastolic imaging of the same target myocardium in the same diffusion weighted gradient direction is N cardiac cycles.
  • the diffusion tensor imaging detection module 11 is specifically used for:
  • the first preset time and the second preset time are preset according to the heart cine image of the subject to be detected.
  • the diffusion tensor imaging detection module is specifically used for:
  • Excitation imaging is performed on the current target myocardium to be imaged based on the adjusted excitation position of the slice.
  • the diffusion tensor imaging detection module 11 is used for:
  • the excitation position of the reference layer of the current target myocardium to be imaged obtained in the standard state is adjusted based on the cardiac displacement.
  • the standard state is a breath-hold state at the end of expiration.
  • the acquisition module 10 of the detection order of the myocardium is specifically used for:
  • the target myocardium of each odd-numbered layer is arranged first, and then the target myocardium of an even-numbered layer is arranged.
  • the target myocardium of each even-numbered layer is arranged first, and then the target myocardium of each odd-numbered layer is arranged;
  • the target myocardium of each odd-numbered layer is first arranged and then the target myocardium of each even-numbered layer is arranged; In the other of the systolic phase detection sequence and the diastolic phase detection sequence, the target myocardium of one odd-numbered layer is arranged first, then the target myocardium of each even-numbered layer is arranged, and finally the target myocardium of the remaining odd-numbered layers is arranged.
  • FIG. 6 it is a schematic diagram of a cardiac magnetic resonance diffusion tensor imaging device provided by an embodiment of the present invention.
  • the cardiac magnetic resonance diffusion tensor imaging device of this embodiment includes: a processor 100, a memory 101, and a computer program stored in the memory 101 and operable on the processor 100, such as cardiac magnetic resonance diffusion tensor imaging program.
  • the processor 100 executes the computer program, it implements the steps in the above embodiments of the cardiac magnetic resonance diffusion tensor imaging method, for example, the cardiac magnetic resonance diffusion tensor imaging step shown in FIG. 1 .
  • functions of the modules/units in the above-mentioned device embodiments, such as cardiac magnetic resonance diffusion tensor imaging are implemented.
  • the computer program can be divided into one or more modules/units, and the one or more modules/units are stored in the memory and executed by the processor to complete the present invention.
  • the one or more modules/units may be a series of computer program instruction segments capable of accomplishing specific functions, and the instruction segments are used to describe the execution process of the computer program in the cardiac magnetic resonance diffusion tensor imaging device.
  • the cardiac magnetic resonance diffusion tensor imaging device may include, but not limited to, a processor and a memory.
  • a processor and a memory.
  • the schematic diagram is only an example of cardiac magnetic resonance diffusion tensor imaging equipment, and does not constitute a limitation to cardiac magnetic resonance diffusion tensor imaging equipment, and may include more or less components than those shown in the illustration , or combine certain components, or different components, for example, the cardiac magnetic resonance diffusion tensor imaging device may also include input and output devices, network access devices, buses, and the like.
  • the so-called processor can be a central processing unit (Central Processing Unit, CPU), and can also be other general-purpose processors, digital signal processors (Digital Signal Processor, DSP), application specific integrated circuits (Application Specific Integrated Circuit, ASIC), off-the-shelf Programmable gate array (Field-Programmable Gate Array, FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc.
  • the general-purpose processor can be a microprocessor or the processor can also be any conventional processor, etc., and the processor is the control center of the cardiac magnetic resonance diffusion tensor imaging device, and uses various interfaces and lines to connect the entire heart Parts of an MRI Diffusion Tensor Imaging facility.
  • the memory can be used to store the computer programs and/or modules, and the processor implements the heart by running or executing the computer programs and/or modules stored in the memory and calling the data stored in the memory.
  • Various functions of the MRI Diffusion Tensor Imaging Equipment may mainly include a program storage area and a data storage area, wherein the program storage area may store an operating system, at least one application program required by a function (such as a sound playback function, an image playback function, etc.) and the like; the storage data area may store Data created based on the use of the mobile phone (such as audio data, phonebook, etc.), etc.
  • the memory can include high-speed random access memory, and can also include non-volatile memory, such as hard disk, internal memory, plug-in hard disk, smart memory card (Smart Media Card, SMC), secure digital (Secure Digital, SD) card , flash card (Flash Card), at least one magnetic disk storage device, flash memory device, or other volatile solid-state storage device.
  • non-volatile memory such as hard disk, internal memory, plug-in hard disk, smart memory card (Smart Media Card, SMC), secure digital (Secure Digital, SD) card , flash card (Flash Card), at least one magnetic disk storage device, flash memory device, or other volatile solid-state storage device.
  • the integrated modules/units of the cardiac magnetic resonance diffusion tensor imaging device are realized in the form of software function units and sold or used as independent products, they can be stored in a computer-readable storage medium.
  • the present invention realizes all or part of the processes in the methods of the above embodiments, and can also be completed by instructing related hardware through a computer program.
  • the computer program can be stored in a computer-readable storage medium, and the computer When the program is executed by the processor, the steps in the above-mentioned various method embodiments can be realized.
  • the computer program includes computer program code, and the computer program code may be in the form of source code, object code, executable file or some intermediate form.
  • the computer-readable medium may include: any entity or device capable of carrying the computer program code, a recording medium, a USB flash drive, a removable hard disk, a magnetic disk, an optical disk, a computer memory, and a read-only memory (ROM, Read-Only Memory) , Random Access Memory (RAM, Random Access Memory), electrical carrier signal, telecommunication signal and software distribution medium, etc.
  • ROM Read-Only Memory
  • RAM Random Access Memory
  • electrical carrier signal telecommunication signal and software distribution medium, etc.
  • the device embodiments described above are only illustrative, and the units described as separate components may or may not be physically separated, and the components shown as units may or may not be physically separated.
  • a unit can be located in one place, or it can be distributed to multiple network units. Part or all of the modules can be selected according to actual needs to achieve the purpose of the solution of this embodiment.
  • the connection relationship between the modules indicates that they have a communication connection, which can be specifically implemented as one or more communication buses or signal lines. It can be understood and implemented by those skilled in the art without creative effort.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Radiology & Medical Imaging (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Magnetic Resonance Imaging Apparatus (AREA)

Abstract

一种心脏磁共振弥散张量成像方法、装置、设备及存储介质，能够在保证心脏磁共振弥散张量成像图像的信噪比良好的前提下，提高对心脏的磁共振弥散张量成像的效率，成像方法包括：获取待检测者的多个目标心肌层(S1, S2, S3, S4, S5)的收缩期检测顺序和舒张期检测顺序(S10)；基于收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各目标心肌层(S1, S2, S3, S4, S5)进行磁共振弥散张量成像检测(S11)；其中，每个收缩期和每个舒张期分别对单个目标心肌层(S1, S2, S3, S4, S5)进行成像，同一目标心肌层(S1, S2, S3, S4, S5)的收缩期成像与舒张期成像之间的最小时间间隔为N个心动周期；N为整数且大于或等于2。

Description

心脏磁共振弥散张量成像方法、装置、设备及存储介质 【技术领域】
本发明涉及磁共振技术领域，尤其涉及一种心脏磁共振弥散张量成像方法、装置、设备及存储介质。
【背景技术】
心脏弥散张量成像技术可以表征心肌微结构的早期变化，在收缩期和舒张期的特征参数变化可反应心肌活性变化，所以采集收缩期和舒张期的特征参数变化，对于分析心肌结构变化至关重要。在心脏弥散张量成像模型中，每层心肌需要采集多个(一般6个以上，通常为10个)不同弥散编码方向的图像和1张不施加弥散编码梯度的参考图像来进行张量的拟合和定量参数的求解。目前的心脏弥散张量成像方式通常使用刺激回波序列成像方式或自旋回波-平面回波序列成像方式，以对心肌进行逐层、单个期相的弥散信号采集。其中，刺激回波序列成像方式受心脏运动影响较小，通常需要屏气采集，且为了保证成像时单层信号的恢复而使得成像的图像信噪比较低，需要经两个心动周期(一个心动周期由一个收缩期和一个舒张期组成)才能采集一幅图像。而自旋回波-平面回波序列成像方式虽然可以在一个心动周期内完成单层、单方向、单期相的成像，且在成像过程中并不需要待检测者屏气，但为了保证成像时单层信号的恢复，通常会间隔一个心动周期采集一幅图像，使得采集单幅图像需要2个心动周期。
由上分析可知，当前常用的心脏弥散张量成像方式在采集心脏的多层、多期相、多弥散加权方向的图像时，每个弥散加权方向下需要的成像时间为层数*期相数*单幅图像采集时间(2个心动周期)，导致心脏磁共振弥散张量成像的总体时间过长，限制了该技术的临床应用。
【发明内容】
本发明实施例提供一种心脏磁共振弥散张量成像方法、装置、设备及存储介质，能在保证心脏磁共振弥散张量成像图像的信噪比良好的前提下，实现每 个心动周期的收缩期和舒张期分别对单个所述目标心肌层进行单次成像，提高了对心脏的磁共振弥散张量成像的效率。
本发明一实施例提供一种心脏磁共振弥散张量成像方法，包括：
获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序；
基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测；
其中，每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行单次成像，同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为N个心动周期；N为整数且大于或等于2。
作为上述方案的改进，所述基于所述收缩期检测顺序和舒张期检测顺序依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，包括：
在同一弥散加权梯度方向下连续完成所有所述目标心肌层的成像；
其中，同一所述目标心肌层在所述同一弥散加权梯度方向的收缩期成像与舒张期成像之间的间隔为N个心动周期。
作为上述方案的改进，所述基于所述收缩期检测顺序和舒张期检测顺序依次在待检测者的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，包括：
检测所述待检测者的心电信号；
在检测到所述心电信号的指定波形后，延迟第一预设时间触发所述目标心肌层的收缩期成像，并在延迟第二预设时间触发所述目标心肌层的舒张期成像；
其中，所述第一预设时间和第二预设时间根据所述待检测者的心脏电影图像预先设置。
作为上述方案的改进，所述基于所述收缩期检测顺序和舒张期检测顺序依次在待检测者的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，包括：
基于所述待测者在自由呼吸状态下的呼吸导航信息对当前待成像的目标心肌层的层激发位置进行调整；
基于调整后的层激发位置对所述当前待成像的目标心肌层进行激发成像。
作为上述方案的改进，所述基于所述待测者在自由呼吸状态下的呼吸导航 信息对当前待成像的目标心肌层的层激发位置进行调整，包括：
基于所述呼吸导航信息确定所述待测者的膈肌的当前位置；
计算所述膈肌的当前位置与标准状态下获得的基准膈肌位置之间的膈肌位移量；
根据所述膈肌位移量和预设的心脏-膈肌位移相关系数计算系数计算心脏位移量；
基于所述心脏位移量对所述标准状态下获得的所述当前待成像的目标心肌层的基准层激发位置进行调整。
作为上述方案的改进，所述标准状态为呼气末期的屏气状态。
作为上述方案的改进，所述获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序，包括：
当所述目标心肌层的数量为偶数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列个偶数层的目标心肌层，在所述收缩期检测顺序和舒张期检测顺序中的另一者中先排列各偶数层的目标心肌层再排列各奇数层的目标心肌层；
当所述目标心肌层的数量为奇数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列各偶数层的目标心肌层；在所述收缩期检测顺序和舒张期检测顺序中的另一者中，先排列其中一奇数层的目标心肌层，接着排列各偶数层的目标心肌层，最后排列其余奇数层的目标心肌层。
本发明另一实施例对应提供了一种心脏磁共振弥散张量成像装置，包括：
心肌层检测顺序获取模块，用于获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序；
弥散张量成像检测模块，用于基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测；
其中，每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行单次成像，同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为N个心动周期；N为整数且大于或等于2。
本发明另一实施例提供了一种心脏磁共振弥散张量成像设备，包括处理器、存储器以及存储在所述存储器中且被配置为由所述处理器执行的计算机程序， 所述处理器执行所述计算机程序时实现上述发明实施例所述的心脏磁共振弥散张量成像方法。
本发明另一实施例提供了一种存储介质，所述计算机可读存储介质包括存储的计算机程序，其中，在所述计算机程序运行时控制所述计算机可读存储介质所在设备执行上述发明实施例所述的心脏磁共振弥散张量成像方法。
相比于现有技术，上述技术方案中的一个技术方案具有如下至少一个优点：
通过基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，其中，在每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行单次成像，这样成像效率相比现有技术提高一倍，并且同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为至少2个心动周期，这样能够保证心脏磁共振弥散张量成像图像的信噪比良好。由此可见，本发明实施例能够在保证心脏磁共振弥散张量成像图像的信噪比良好的前提下，提高对心脏的磁共振弥散张量成像的效率。
【附图说明】
为了更清楚地说明本发明实施例中的技术方案，下面将对实施例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。其中：
图1是本发明一实施例提供的一种心脏磁共振弥散张量成像方法的流程示意图；
图2是本发明一实施例中的触发目标心肌层的收缩期和舒张期成像的示意图；
图3是本发明一实施例中的对不同弥散加权梯度方向下不同心动周期的各目标心肌层成像的成像顺序示意图；
图4是本发明一实施例中的其中一个弥散加权梯度方向下的收缩期和舒张期的各目标心肌层的成像图；
图5是本发明一实施例提供的一种心脏磁共振弥散张量成像装置的结构示意图；
图6是本发明一实施例提供的一种心脏磁共振弥散张量成像设备的结构示意图。
【具体实施方式】
下面将结合本发明实施例中的附图，对本发明实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本发明一部分实施例，而不是全部的实施例。基于本发明中的实施例，本领域普通技术人员在没有作出创造性劳动前提下所获得的所有其他实施例，都属于本发明保护的范围。
参见图1，是本发明一实施例提供的一种心脏磁共振弥散张量成像方法的流程示意图。所述方法的执行主体为心脏磁共振弥散张量成像设备，所述方法包括步骤S10至步骤S11：
S10，获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序。
S11，基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测。
其中，每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行成像，同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为N个心动周期；N为整数且大于或等于2。
作为举例的，在本步骤中可以在同一弥散加权梯度方向下连续完成所有所述目标心肌层的成像；其中，同一所述目标心肌层在所述同一弥散加权梯度方向的收缩期成像与舒张期成像之间的间隔为N个心动周期。可以理解的是，当完成首个目标的弥散加权梯度方向下所有目标心肌层在各心动周期的成像后，可以重复上述过程，直至完成所有目标的弥散加权梯度方向下所有目标心肌层在各心动周期的成像。
在本发明实施例中，通过基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，其中，在每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行单次成像，这样成像效率相比现有技术提高一倍，并且同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为至少2个心动周期，这样能够保证心脏磁共振弥散张量成像图像的信噪比良好。由此可见，本发明实施例能够在保证心脏磁共振弥散张量成像图像的信噪比良 好的前提下，提高对心脏的磁共振弥散张量成像的效率。
在其中一个实施例中，具体的，所述步骤S11包括步骤S110至步骤S111：
S110，检测所述待检测者的心电信号。
作为示例的，可以采用现有的心电触发采集技术来检测待检测者当前的心电信号。
S111，在检测到所述心电信号的指定波形后，延迟第一预设时间触发所述目标心肌层的收缩期成像，并在延迟第二预设时间触发所述目标心肌层的舒张期成像；其中，所述第一预设时间和第二预设时间根据所述待检测者的心脏电影图像预先设置。
作为举例的，所述指定波形为心电信号的R波。参见图2，在距离每次检测到R波后的第一预设时间TD1时开始进入目标心肌层的收缩期(收缩期一般为0.1-0.3秒，不同待检测者的收缩期的时刻不同)，此时开始触发对所述目标心肌层的收缩期成像。在距离每次检测到R波后的第二预设时间TD2时开始进入目标心肌层的舒张期(一般为0.5-0.7秒，不同待检测者的舒张期的时刻不同)为舒张期，此时开始触发对所述目标心肌层的舒张期成像。其中，在触发所述目标心肌层的收缩期或舒张期的成像时，可以通过单次激发平面回波技术来实现相关成像：在激发位置进行90°脉冲激发后，施加预设的弥散加权梯度脉冲，之后180°脉冲对初步弥散的信号进行相位回聚；对相位回聚后的信号施加预设的弥散加权梯度脉冲，得到弥散加权心肌信号；通过单次激发平面回波技术对待检测者心脏的弥散加权心肌信号进行采集，最后经过重建得到当前选定心肌层在当前弥散加权梯度方向下的弥散加权图像。
作为示例的，所述第一预设时间和第二预设时间根据所述待检测者的心脏电影图像设置的过程，可以参考现有的心脏电影图像分析技术，在此不做赘述。
在其中一个实施例中，具体的，所述步骤S11包括步骤S110’至步骤S111’：
S110’，基于所述待测者在自由呼吸状态下的呼吸导航信息对当前待成像的目标心肌层的层激发位置进行调整。
具体的，所述步骤S110’包括步骤S1100’至步骤S1100’：
S1100’，基于所述呼吸导航信息确定所述待测者的膈肌的当前位置；
S1101’，计算所述膈肌的当前位置与标准状态下获得的基准膈肌位置之间的膈肌位移量；
S1102’，根据所述膈肌位移量和预设的心脏-膈肌位移相关系数计算心脏位 移量；
S1103’，基于所述心脏位移量对所述标准状态下获得的所述当前待成像的目标心肌层的基准层激发位置进行调整。
S111’，基于调整后的层激发位置对所述当前待成像的目标心肌层进行激发成像。
在本实施例中，在自由呼吸状态下，通过结合自旋回波-平面回波成像的呼吸导航跟随技术，利用所述膈肌的当前位置与标准状态下的基准膈肌位置之间的膈肌位移量和预设的心脏-膈肌位移相关系数，来计算当前的心脏位移量，然后基于所述心脏位移量对所述标准状态下获得的所述当前待成像的目标心肌层的基准层激发位置进行调整，这样能够实现在自由呼吸状态下对待检测者进行正常的心脏磁共振弥散张量成像。由此可见，采用本发明实施例，在对待检测者进行心脏的磁共振弥散张量成像过程中，待检测者无需屏气，这样无需待检测者具有较高的依从性，提高了待检测者的舒适度。
作为示例的，所述心脏-膈肌位移相关系数为0.6。可以理解的是，所述心脏-膈肌位移相关系数也可以是使用个性化拟合计算的方式来计算得到，从而使得心脏-膈肌位移相关系数更符合当前的待检测者。
作为示例的，所述标准状态为呼气末期的屏气状态。
在其中一个实施例中，具体的，所述步骤S10包括：
当所述目标心肌层的数量为偶数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列个偶数层的目标心肌层，在所述收缩期检测顺序和舒张期检测顺序中的另一者中先排列各偶数层的目标心肌层再排列各奇数层的目标心肌层；
当所述目标心肌层的数量为奇数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列各偶数层的目标心肌层；在所述收缩期检测顺序和舒张期检测顺序中的另一者中，先排列其中一奇数层的目标心肌层，接着排列各偶数层的目标心肌层，最后排列其余奇数层的目标心肌层。
为了便于理解，作为举例的，各目标心肌层的收缩期检测顺序和舒张期检测顺序如表1所示，这样可以保证对心肌进行弥散张量成像的弥散信号至少有2个心动周期的恢复时间，从而能够保证心脏磁共振弥散张量成像图像的信噪比良好。例如参见表1，在所述目标心肌层的数量为6层的情况下，在所述收缩期 检测顺序中，先排列奇数层的心肌层1、5、3，再排列偶数层的心肌层6、2、4；在所述舒张期检测顺序中，先排列偶数层的6、2、4，再排列奇数层的1、5、3，这样可以保证对心肌进行弥散张量成像的弥散信号至少有2个心动周期的恢复时间。当然，在所述目标心肌层的数量为6层的情况下，在所述收缩期检测顺序中，也可以先排列偶数层的6、2、4，再排列奇数层的1、5、3；在所述舒张期检测顺序中，也可以先排列奇数层的心肌层1、5、3，再排列偶数层的心肌层6、2、4。
表1.各目标心肌层的收缩期检测顺序和舒张期检测顺序示例表
Figure PCTCN2021141815-appb-000001
当在成像完一个弥散加权梯度方向的收缩期和舒张期的各目标心肌层图像之后，再成像下一个弥散加权梯度方向的收缩期和舒张期的各目标心肌层图像。为了便于理解，在此进行如下举例说明：
参见图3，以当需要弥散张量成像的目标心肌层的数量为5层为例，需要通过5个心动周期来对每个弥散加权梯度方向下的目标心肌层成像，例如，第一个弥散加权梯度方向(D1)下的心动周期数量为图3中的前面5个心动周期。在进行第一个弥散加权梯度方向(D1)的弥散张量成像过程中,相继成像第1、5、3、2、4目标心肌层(S1、S5、S3、S2、S4)的收缩期和3、2、4、5、1心肌层(S3、S2、S4、S5、S1)的舒张期，使得同一目标心肌层的收缩期成像与舒张期成像之间的时间间隔为2个心动周期，各目标心肌层的成像图像请参见图4。在第二个弥散加权梯度方向(D2)和其余弥散加权梯度方向下下，对各个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测可以参照上述过程。通过以上方法，在弥散张量成像5个目标心肌层和10个弥散加权方向的情况下，成像时间共5*10＝50个心动周期(人类的心动周期一般少于1秒)，在1分钟内即可完成对10个弥散加权方向的收缩期和舒张期的5 个心肌层的弥散张量成像，而传统的方式按照：层数*弥散加权方向数*期相数*单幅图像采集时间(2个心动周期)来计算，则需5*10*2*2＝200个心动周期。
参见图5，是本发明一实施例提供的一种心脏磁共振弥散张量成像装置的结构示意图。所述装置包括：
心肌层检测顺序获取模块10，用于获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序；
弥散张量成像检测模块11，用于基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测；
其中，每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行单次成像，同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为N个心动周期；N为整数且大于或等于2。
在本发明实施例中，通过基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，其中，在每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行单次成像，这样成像效率相比现有技术提高一倍，并且同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为至少2个心动周期，这样能够保证心脏磁共振弥散张量成像图像的信噪比良好。由此可见，本发明实施例能够在保证心脏磁共振弥散张量成像图像的信噪比良好的前提下，提高对心脏的磁共振弥散张量成像的效率。
作为上述实施例的改进，所述弥散张量成像检测模块11具体用于：
在同一弥散加权梯度方向下连续完成所有所述目标心肌层的成像；
其中，同一所述目标心肌层在所述同一弥散加权梯度方向的收缩期成像与舒张期成像之间的间隔为N个心动周期。
作为上述实施例的改进，所述弥散张量成像检测模块11具体用于：
检测所述待检测者的心电信号；
在检测到所述心电信号的指定波形后，延迟第一预设时间触发所述目标心肌层的收缩期成像，并在延迟第二预设时间触发所述目标心肌层的舒张期成像；
其中，所述第一预设时间和第二预设时间根据所述待检测者的心脏电影图像预先设置。
作为上述实施例的改进，所述弥散张量成像检测模块具体用于：
基于所述待测者在自由呼吸状态下的呼吸导航信息对当前待成像的目标心肌层的层激发位置进行调整；
基于调整后的层激发位置对所述当前待成像的目标心肌层进行激发成像。
作为上述实施例的改进，更具体的，所述弥散张量成像检测模块11用于：
基于所述呼吸导航信息确定所述待测者的膈肌的当前位置；
计算所述膈肌的当前位置与标准状态下获得的基准膈肌位置之间的膈肌位移量；
根据所述膈肌位移量和预设的心脏-膈肌位移相关系数计算心脏位移量；
基于所述心脏位移量对所述标准状态下获得的所述当前待成像的目标心肌层的基准层激发位置进行调整。
作为上述实施例的改进，所述标准状态为呼气末期的屏气状态。
作为上述实施例的改进，所述心肌层检测顺序获取模块10具体用于：
当所述目标心肌层的数量为偶数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列个偶数层的目标心肌层，在所述收缩期检测顺序和舒张期检测顺序中的另一者中先排列各偶数层的目标心肌层再排列各奇数层的目标心肌层；
当所述目标心肌层的数量为奇数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列各偶数层的目标心肌层；在所述收缩期检测顺序和舒张期检测顺序中的另一者中，先排列其中一奇数层的目标心肌层，接着排列各偶数层的目标心肌层，最后排列其余奇数层的目标心肌层。
需要说明的是，上述各个心脏磁共振弥散张量成像装置的实施例可以对应参考上述心脏磁共振弥散张量成像方法实施例的相关内容，在此不做赘述。
参见图6，是本发明一实施例提供的心脏磁共振弥散张量成像设备的示意图。该实施例的心脏磁共振弥散张量成像设备包括：处理器100、存储器101以及存储在所述存储器101中并可在所述处理器100上运行的计算机程序，例如心脏磁共振弥散张量成像程序。所述处理器100执行所述计算机程序时实现上述各个心脏磁共振弥散张量成像方法实施例中的步骤，例如图1所示的步骤心脏磁共振弥散张量成像。或者，所述处理器100执行所述计算机程序时实现上述各装置实施例中各模块/单元的功能，例如心脏磁共振弥散张量成像。
示例性的，所述计算机程序可以被分割成一个或多个模块/单元，所述一个 或者多个模块/单元被存储在所述存储器中，并由所述处理器执行，以完成本发明。所述一个或多个模块/单元可以是能够完成特定功能的一系列计算机程序指令段，该指令段用于描述所述计算机程序在所述心脏磁共振弥散张量成像设备中的执行过程。
所述心脏磁共振弥散张量成像设备可包括，但不仅限于，处理器、存储器。本领域技术人员可以理解，所述示意图仅仅是心脏磁共振弥散张量成像设备的示例，并不构成对心脏磁共振弥散张量成像设备的限定，可以包括比图示更多或更少的部件，或者组合某些部件，或者不同的部件，例如所述心脏磁共振弥散张量成像设备还可以包括输入输出设备、网络接入设备、总线等。
所称处理器可以是中央处理单元(Central Processing Unit，CPU)，还可以是其他通用处理器、数字信号处理器(Digital Signal Processor，DSP)、专用集成电路(Application Specific Integrated Circuit，ASIC)、现成可编程门阵列(Field-Programmable Gate Array，FPGA)或者其他可编程逻辑器件、分立门或者晶体管逻辑器件、分立硬件组件等。通用处理器可以是微处理器或者该处理器也可以是任何常规的处理器等，所述处理器是所述心脏磁共振弥散张量成像设备的控制中心，利用各种接口和线路连接整个心脏磁共振弥散张量成像设备的各个部分。
所述存储器可用于存储所述计算机程序和/或模块，所述处理器通过运行或执行存储在所述存储器内的计算机程序和/或模块，以及调用存储在存储器内的数据，实现所述心脏磁共振弥散张量成像设备的各种功能。所述存储器可主要包括存储程序区和存储数据区，其中，存储程序区可存储操作系统、至少一个功能所需的应用程序(比如声音播放功能、图像播放功能等)等；存储数据区可存储根据手机的使用所创建的数据(比如音频数据、电话本等)等。此外，存储器可以包括高速随机存取存储器，还可以包括非易失性存储器，例如硬盘、内存、插接式硬盘，智能存储卡(Smart Media Card,SMC)，安全数字(Secure Digital,SD)卡，闪存卡(Flash Card)、至少一个磁盘存储器件、闪存器件、或其他易失性固态存储器件。
其中，所述心脏磁共振弥散张量成像设备集成的模块/单元如果以软件功能单元的形式实现并作为独立的产品销售或使用时，可以存储在一个计算机可读取存储介质中。基于这样的理解，本发明实现上述实施例方法中的全部或部分流程，也可以通过计算机程序来指令相关的硬件来完成，所述的计算机程序可 存储于一计算机可读存储介质中，该计算机程序在被处理器执行时，可实现上述各个方法实施例的步骤。其中，所述计算机程序包括计算机程序代码，所述计算机程序代码可以为源代码形式、对象代码形式、可执行文件或某些中间形式等。所述计算机可读介质可以包括：能够携带所述计算机程序代码的任何实体或装置、记录介质、U盘、移动硬盘、磁碟、光盘、计算机存储器、只读存储器(ROM，Read-Only Memory)、随机存取存储器(RAM，Random Access Memory)、电载波信号、电信信号以及软件分发介质等。需要说明的是，所述计算机可读介质包含的内容可以根据司法管辖区内立法和专利实践的要求进行适当的增减，例如在某些司法管辖区，根据立法和专利实践，计算机可读介质不包括电载波信号和电信信号。
需说明的是，以上所描述的装置实施例仅仅是示意性的，其中所述作为分离部件说明的单元可以是或者也可以不是物理上分开的，作为单元显示的部件可以是或者也可以不是物理单元，即可以位于一个地方，或者也可以分布到多个网络单元上。可以根据实际的需要选择其中的部分或者全部模块来实现本实施例方案的目的。另外，本发明提供的装置实施例附图中，模块之间的连接关系表示它们之间具有通信连接，具体可以实现为一条或多条通信总线或信号线。本领域普通技术人员在不付出创造性劳动的情况下，即可以理解并实施。
以上所述是本发明的优选实施方式，应当指出，对于本技术领域的普通技术人员来说，在不脱离本发明原理的前提下，还可以做出若干改进和润饰，这些改进和润饰也视为本发明的保护范围。

Claims (10)

  1. 一种心脏磁共振弥散张量成像方法，其特征在于，包括：
    获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序；
    基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测；
    其中，每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行成像，同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为N个心动周期；N为整数且大于或等于2。
  2. 如权利要求1所述的心脏磁共振弥散张量成像方法，所述基于所述收缩期检测顺序和舒张期检测顺序依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，包括：
    在同一弥散加权梯度方向下连续完成所有所述目标心肌层的成像；
    其中，同一所述目标心肌层在所述同一弥散加权梯度方向的收缩期成像与舒张期成像之间的间隔为N个心动周期。
  3. 如权利要求1所述的心脏磁共振弥散张量成像方法，所述基于所述收缩期检测顺序和舒张期检测顺序依次在待检测者的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，包括：
    检测所述待检测者的心电信号；
    在检测到所述心电信号的指定波形后，延迟第一预设时间触发所述目标心肌层的收缩期成像，并在延迟第二预设时间触发所述目标心肌层的舒张期成像；
    其中，所述第一预设时间和第二预设时间根据所述待检测者的心脏电影图像预先设置。
  4. 如权利要求1所述的心脏磁共振弥散张量成像方法，所述基于所述收缩期检测顺序和舒张期检测顺序依次在待检测者的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测，包括：
    基于所述待测者在自由呼吸状态下的呼吸导航信息对当前待成像的目标心肌层的层激发位置进行调整；
    基于调整后的层激发位置对所述当前待成像的目标心肌层进行激发成像。
  5. 如权利要求4所述的心脏磁共振弥散张量成像方法，其特征在于，所述 基于所述待测者在自由呼吸状态下的呼吸导航信息对当前待成像的目标心肌层的层激发位置进行调整，包括：
    基于所述呼吸导航信息确定所述待测者的膈肌的当前位置；
    计算所述膈肌的当前位置与标准状态下获得的基准膈肌位置之间的膈肌位移量；
    根据所述膈肌位移量和预设的心脏-膈肌位移相关系数计算心脏位移量；
    基于所述心脏位移量对所述标准状态下获得的所述当前待成像的目标心肌层的层激发位置进行调整。
  6. 如权利要求5所述的心脏磁共振弥散张量成像方法，其特征在于，所述标准状态为呼气末期的屏气状态。
  7. 如权利要求1所述的心脏磁共振弥散张量成像方法，其特征在于，所述获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序，包括：
    当所述目标心肌层的数量为偶数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列个偶数层的目标心肌层，在所述收缩期检测顺序和舒张期检测顺序中的另一者中先排列各偶数层的目标心肌层再排列各奇数层的目标心肌层；
    当所述目标心肌层的数量为奇数时，在所述收缩期检测顺序和舒张期检测顺序中的一者中，先排列各奇数层的目标心肌层再排列各偶数层的目标心肌层；在所述收缩期检测顺序和舒张期检测顺序中的另一者中，先排列其中一奇数层的目标心肌层，接着排列各偶数层的目标心肌层，最后排列其余奇数层的目标心肌层。
  8. 一种心脏磁共振弥散张量成像装置，其特征在于，包括：
    心肌层检测顺序获取模块，用于获取待检测者的多个目标心肌层的收缩期检测顺序和舒张期检测顺序；
    弥散张量成像检测模块，用于基于所述收缩期检测顺序和舒张期检测顺序，依次在待检测者连续的多个心动周期的收缩期和舒张期内分别对各所述目标心肌层进行磁共振弥散张量成像检测；
    其中，每个所述收缩期和每个所述舒张期分别对单个所述目标心肌层进行成像，同一所述目标心肌层的收缩期成像与舒张期成像之间的时间间隔为N个心动周期；N为整数且大于或等于2。
  9. 一种心脏磁共振弥散张量成像设备，其特征在于，包括处理器、存储器 以及存储在所述存储器中且被配置为由所述处理器执行的计算机程序，所述处理器执行所述计算机程序时实现如权利要求1至7中任意一项所述的心脏磁共振弥散张量成像方法。
  10. 一种计算机可读存储介质，其特征在于，所述计算机可读存储介质包括存储的计算机程序，其中，在所述计算机程序运行时控制所述计算机可读存储介质所在设备执行如权利要求1至7中任意一项所述的心脏磁共振弥散张量成像方法。
PCT/CN2021/141815 2021-12-27 2021-12-27 心脏磁共振弥散张量成像方法、装置、设备及存储介质 WO2023122919A1 (zh)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/CN2021/141815 WO2023122919A1 (zh) 2021-12-27 2021-12-27 心脏磁共振弥散张量成像方法、装置、设备及存储介质

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2021/141815 WO2023122919A1 (zh) 2021-12-27 2021-12-27 心脏磁共振弥散张量成像方法、装置、设备及存储介质

Publications (1)

Publication Number Publication Date
WO2023122919A1 true WO2023122919A1 (zh) 2023-07-06

Family

ID=86996848

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2021/141815 WO2023122919A1 (zh) 2021-12-27 2021-12-27 心脏磁共振弥散张量成像方法、装置、设备及存储介质

Country Status (1)

Country Link
WO (1) WO2023122919A1 (zh)

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH11239571A (ja) * 1997-12-26 1999-09-07 Toshiba Corp Ｍｒｉ装置およびｍｒ撮像方法
CN102008307A (zh) * 2010-12-29 2011-04-13 中国科学院深圳先进技术研究院 磁共振弥散张量成像方法和系统
CN102665544A (zh) * 2010-10-13 2012-09-12 株式会社东芝 磁共振成像装置及磁共振成像方法
CN103110420A (zh) * 2013-01-31 2013-05-22 深圳先进技术研究院 磁共振血管成像方法和系统
CN105662413A (zh) * 2015-12-31 2016-06-15 深圳先进技术研究院 一种心肌t1定量的方法和装置
CN110547799A (zh) * 2019-08-19 2019-12-10 上海联影医疗科技有限公司 磁共振成像方法、计算机设备和计算机可读存储介质

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH11239571A (ja) * 1997-12-26 1999-09-07 Toshiba Corp Ｍｒｉ装置およびｍｒ撮像方法
CN102665544A (zh) * 2010-10-13 2012-09-12 株式会社东芝 磁共振成像装置及磁共振成像方法
CN102008307A (zh) * 2010-12-29 2011-04-13 中国科学院深圳先进技术研究院 磁共振弥散张量成像方法和系统
CN103110420A (zh) * 2013-01-31 2013-05-22 深圳先进技术研究院 磁共振血管成像方法和系统
CN105662413A (zh) * 2015-12-31 2016-06-15 深圳先进技术研究院 一种心肌t1定量的方法和装置
CN110547799A (zh) * 2019-08-19 2019-12-10 上海联影医疗科技有限公司 磁共振成像方法、计算机设备和计算机可读存储介质

Similar Documents

Publication Publication Date Title
Usman et al. Free breathing whole-heart 3D CINE MRI with self-gated Cartesian trajectory
Marcus et al. Impaired left ventricular filling due to right ventricular pressure overload in primary pulmonary hypertension: noninvasive monitoring using MRI
US10405772B2 (en) Magnetic resonance angiography and venography
US10677870B2 (en) System and method for optimized diffusion-weighted imaging
JP6073570B2 (ja) 磁気共鳴イメージングシステム及び方法
US9241654B2 (en) System and method for selective magnetic resonance imaging angiography of arteries or veins
US10191132B2 (en) Method and apparatus for multi-slice imaging of T2-relaxation time
JP2015510812A (ja) 非虚血性心筋症及びその他における、ｔ１マッピングを使用して正常な心筋層をびまん性疾患から識別するシステム及び方法
CN108720821A (zh) 一种血压估计装置和血压估计系统
JP2002000582A (ja) 磁気的核スピン共鳴により生物の機能的脳活動を時間および位置的に分解して表示する方法および装置
CN117858671A (zh) 无电路心动周期确定
Thavendiranathan et al. Comparison of treadmill exercise stress cardiac MRI to stress echocardiography in healthy volunteers for adequacy of left ventricular endocardial wall visualization: A pilot study
US10353031B2 (en) Shimming method for magnetic resonance imaging
US8200311B2 (en) Cardiac motion artifact suppression using ECG ordering
US10568531B2 (en) Interleaved dual-contrast unenhanced magnetic resonance angiography
WO2021115055A1 (zh) 一种动脉输入函数曲线生成方法及装置
CN113538336A (zh) 全心脏多期相定位图像生成方法、装置、设备和介质
WO2023122919A1 (zh) 心脏磁共振弥散张量成像方法、装置、设备及存储介质
US11375914B2 (en) Data acquisition acceleration in magnetic resonance angiography applications using magnetization-prepared simultaneous multi-slice acquisition
WO2020034675A1 (zh) 定量心肌磁共振成像方法、设备及存储介质
WO2020034676A1 (zh) 心肌定量磁共振成像方法、设备及存储介质
WO2020034674A1 (zh) 定量心肌磁共振成像方法、设备及存储介质
US20230079852A1 (en) Assignment of mr images to cardiac phases
CN116359813A (zh) 心脏磁共振弥散张量成像方法、装置、设备及存储介质
CN111407278B (zh) 利用流速补偿和非补偿的弥散磁共振测量胎盘血流的方法及装置

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: 21969304

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE