WO2021012972A1 - 核磁共振成像控制方法、装置及计算机可读存储介质 - Google Patents

核磁共振成像控制方法、装置及计算机可读存储介质 Download PDF

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WO2021012972A1
WO2021012972A1 PCT/CN2020/101520 CN2020101520W WO2021012972A1 WO 2021012972 A1 WO2021012972 A1 WO 2021012972A1 CN 2020101520 W CN2020101520 W CN 2020101520W WO 2021012972 A1 WO2021012972 A1 WO 2021012972A1
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magnetic resonance
nuclear magnetic
scan
scanning
resonance imaging
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PCT/CN2020/101520
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English (en)
French (fr)
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张贯京
高伟明
葛新科
姚育东
钱唯
郑斌
齐守良
张红治
周亮
陈琦
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深圳市安测健康信息技术有限公司
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Publication of WO2021012972A1 publication Critical patent/WO2021012972A1/zh

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/4802—Travelling-wave MR
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/561—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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/561—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]
    • G01R33/5616—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 gradient refocusing, e.g. EPI
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/58—Calibration of imaging systems, e.g. using test probes, Phantoms; Calibration objects or fiducial markers such as active or passive RF coils surrounding an MR active material
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06N—COMPUTING ARRANGEMENTS BASED ON SPECIFIC COMPUTATIONAL MODELS
    • G06N3/00—Computing arrangements based on biological models
    • G06N3/02—Neural networks
    • G06N3/08—Learning methods

Definitions

  • the present invention relates to the technical field of nuclear magnetic resonance imaging, in particular to a nuclear magnetic resonance imaging control method, device and computer readable storage medium.
  • Magnetic Resonance Imaging is a new type of medical imaging technology that uses the nuclear magnetic resonance phenomenon of a certain atomic nucleus in human tissues to process the resulting radio frequency signals through an electronic computer to reconstruct a certain scan level image of the human body Because of its non-ionizing radiation, multi-sequence, multi-parameter, multi-plane imaging, and high soft tissue resolution, it is widely used in disease diagnosis.
  • a typical magnetic resonance imaging method is: the current signal induced by the receiving coil module is converted from analog to digital to obtain a digital signal, and the digital signal is filled into K space according to a certain encoding direction, where the K space is a kind of The data of the original magnetic resonance signal fills the space.
  • the user can set the desired orientation of the reconstructed image, such as cross section or coronal plane or other angles.
  • the desired orientation of the reconstructed image fill the collected data into K-space according to the encoding direction, and then After processing the data in the K-space with an image reconstruction algorithm, an MRI image of a certain scanning plane (section) of the scanning part is obtained.
  • Artifacts refer to various forms of images that do not exist in the scanned object but appear on the image. Take the upper abdomen and lower abdomen as an example. Due to the breathing movement and gastrointestinal peristalsis, the MRI images usually have artifacts. In order to suppress motion artifacts, the scanning methods usually used are: (1) Scanning during the patient's breath-holding; this method has limitations, often requiring the subject to hold the breath several times, and some patients cannot fully cooperate or hold the breath for a long time. The patient brings discomfort. (2) Use a breathing monitoring device or collect navigation signals to trigger the collection of echo signals, so that the collected K-space data always corresponds to the same or similar motion state.
  • the main purpose of the present invention is to provide a MRI control method, device, and computer readable storage medium, aiming to solve the problem of low calibration efficiency and low accuracy in the MRI clinical scanning process, which affects the quality of MRI images .
  • the present invention provides a nuclear magnetic resonance imaging control device, which includes a processor suitable for realizing various computer program instructions and a memory suitable for storing multiple computer program instructions.
  • the device is connected with magnetic resonance imaging equipment, so
  • the computer program instructions are loaded by the processor and execute the following steps: set the pre-scanning field of view FOV, and control the MRI equipment under the preset FOV to activate the scan sequence to pre-scan the target scanning part to obtain the scan data; input the scan data into a user To identify the neural network model of the scan location information, and output the scan location information corresponding to the scan data from the neural network model; determine the gradient encoding direction of MRI according to the scan location information and the phase encoding direction in the gradient encoding direction relative to the preset reference Rotate the direction to a preset deflection angle; control the MRI equipment to excite the scanning sequence to perform MRI scans on the target scanning part to obtain multiple echo signals, where a gradient along the gradient encoding direction is applied during the acquisition of multiple echo signals Field
  • the step of controlling the nuclear magnetic resonance imaging device to excite a scanning sequence to perform nuclear magnetic resonance scanning on the target scanning site to obtain multiple echo signals includes: controlling the radio frequency transmitting coil of the nuclear magnetic resonance imaging device to transmit radio frequency pulses to the scanning site to stimulate scanning Position of nuclear spin; control the gradient coil of the MRI equipment to generate a gradient field, the gradient field encodes the nuclear spin excited by the scanning part to generate an echo signal, the phase encoding direction of the gradient field is rotated relative to the preset reference direction Set the deflection angle; receive the echo signal through the radio frequency receiving coil of the MRI equipment.
  • the preset deflection angle is determined by the included angle on the scan level between the preset reference direction of the sporty reference target object and the preset target direction of the region of interest of the scanning part.
  • the computer program instructions are loaded by the processor and perform the following steps: training the neural network model in advance, and the specific steps of training the neural network model include: inputting the sample image into the information recognition model to be trained to obtain and The current output recognition result corresponding to the sample image; according to the error between the current output recognition result and the recognition result of the scanned part and tissue of the sample image, determine whether the loss function of the neural network model converges; when the loss function converges, the The neural network model training is over.
  • the computer program instructions are loaded by the processor to perform the following steps: acquiring the generated nuclear magnetic resonance image from the nuclear magnetic resonance imaging device, and displaying it on the display of the device or storing it in the memory.
  • the present invention also provides a nuclear magnetic resonance imaging control method, which is applied to a computer device, the computer device is connected to the nuclear magnetic resonance imaging equipment, the method includes the following steps: setting the pre-scanning field of view FOV, under the preset FOV Control the MRI equipment to activate the scan sequence to pre-scan the target scan location to obtain scan data; input the scan data into a neural network model for identifying the scan location information, and output the scan location information corresponding to the scan data from the neural network model;
  • the scanning position information determines the gradient encoding direction of the MRI and the phase encoding direction in the gradient encoding direction rotates the preset deflection angle relative to the preset reference direction; controls the MRI equipment to activate the scan sequence to perform the MRI scan of the target scan position to obtain Multiple echo signals, where a gradient field along the gradient encoding direction is applied during the acquisition process of multiple echo signals; multiple echo signals are filled into K-space to obtain K-space data of the target scanning part; according to K-space The data determines the following steps
  • the step of controlling the nuclear magnetic resonance imaging device to excite a scanning sequence to perform nuclear magnetic resonance scanning on the target scanning site to obtain multiple echo signals includes: controlling the radio frequency transmitting coil of the nuclear magnetic resonance imaging device to transmit radio frequency pulses to the scanning site to stimulate scanning Position of nuclear spin; control the gradient coil of the MRI equipment to generate a gradient field, the gradient field encodes the nuclear spin excited by the scanning part to generate an echo signal, the phase encoding direction of the gradient field is rotated relative to the preset reference direction Set the deflection angle; receive the echo signal through the radio frequency receiving coil of the MRI equipment.
  • the preset deflection angle is determined by the included angle on the scan level between the preset reference direction of the sporty reference target object and the preset target direction of the region of interest of the scanning part.
  • the MRI control method further includes the step of pre-training the neural network model, and the specific steps of training the neural network model include: inputting the sample image into the information recognition model to be trained to obtain a corresponding sample image The current output recognition result; according to the current output recognition result and the error of the recognition result of the scanning part and tissue of the sample image, determine whether the loss function of the neural network model converges; when the loss function converges, the neural network model The training is over.
  • the present invention also provides a computer-readable storage medium that stores a plurality of computer program instructions and is applied to a computer device that is connected to a nuclear magnetic resonance imaging device.
  • the computer program instructions The steps of the control method based on nuclear magnetic resonance imaging are executed and realized by the processor of the computer device.
  • the MRI control method, device and computer readable medium of the present invention perform pre-scanning of the object to be scanned, and input the obtained scan data into the neural network model for information identification, and then according to the neural network
  • the output result of the model determines the calibration parameters to complete the calibration of the MRI equipment, which realizes the improvement of the calibration efficiency and accuracy during the patient calibration process, and at the same time, the phase encoding direction and the region of interest are preset at the scan level.
  • Directional deflection presets the deflection angle to reduce the influence of artifacts in the phase-encoding direction from the movement of the moving reference organ on the region of interest, thereby improving the image quality of the MRI image, which is conducive to improving the accuracy of clinical diagnosis.
  • FIG. 1 is a schematic block diagram of the structure of a preferred embodiment of the nuclear magnetic resonance imaging control device of the present invention.
  • Fig. 2 is a method flowchart of a preferred embodiment of the MRI control method of the present invention.
  • FIG. 1 is a schematic structural diagram of a preferred embodiment of the nuclear magnetic resonance imaging control device of the present invention.
  • the nuclear magnetic resonance imaging control device 1 includes, but is not limited to, a memory 11 suitable for storing various computer program instructions, a processor 12 that executes various computer program instructions, and a display 13. Both the memory 11 and the display 13 are electrically connected to the processor 12 through an electrical connection line, and are connected to the processor 12 through a data bus for data transmission.
  • the processor 12 can call the nuclear magnetic resonance imaging control program 10 stored in the memory 11, and execute the nuclear magnetic resonance imaging control program 10 to control the nuclear magnetic resonance imaging device 2 to scan the target scanning part of the object to be scanned to obtain scan data, And generate nuclear magnetic resonance images based on the scan data.
  • the nuclear magnetic resonance imaging control device 1 may be a personal computer, a notebook computer, a server, and other computer devices installed with the nuclear magnetic resonance imaging control program 10 of the present invention.
  • the nuclear magnetic resonance imaging control device 1 is connected with a nuclear magnetic resonance imaging device 2, which can scan different parts of the human body of a target object for nuclear magnetic resonance scanning to obtain multiple different echo signals
  • the processor 12 executes the nuclear magnetic resonance imaging control program 10 to process the echo signal.
  • the nuclear magnetic resonance image can be generated. Reduce the influence of the artifacts in the phase encoding direction from the movement of the moving reference organ on the region of interest, thereby improving the image quality of the MRI image, which is beneficial to improving the accuracy of clinical diagnosis.
  • the memory 11 includes at least one type of readable storage medium.
  • the readable storage medium includes flash memory, hard disk, multimedia card, card-type memory (for example, SD or DX memory, etc.), and magnetic memory. , Disks, CDs, etc.
  • the memory 11 may be an internal storage unit of the nuclear magnetic resonance imaging control device 1, such as the hard disk, read-only memory ROM, random access memory RAM, and electrically erasable memory EEPROM of the nuclear magnetic resonance imaging control device 1. , Flash memory FLASH or CD, etc.
  • the memory 11 may also be an external storage device of the nuclear magnetic resonance imaging control device 1, for example, a plug-in hard disk equipped on the nuclear magnetic resonance imaging control device 1, a smart memory card (Smart Media Card, SMC), Secure Digital (SD) card, Flash Card, etc. Further, the memory 11 may also include both an internal storage unit of the nuclear magnetic resonance imaging control device 1 and an external storage device.
  • the memory 11 can be used not only to store application software and various data installed in the nuclear magnetic resonance imaging control device 1, for example, to store the program code of the nuclear magnetic resonance imaging control program 10, etc., but also to temporarily store what has been output or will be output. Data, such as a nuclear magnetic resonance image generated by the nuclear magnetic resonance imaging device 2.
  • the processor 12 may be a central processing unit (Central Processing Unit) in some embodiments.
  • Central Processing Unit CPU
  • controller a controller
  • microcontroller a microprocessor or other data processing chips are used to call and run the program code or processing data stored in the memory 11, for example to execute the nuclear magnetic resonance imaging control program 10, etc.
  • the display 13 may be a touch display screen or a general LED display screen, which can display the nuclear magnetic resonance image generated by the nuclear magnetic resonance imaging device 2.
  • the nuclear magnetic resonance imaging control program 10 may also be divided into one or more modules, and the one or more modules are stored in the memory 11 and run by one or more processors ( This embodiment is executed by the processor 12) to complete the present invention.
  • the module referred to in the present invention refers to a series of computer program instruction segments that can complete specific functions, and is used to describe the nuclear magnetic resonance imaging control program 10 in the nuclear magnetic resonance imaging The execution process in the control device 1.
  • the MRI control program 10 is composed of program modules composed of multiple computer program instructions, including, but not limited to, a neural network creation module 101, a scanning position determination module 102, a scanning gradient determination module 103, The scan data acquisition module 104 and the nuclear magnetic resonance image generation module 105.
  • the module referred to in the present invention refers to a series of computer program instruction segments that can be executed by the processor 12 of the nuclear magnetic resonance imaging control device 1 and can complete fixed functions, which are stored in the nuclear magnetic resonance imaging control device 1 In the memory 11.
  • the neural network creation module 101 is used for pre-training a neural network model for identifying the scanning part information of the object to be scanned.
  • the neural network model is a model used for identifying scanning part information obtained by training a large number of image samples in advance.
  • the image sample is the detection data of various parts of the human body or the detection data after Fourier transform, and the recognition result of the tissue information corresponding to each detection data.
  • the neural network creation module 101 inputs the sample data recognized by the scanned parts and tissues into the neural network model for training. Specifically, the neural network creation module 101 inputs the sample image into the information recognition model to be trained to obtain the current image corresponding to the sample image.
  • the neural network creation module 101 determines whether the loss function of the neural network model converges according to the current output recognition result and the error of the recognition result of the scanned part of the sample image and the tissue; when the loss function converges, the The neural network model training is over.
  • the scanning position determining module 102 is used to set a pre-scanning field of view (FOV), and controlling the nuclear magnetic resonance imaging device 2 to excite a scanning sequence under a preset FOV to perform pre-scanning of the target scanning position of the object to be scanned to obtain scan data.
  • the object to be scanned is a target scan location of a patient undergoing an MRI scan. According to medical clinical requirements, the target scan location may be one or more of the limbs, abdomen, pelvis, chest, or head.
  • the scan data may be pre-scan data collected by using a fast pre-scan sequence to excite the target scanning part of the object to be scanned, and the scan data may be a positioning image obtained by collecting the scanned part of the object to be scanned by a positioning scanning method.
  • the scan data may also be a diagnostic image obtained by collecting an object to be scanned using an imaging sequence.
  • the type of the scan data may be one or more of amplitude image, phase image or K-space data.
  • the scanning sequence may be a low-resolution nuclear magnetic resonance sequence, such as a 3D gradient echo sequence (GRE) or a single shot fast spin echo sequence (Single Shot Fast Spin Echo, SSFSE).
  • GRE 3D gradient echo sequence
  • SSFSE single shot fast spin Echo
  • the three-dimensional amplitude image, phase image or K-space data corresponding to the target scanning part can be obtained through pre-scanning.
  • the positioning scanning method may adopt camera shooting, infrared imaging, or positioning scanning sequence scanning.
  • the scanning position determination module 102 is also used for inputting scanning data into the trained neural network model, and outputting scanning position information corresponding to the scanning data from the neural network model.
  • the scan data of the target scan part is obtained, the scan data can be directly input to the trained neural network model, and the neural network model recognizes and outputs scan part information corresponding to the scan data, wherein the scanned part information includes the The organization to which the scanned part belongs and the geometric information of the scanned part.
  • the neural network model can select an image recognition model, and according to the input scanned image, the model will correspondingly output a recognition result, that is, the information of the target scanning part.
  • the scan gradient determination module 103 is used to determine the gradient encoding direction of the nuclear magnetic resonance imaging and the phase encoding direction in the gradient encoding direction according to the scan position information; the phase encoding direction in the gradient encoding direction rotates preset relative to the preset reference direction The deflection angle, wherein the preset deflection angle is determined by the angle between the preset reference direction of the sporty reference target and the preset target direction of the region of interest of the scanning part on the scan level. Since the time to complete data acquisition in the phase encoding direction is much longer than the time to complete data acquisition in the frequency encoding direction, data differences caused by organ movement are likely to appear in the phase encoding direction, which makes the reconstructed image blurry or overlapping artifacts In the area of interest.
  • the phase encoding direction in the encoding direction of this embodiment is deflected by a preset deflection angle relative to the preset reference direction, so as to reduce the effect of artifacts in the phase encoding direction on the region of interest. influences.
  • the preset reference direction can be manually set, such as the left and right direction of the object to be scanned.
  • the preset deflection angle is determined by the angle between the preset reference direction of the sporty reference target and the preset target direction of the region of interest of the scanning part on the scan level.
  • the scan data acquisition module 104 is used to control the nuclear magnetic resonance imaging device 2 to excite a scan sequence to perform a nuclear magnetic resonance scan on the target scanning part to obtain multiple echo signals, wherein the along-gradient coding is applied during the acquisition of the multiple echo signals Directional gradient field.
  • the scan data acquisition module 104 controls the radio frequency transmitting coil of the nuclear magnetic resonance imaging device 2 to emit radio frequency pulses to the scanning part to excite nuclear spins at the scanning part; controls the gradient coil of the nuclear magnetic resonance imaging device 2 to generate a gradient field ,
  • the gradient field encodes the nuclear spins excited by the scanning part to generate an echo signal, the phase encoding direction of the gradient field rotates a preset deflection angle relative to the preset reference direction; the echo is received by the radio frequency receiving coil of the nuclear magnetic resonance imaging device 2 signal.
  • the scanning sequence includes a radio frequency pulse sequence and a gradient pulse sequence, etc.
  • the scanning parameters corresponding to the two sequences include echo time (echo time, TE), inversion time (inversion time, TI), the size of the flip angle of the RF pulse, and the measurement time (acquisition time, TA), delay (time delay, TD) one or a combination of more.
  • the nuclear magnetic resonance image generating module 105 is used for filling multiple echo signals into K-space to obtain K-space data of the target scanning part. Obtain the echo signal received by the radio frequency receiving coil, and fill multiple echo signals into the K-space to obtain the K-space data of the scanned part. It can be understood that after the gradient encoding direction is determined, the filling trajectory of the K space is also determined, and the K space data of the scanning part can be obtained by filling the K space data according to the predetermined filling trajectory. Optionally, the K-space data of the scanned part may be fully collected or under-collected.
  • the filling trajectory of the K-space data may be one or a combination of one or more of sequential symmetric filling, center priority acquisition filling, circuitous filling, spiral filling, and radial filling.
  • the nuclear magnetic resonance image generating module 105 is also used to determine the initial nuclear magnetic resonance image according to the K-space data, and rotate the initial nuclear magnetic resonance image by a preset deflection angle to generate the nuclear magnetic resonance image; since the phase encoding direction is of interest relative to the scanning part
  • the preset target direction of the area on the scan level is deflected by the preset deflection angle, then the K-space data is deflected by the preset deflection angle relative to the left and right or front and back directions of the human body, so the reconstructed initial MRI image is relative to the left and right sides of the human body.
  • the direction or front-to-back direction is deflected by the preset deflection angle.
  • the initial MRI image needs to be rotated reversely to the preset deflection angle to obtain clinically commonly used MRI images.
  • the left and right directions of the MRI image are the left and right directions of the human body.
  • the direction is the front and back direction of the human body.
  • this embodiment does not limit the image reconstruction method, and it is sufficient to perform image reconstruction on the collected K-space data by using an existing image reconstruction method.
  • the nuclear magnetic resonance image generating module 105 is also used to obtain the generated nuclear magnetic resonance image from the nuclear magnetic resonance imaging device, and display it on the display 13 or store it in the memory 11 for the doctor to provide reference for diagnosis and treatment.
  • FIG. 2 it is a flowchart of a preferred embodiment of the MRI control method of the present invention.
  • the various method steps of the nuclear magnetic resonance imaging control method are implemented by a computer software program, which is stored in a computer-readable storage medium (such as the memory 11 of this embodiment) in the form of computer program instructions.
  • the computer-readable storage medium may include: read-only memory, random access memory, magnetic disk or optical disk, etc.
  • the computer program instructions can be loaded by a processor (for example, the processor 12 in this embodiment) and execute the following steps.
  • Step S21 pre-training a neural network model for identifying the scanning part information of the object to be scanned;
  • the neural network model is a pre-trained one for identifying the scanning part information through a large number of image samples. model.
  • the image sample is the detection data of various parts of the human body or the detection data after Fourier transform, and the recognition result of the tissue information corresponding to each detection data.
  • the sample data recognized by the scanned parts and tissues are input into the neural network model for training.
  • the input data of the neural network model includes each sample image obtained by pre-scanning and each The scan location and tissue recognition result of a pre-scan sample image.
  • a large number of samples must be collected first, which can be a pre-scan sequence for a certain number of people of various types (such as the elderly, adults, children, men, women) to perform rapid MRI scans of various parts of the body.
  • the corresponding scanned image database is collected, and the scanned position of each scanned image in the scanned image database and the tissue shape information of the scanned position are marked.
  • the Fourier transform of each scanned image can also be performed to obtain a corresponding amplitude image, and the amplitude image is used as a training sample of the model.
  • the specific process of the neural network model training includes: inputting the sample image into the information recognition model to be trained to obtain the current output recognition result corresponding to the sample image; according to the current output recognition result and the sample image The error of the recognition result of the scanning part and the tissue determines whether the loss function of the neural network model converges; when the loss function converges, the training of the neural network model ends.
  • Step S22 Set a pre-scan FOV, and control the nuclear magnetic resonance imaging device 2 to excite the scan sequence under the preset FOV to perform pre-scan on the target scanning part of the object to be scanned to obtain scan data.
  • first set the pre-scan field of view Field of View, FOV
  • control the scanning sequence of the nuclear magnetic resonance imaging device 2 under the preset FOV to excite the target scanning part of the object to be scanned for pre-scanning to obtain scan data.
  • the object to be scanned is a target scan location of a patient undergoing an MRI scan. According to medical clinical requirements, the target scan location may be one or more of the limbs, abdomen, pelvis, chest, or head.
  • the scan data may be pre-scan data collected by using a fast pre-scan sequence to excite the target scanning part of the object to be scanned, and the scan data may be a positioning image obtained by collecting the scanned part of the object to be scanned by a positioning scanning method.
  • the scan data may also be a diagnostic image obtained by collecting an object to be scanned using an imaging sequence.
  • the type of the scan data may be one or more of amplitude image, phase image or K-space data.
  • the scanning sequence may be a low-resolution nuclear magnetic resonance sequence, such as a 3D gradient echo sequence (GRE) or a single shot fast spin echo sequence (Single Shot Fast Spin Echo, SSFSE).
  • the three-dimensional amplitude image, phase image or K-space data corresponding to the target scanning part can be obtained through pre-scanning.
  • the positioning scanning method may adopt camera shooting, infrared imaging, or positioning scanning sequence scanning. By using the pre-scan sequence to excite the object to be scanned to obtain scan data, the entire process takes a short time and can be completed in about 3 seconds.
  • Step S23 Input the scan data into the trained neural network model, and output the scan location information corresponding to the scan data from the neural network model.
  • the scan data can be directly input to the trained neural network model, and the neural network model recognizes and outputs scan part information corresponding to the scan data, wherein the scanned part information includes the The organization to which the scanned part belongs and the geometric information of the scanned part.
  • the neural network model can select an image recognition model, and according to the input scanned image, the model will correspondingly output a recognition result, that is, the information of the target scanning part.
  • Step S24 Determine the gradient encoding direction of the MRI and the phase encoding direction in the gradient encoding direction according to the scan position information; the phase encoding direction in the gradient encoding direction is rotated by a preset deflection angle relative to a preset reference direction, wherein It is assumed that the deflection angle is determined by the angle between the preset reference direction of the sporty reference target object and the preset target direction of the region of interest of the scanning part on the scan level.
  • three orthogonal gradient magnetic fields are usually used for spatial positioning.
  • the gradient magnetic field in one direction is used for radio frequency pulses to selectively excite the nuclear spins of protons in a scanning plane, and the gradient magnetic field in one direction is used for To phase-encode the echo signal in one direction in the scanning plane, the gradient magnetic field in the other direction is used to read out and encode the echo signal in the other direction in the scanning plane.
  • the direction of the gradient magnetic field used for phase encoding is called the phase encoding direction
  • the direction of the gradient magnetic field used for frequency encoding is called the frequency encoding direction.
  • the phase encoding direction in the encoding direction of this embodiment is deflected by a preset deflection angle relative to the preset reference direction, so as to reduce the effect of artifacts in the phase encoding direction on the region of interest. influences.
  • the preset reference direction can be manually set, such as the left and right direction of the object to be scanned.
  • the preset deflection angle is determined by the angle between the preset reference direction of the sporty reference target and the preset target direction of the region of interest of the scanning part on the scan level.
  • Step S25 controlling the nuclear magnetic resonance imaging device 2 to excite the scanning sequence to perform nuclear magnetic resonance scanning on the target scanning part to obtain multiple echo signals, wherein a gradient field along the gradient encoding direction is applied during the acquisition of the multiple echo signals.
  • the step of controlling the scanning sequence of the nuclear magnetic resonance imaging device 2 to excite the target scanning part to obtain multiple echo signals includes: controlling the radio frequency transmitting coil of the nuclear magnetic resonance imaging device 2 to emit radio frequency pulses to the scanning part to excite The nuclear spin of the scanning part; the gradient coil of the MRI equipment 2 is controlled to generate a gradient field, the gradient field encodes the nuclear spin excited by the scanning part to generate an echo signal, and the phase encoding direction of the gradient field is relative to the preset reference direction Rotate the preset deflection angle; receive the echo signal through the radio frequency receiving coil of the nuclear magnetic resonance imaging device 2.
  • the scanning sequence includes a radio frequency pulse sequence and a gradient pulse sequence, etc.
  • the scanning parameters corresponding to the two sequences include echo time (echo time, TE), inversion time (inversion time, TI), the size of the flip angle of the RF pulse, and the measurement time (acquisition time, TA), delay (time delay, TD) one or a combination of more.
  • Step S26 Fill the K-space with multiple echo signals to obtain K-space data of the target scanning part. Obtain the echo signal received by the radio frequency receiving coil, and fill multiple echo signals into the K-space to obtain the K-space data of the scanned part. It can be understood that after the gradient encoding direction is determined, the filling trajectory of the K space is also determined, and the K space data of the scanning part can be obtained by filling the K space data according to the predetermined filling trajectory. Optionally, the K-space data of the scanned part may be fully collected or under-collected.
  • the filling trajectory of the K-space data may be one or a combination of one or more of sequential symmetric filling, center priority acquisition filling, circuitous filling, spiral filling, and radial filling.
  • Step S27 Determine the initial nuclear magnetic resonance image according to the K-space data, and rotate the initial nuclear magnetic resonance image by a preset deflection angle to generate the nuclear magnetic resonance image; since the phase encoding direction is preset relative to the region of interest of the scanning part on the scanning level The target direction is deflected by the preset deflection angle, then the K-space data is deflected by the preset deflection angle relative to the left-right or front-rear direction of the human body, so the reconstructed initial MRI image is deflected by the preset relative to the left-right or front-rear direction of the human body Deflection angle, therefore, it is necessary to reversely rotate the initial MRI image to a preset deflection angle to obtain commonly used clinical MRI images.
  • the left and right directions of the MRI image are the left and right directions of the human body
  • the up and down directions are the front and back directions of the human body.
  • this embodiment does not limit the image reconstruction method, and it is sufficient to perform image reconstruction on the collected K-space data by using an existing image reconstruction method.
  • step S28 the generated nuclear magnetic resonance image is obtained from the nuclear magnetic resonance imaging device, and displayed on the display 13 or stored in the memory 11.
  • the nuclear magnetic resonance imaging control method further includes the following steps: acquiring the generated nuclear magnetic resonance image from the nuclear magnetic resonance imaging device 2 and displaying it on the display 13, or the output is stored in the memory 11 for the doctor to diagnose and treat Provide reference.
  • the present invention also provides a computer-readable storage medium that stores a plurality of computer program instructions, and the computer program instructions are loaded by a processor of a computer device and execute each of the nuclear magnetic resonance imaging control methods of the present invention. step.
  • the program can be stored in a computer-readable storage medium.
  • the storage medium may include: read-only memory, random access memory, Disk or CD, etc.
  • the nuclear magnetic resonance imaging control method, device and computer readable medium of the present invention pre-scan the object to be scanned, input the obtained scan data into the neural network model for information identification, and then determine the calibration parameters according to the output result of the neural network model , In order to complete the calibration of the MRI equipment, solve the problem of low calibration efficiency and need to be improved in the patient calibration process of MRI clinical scanning, and realize the improvement of the calibration efficiency and calibration accuracy during the patient calibration process.
  • the effect of artifacts in the phase encoding direction from the movement of the moving reference organ on the region of interest is reduced, thereby improving the NMR
  • the image quality of the resonance image is conducive to improving the accuracy of clinical diagnosis.
  • the MRI control method, device and computer readable medium of the present invention perform pre-scanning of the object to be scanned, and input the obtained scan data into the neural network model for information identification, and then according to the neural network
  • the output result of the model determines the calibration parameters to complete the calibration of the MRI equipment, which realizes the improvement of the calibration efficiency and accuracy during the patient calibration process, and at the same time, the phase encoding direction and the region of interest are preset at the scan level.
  • Directional deflection presets the deflection angle to reduce the influence of artifacts in the phase-encoding direction from the movement of the moving reference organ on the region of interest, thereby improving the image quality of the MRI image, which is conducive to improving the accuracy of clinical diagnosis.

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Abstract

一种核磁共振成像控制方法、装置（1）及计算机可读存储介质，控制方法包括：在预设的FOV下控制核磁共振成像设备（2）激发扫描序列对目标扫描部位进行预扫描得到扫描数据（S22）；将扫描数据输入神经网络模型，从神经网络模型输出扫描数据对应的扫描部位信息（S23）；根据扫描部位信息确定核磁共振成像的梯度编码方向（S24）；控制核磁共振成像设备（2）激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号（S25）；将多个回波信号填充入K空间以获取目标扫描部位的K空间数据（S26）；根据K空间数据确定初始核磁共振图像，将初始核磁共振图像反向旋转预设偏转角度以生成核磁共振图像（S27）。核磁共振成像控制方法能够提高核磁共振扫描的校正效率和校正准确度，进而提高核磁共振图像的质量。

Description

核磁共振成像控制方法、装置及计算机可读存储介质 技术领域
本发明涉及核磁共振成像技术领域，尤其涉及一种核磁共振成像控制方法、装置及计算机可读存储介质。
 背景技术
核磁共振成像（Magnetic Resonance Imaging，MRI）主要是利用人体组织中某种原子核的核磁共振现象，将所得的射频信号经过电子计算机处理，重建出人体某一扫描层面图像的一种新型的医学影像技术，由于其无电离辐射、多序列、多参数、多平面成像以及较高的软组织分辨力，而被广泛应用于疾病的诊断。现有技术中，典型的磁共振成像方法为：接收线圈模块感应出的电流信号经模数转换后得到数字信号，将数字信号按照一定的编码方向填充到K空间，其中，K空间是一种原始磁共振信号的数据填充空间，用户可以自行设置所需的重建图像方位，比如横截面或冠状面或其他角度，根据设置的重建图像方位，将采集的数据按照编码方向填充到K空间，然后将K空间内的数据经图像重建算法处理后，得到扫描部位某一扫描层面（断面）的核磁共振图像。
伪影（Artifacts）是指原本被扫描物体并不存在而在图像上却出现的各种形态的影像。以上腹和下腹为例，由于存在呼吸运动、胃肠蠕动，其核磁共振图像通常存在伪影。为了抑制运动伪影，通常采用的扫描方式有：(1)在病人屏气期间进行扫描；该方法具有局限性，常常需要受检者多次屏气，而且有些病人不能完全配合，或者长时间屏气给病人带来不舒服。(2)使用呼吸监控装置，或者采集导航信号，用来触发回波信号的采集，使采集到的K空间数据总是对应相同或相近的运动状态。
上述扫描方式均存在局限性，如果存在不规律的呼吸运动，或者显著的胃肠蠕动情况下，核磁共振图像，特别是核磁共振图像的感兴趣区会存在伪影，影响临床诊断的准确性。因此，有必要提供一种核磁共振成像控制方法，以避免由器官运动引起的伪影分布在核磁共振图像的感兴趣区。
 技术问题
本发明的主要目的在于提供一种核磁共振成像控制方法、装置及计算机可读存储介质，旨在解决在磁共振临床扫描过程中，校准效率低且准确度不高而影响核磁共振图像质量的问题。
 技术解决方案
为实现上述目的，本发明提供一种核磁共振成像控制装置，包括适于实现各种计算机程序指令的处理器以及适于存储多条计算机程序指令的存储器，该装置连接有磁共振成像设备，所述计算机程序指令由处理器加载并执行如下步骤：设置预扫描视野FOV，在预设的FOV下控制核磁共振成像设备激发扫描序列对目标扫描部位进行预扫描得到扫描数据；将扫描数据输入一个用于识别扫描部位信息的神经网络模型，并从神经网络模型输出扫描数据对应的扫描部位信息；根据扫描部位信息确定核磁共振成像的梯度编码方向以及梯度编码方向中的相位编码方向相对于预设基准方向旋转预设偏转角度；控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号，其中，在多个回波信号的采集过程中施加沿梯度编码方向的梯度场；将多个回波信号填充入K空间以获取目标扫描部位的K空间数据；根据K空间数据确定初始核磁共振图像，将初始核磁共振图像反向旋转预设偏转角度以生成核磁共振图像。
优选的，所述控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号的步骤包括：控制核磁共振成像设备的射频发射线圈向扫描部位发射射频脉冲以激发扫描部位的核自旋；控制核磁共振成像设备的梯度线圈产生梯度场，梯度场对扫描部位激发的核自旋进行编码以产生回波信号，梯度场的相位编码方向相对于预设基准方向旋转预设偏转角度；通过核磁共振成像设备的射频接收线圈接收回波信号。
优选的，所述预设偏转角度由运动型参考目标对象的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。
优选的，所述计算机程序指令由处理器加载还执行如下步骤：预先训练所述神经网络模型，该神经网络模型训练的具体步骤包括：将样本图像输入至待训练的信息识别模型中，得到与样本图像对应的当前输出识别结果；根据当前输出识别结果和样本图像的扫描部位和组织的识别结果的误差，确定所述神经网络模型的损失函数是否收敛；当所述损失函数收敛时，所述神经网络模型训练结束。
优选的，所述计算机程序指令由处理器加载还执行如下步骤：从核磁共振成像设备获取生成的核磁共振图像，并显示在该装置的显示器上或者存储在存储器中。
另一方面，本发明还提供一种核磁共振成像控制方法，应用于计算机装置中，该计算机装置连接有核磁共振成像设备，该方法包括如下步骤：设置预扫描视野FOV，在预设的FOV下控制核磁共振成像设备激发扫描序列对目标扫描部位进行预扫描得到扫描数据；将扫描数据输入一个用于识别扫描部位信息的神经网络模型，并从神经网络模型输出扫描数据对应的扫描部位信息；根据扫描部位信息确定核磁共振成像的梯度编码方向以及梯度编码方向中的相位编码方向相对于预设基准方向旋转预设偏转角度；控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号，其中，在多个回波信号的采集过程中施加沿梯度编码方向的梯度场；将多个回波信号填充入K空间以获取目标扫描部位的K空间数据；根据K空间数据确定初始核磁共振图像，将初始核磁共振图像反向旋转预设偏转角度以生成核磁共振图像。
优选的，所述控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号的步骤包括：控制核磁共振成像设备的射频发射线圈向扫描部位发射射频脉冲以激发扫描部位的核自旋；控制核磁共振成像设备的梯度线圈产生梯度场，梯度场对扫描部位激发的核自旋进行编码以产生回波信号，梯度场的相位编码方向相对于预设基准方向旋转预设偏转角度；通过核磁共振成像设备的射频接收线圈接收回波信号。
优选的，所述预设偏转角度由运动型参考目标对象的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。
优选的，所述核磁共振成像控制方法还包括预先训练所述神经网络模型的步骤，该神经网络模型训练的具体步骤包括：将样本图像输入至待训练的信息识别模型中，得到与样本图像对应的当前输出识别结果；根据当前输出识别结果和样本图像的扫描部位和组织的识别结果的误差，确定所述神经网络模型的损失函数是否收敛；当所述损失函数收敛时，所述神经网络模型训练结束。
再一方面，本发明还提供一种计算机可读存储介质，该计算机可读存储介质存储多条计算机程序指令，应用于计算机装置中，该计算机装置连接有核磁共振成像设备，所述计算机程序指令由计算机装置的处理器执行并实现所述基于核磁共振成像控制方法的各项步骤。
 有益效果
相较于现有技术，本发明所述核磁共振成像控制方法、装置及计算机可读介质，通过对待扫描对象进行预扫描，将得到的扫描数据输入至神经网络模型进行信息识别，然后根据神经网络模型的输出结果确定校准参数，以完成对核磁共振设备的校准，实现了在患者校正过程中提高校正效率和校正准确度，同时通过使相位编码方向与感兴趣区在扫描层面上的预设目标方向偏转预设偏转角度，降低由运动型参考器官的运动在相位编码方向上的伪影对感兴趣区的影响，进而提高核磁共振图像的图像质量，有利于提高临床诊断的准确性。
 附图说明
图1是本发明核磁共振成像控制装置的较佳实施例的结构方框示意图。
图2是本发明核磁共振成像控制方法较佳实施例的方法流程图。
本发明目的的实现、功能特点及优点将结合实施例，参照附图做进一步说明。
 本发明的实施方式
为更进一步阐述本发明为达成预定发明目的所采取的技术手段及功效，以下结合附图及较佳实施例，对本发明的具体实施方式、结构、特征及其功效，详细说明如下。应当理解，此处所描述的具体实施例仅仅用以解释本发明，并不用于限定本发明。
参照图1所示，图1是本发明核磁共振成像控制装置的较佳实施例的结构示意图。在本实施例中，所述核磁共振成像控制装置1包括，但不仅限于，适于存储各种计算机程序指令的存储器11、执行各种计算机程序指令的处理器12以及显示器13。所述存储器11和显示器13均通过电连接线与所述处理器12进行电气连接，并通过数据总线与处理器12进行数据传输连接。所述处理器12能够调用存储在所述存储器11中的核磁共振成像控制程序10，并执行该核磁共振成像控制程序10控制核磁共振成像设备2对待扫描对象的目标扫描部位进行扫描获得扫描数据，并根据扫描数据生成核磁共振图像。所述核磁共振成像控制装置1可以为安装有本发明所述核磁共振成像控制程序10的个人计算机、笔记本电脑、服务器等计算机装置。
在本实施例中，所述核磁共振成像控制装置1连接有核磁共振成像设备2，该核磁共振成像设备2能够扫描目标对象的人体不同部位进行核磁共振扫描以获取多个不同的回波信号，并通过处理器12执行核磁共振成像控制程序10对回波信号进行处理，通过使相位编码方向与感兴趣区在扫描层面上的预设目标方向偏转预设偏转角度以此生成核磁共振图像，能够降低由运动型参考器官的运动在相位编码方向上的伪影对感兴趣区的影响，进而提高核磁共振图像的图像质量，有利于提高临床诊断的准确性。
在本实施例中，所述存储器11至少包括一种类型的可读存储介质，所述可读存储介质包括闪存、硬盘、多媒体卡、卡型存储器（例如，SD或DX存储器等）、磁性存储器、磁盘、光盘等。所述存储器11在一些实施例中可以是所述核磁共振成像控制装置1的内部存储单元，例如该核磁共振成像控制装置1的硬盘、只读存储器ROM，随机存储器RAM、电可擦写存储器EEPROM、快闪存储器FLASH或光盘等。所述存储器11在另一些实施例中也可以是核磁共振成像控制装置1的外部存储设备，例如该核磁共振成像控制装置1上配备的插接式硬盘，智能存储卡（Smart Media Card, SMC），安全数字（Secure Digital，SD）卡，闪存卡（Flash Card）等。进一步地，所述存储器11还可以既包括核磁共振成像控制装置1的内部存储单元也包括外部存储设备。所述存储器11不仅可以用于存储安装于核磁共振成像控制装置1的应用软件及各类数据，例如存储核磁共振成像控制程序10的程序代码等，还可以用于暂时地存储已经输出或者将要输出的数据，例如核磁共振成像设备2生成的核磁共振图像。
在本实施例中，所述处理器12在一些实施例中可以是一中央处理器（Central Processing Unit，CPU）、控制器、微控制器、微处理器或其他数据处理芯片，用于调用并运行存储器11中存储的程序代码或处理数据，例如执行核磁共振成像控制程序10等。所述显示器13可以为触摸显示屏也可以为通用的LED显示屏，能够显示核磁共振成像设备2生成的核磁共振图像。
可选地，在其他实施例中，所述核磁共振成像控制程序10还可以被分割为一个或者多个模块，一个或者多个模块被存储于存储器11中，并由一个或多个处理器（本实施例为处理器12）所执行以完成本发明，本发明所称的模块是指能够完成特定功能的一系列计算机程序指令段，用于描述核磁共振成像控制程序10在所述核磁共振成像控制装置1中的执行过程。
在本实施例中，所述核磁共振成像控制程序10由多条计算机程序指令组成的程序模块组成，包括但不局限于，神经网络创建模块101、扫描部位确定模块102、扫描梯度确定模块103、扫描数据获取模块104以及核磁共振图像生成模块105。本发明所称的模块是指一种能够被所述核磁共振成像控制装置1的处理器12执行并且能够完成固定功能的一系列计算机程序指令段，其存储在所述核磁共振成像控制装置1的存储器11中。
所述神经网络创建模块101用于预先训练一个用于识别待扫描对象的扫描部位信息的神经网络模型。在本实施例中，所述神经网络模型是预先经过大量图像样本进行训练得到的一个用于识别扫描部位信息的模型。图像样本为人的全身各部位的检测数据或经过傅立叶变换的检测数据，与各检测数据相应的组织信息的识别结果。神经网络创建模块101将经过扫描部位与组织识别的样本数据输入神经网络模型进行训练具体地包括：神经网络创建模块101将样本图像输入至待训练的信息识别模型中，得到与样本图像对应的当前输出识别结果；神经网络创建模块101根据当前输出识别结果和样本图像的扫描部位和组织的识别结果的误差，确定所述神经网络模型的损失函数是否收敛；当所述损失函数收敛时，所述神经网络模型训练结束。
所述扫描部位确定模块102用于设置预扫描视野（Field of View，FOV），在预设的FOV下控制核磁共振成像设备2激发扫描序列对待扫描对象的目标扫描部位进行预扫描得到扫描数据。所述待扫描对象为进行核磁共振扫描的患者的目标扫描部位，根据医学临床需求，所述目标扫描部位可以是四肢、腹部、盆腔、胸部或头部中的一个或多个部位。所述扫描数据可以是利用快速预扫描序列激发待扫描对象的目标扫描部位采集得到的预扫描数据，所述扫描数据可以是利用定位扫描方法采集待扫描对象的被扫描部位得到的定位图像，所述扫描数据还可以是利用成像序列采集待扫描对象得到的诊断图像。所述扫描数据的类型可以是幅值图像、相位图像或者K空间数据的一种或多种。可选地，所述扫描序列可以是低分辨率的核磁共振序列，例如3D梯度回波序列（Gradient Recalled Echo，GRE）或者单次激发快速自旋回波序列（Single Shot FastSpin Echo，SSFSE）。可选地，通过预扫描可以得到目标扫描部位对应的三维幅值图像、相位图像或者K空间数据。定位扫描方法可以采用相机拍摄、红外成像或者定位扫描序列扫描等。
所述扫描部位确定模块102还用于将扫描数据输入训练好的神经网络模型，并从神经网络模型输出扫描数据对应的扫描部位信息。当获取到目标扫描部位的扫描数据后可以直接将扫描数据输入到训练好的神经网络模型，该神经网络模型识别并输出扫描数据对应的扫描部位信息，其中，所述被扫描部位信息包括所述被扫描部位所属的组织和所述被扫描部位的几何形态信息。示例性地，神经网络模型可选择图像识别模型，根据输入的扫描图像，该模型会相应的输出一个识别结果，即目标扫描部位的信息。
所述扫描梯度确定模块103用于根据扫描部位信息确定核磁共振成像的梯度编码方向以及梯度编码方向中的相位编码方向；所述梯度编码方向中的相位编码方向相对于预设基准方向旋转预设偏转角度，其中，预设偏转角度由运动型参考目标的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。由于相位编码方向完成数据采集的时间远远高于频率编码方向完成数据采集的时间，因此由器官运动所导致的数据差异容易出现在相位编码方向上，从而使得重建出的图像模糊或伪影重叠在感兴趣区。为了避免磁共振图像的感兴趣区叠加有伪影，本实施例编码方向中的相位编码方向相对于预设基准方向偏转预设偏转角度，以降低相位编码方向上的伪影对感兴趣区的影响。其中，预设基准方向可人为设定，比如待扫描对象的左右方向。预设偏转角度由运动型参考目标的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。
所述扫描数据获取模块104用于控制核磁共振成像设备2激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号，其中，在多个回波信号的采集过程中施加沿梯度编码方向的梯度场。在本实施例中，所述扫描数据获取模块104控制核磁共振成像设备2的射频发射线圈向扫描部位发射射频脉冲以激发扫描部位的核自旋；控制核磁共振成像设备2的梯度线圈产生梯度场，梯度场对扫描部位激发的核自旋进行编码以产生回波信号，梯度场的相位编码方向相对于预设基准方向旋转预设偏转角度；通过核磁共振成像设备2的射频接收线圈接收回波信号。可选地，所述扫描序列包括射频脉冲序列和梯度脉冲序列等，两种序列对应的扫描参数包括回波时间(echo time，TE)、反转时间(inversion time，TI)、射频脉冲翻转角的大小、测量时间(acquisition time，TA)、延时(time delay，TD)中的一种或者多种的组合。
所述核磁共振图像生成模块105用于将多个回波信号填充入K空间，以获取目标扫描部位的K空间数据。获取射频接收线圈接收的回波信号，并将多个回波信号填充入K空间以获取扫描部位的K空间数据。可以理解的是，梯度编码方向确定后，K空间的填充轨迹也就确定了，按照预定的填充轨迹填充K空间数据即可获得扫描部位的K空间数据。可选地，扫描部位的K空间数据可以是满采集的或者欠采集的。K空间数据的填充轨迹可以是循序对称填充、中心优先采集填充、迂回填充、螺旋填充、放射状填充中的一种或多种的组合。
所述核磁共振图像生成模块105还用于根据K空间数据确定初始核磁共振图像，将初始核磁共振图像反向旋转预设偏转角度以生成核磁共振图像；由于相位编码方向相对于扫描部位的感兴趣区在扫描层面上的预设目标方向偏转了预设偏转角度，那么K空间数据相对于人体的左右方向或前后方向偏转了预设偏转角度，因此重建出的初始核磁共振图像相对于人体的左右方向或前后方向偏转了预设偏转角度，因此需要将初始核磁共振图像反向旋转预设偏转角度，以得到临床常用的核磁共振图像，比如，核磁共振图像的左右方向为人体的左右方向，上下方向为人体的前后方向。其中，本实施例对图像重建方法不予限定，采用现有的图像重建方法对采集的K空间数据进行图像重建即可。
所述核磁共振图像生成模块105还用于从核磁共振成像设备获取生成的核磁共振图像，并显示在显示器13上或者存储在存储器11中，以供医生在诊断治疗方面提供参考。
参考图2所示，是本发明核磁共振成像控制方法较佳实施例的流程图。在本实施例中，所述核磁共振成像控制方法的各种方法步骤通过计算机软件程序来实现，该计算机软件程序以计算机程序指令的形式存储于计算机可读存储介质（例如本实施例的存储器11）中，计算机可读存储介质可以包括：只读存储器、随机存储器、磁盘或光盘等，所述计算机程序指令能够被处理器（例如本实施例的处理器12）加载并执行如下步骤。
步骤S21，预先训练一个用于识别待扫描对象的扫描部位信息的神经网络模型；在本实施例中，所述神经网络模型是预先经过大量图像样本进行训练得到的一个用于识别扫描部位信息的模型。图像样本为人的全身各部位的检测数据或经过傅立叶变换的检测数据，与各检测数据相应的组织信息的识别结果。具体地，将经过扫描部位与组织识别的样本数据输入神经网络模型进行训练，其中，以图像检测为例说明，所述神经网络模型的输入数据包括预扫描获取的每一张样本图像和每一张预扫描样本图像的扫描部位和组织的识别结果。在模型训练过程中，首先要采集大量的样本，可以是预先通过预扫描序列对一定数量的各类型人员（例如老人、成年人、小孩、男性、女性）进行全身各部位的核磁共振快速扫描，采集得到相应的扫描图像数据库，并对扫描图像数据库中的各扫描图像的扫描部位及扫描部位的组织形态信息进行标注。在一种实施方式中，还可以对各扫描图像进行傅立叶变换得到相应的幅值图像，将幅值图像作为模型的训练样本。
在本实施例中，所述神经网络模型训练的具体过程包括：将样本图像输入至待训练的信息识别模型中，得到与样本图像对应的当前输出识别结果；根据当前输出识别结果和样本图像的扫描部位和组织的识别结果的误差，确定所述神经网络模型的损失函数是否收敛；当所述损失函数收敛时，所述神经网络模型训练结束。
步骤S22，设置预扫描的FOV，在预设的FOV下控制核磁共振成像设备2激发扫描序列对待扫描对象的目标扫描部位进行预扫描得到扫描数据。在本实施例中，在核磁共振扫描开始之前，首先设置预扫描视野（Field of View，FOV），然后在预设的FOV下控制核磁共振成像设备2的扫描序列激发待扫描对象的目标扫描部位进行预扫描得到扫描数据。所述待扫描对象为进行核磁共振扫描的患者的目标扫描部位，根据医学临床需求，所述目标扫描部位可以是四肢、腹部、盆腔、胸部或头部中的一个或多个部位。所述扫描数据可以是利用快速预扫描序列激发待扫描对象的目标扫描部位采集得到的预扫描数据，所述扫描数据可以是利用定位扫描方法采集待扫描对象的被扫描部位得到的定位图像，所述扫描数据还可以是利用成像序列采集待扫描对象得到的诊断图像。所述扫描数据的类型可以是幅值图像、相位图像或者K空间数据的一种或多种。可选地，所述扫描序列可以是低分辨率的核磁共振序列，例如3D梯度回波序列（Gradient Recalled Echo，GRE）或者单次激发快速自旋回波序列（Single Shot FastSpin Echo，SSFSE）。可选地，通过预扫描可以得到目标扫描部位对应的三维幅值图像、相位图像或者K空间数据。可选地，定位扫描方法可以采用相机拍摄、红外成像或者定位扫描序列扫描等。通过利用预扫描序列激发待扫描对象获得扫描数据，整个过程耗时较短，约3秒钟即可完成。
步骤S23，将扫描数据输入训练好的神经网络模型，并从神经网络模型输出扫描数据对应的扫描部位信息。当获取到目标扫描部位的扫描数据后可以直接将扫描数据输入到训练好的神经网络模型，该神经网络模型识别并输出扫描数据对应的扫描部位信息，其中，所述被扫描部位信息包括所述被扫描部位所属的组织和所述被扫描部位的几何形态信息。示例性地，神经网络模型可选择图像识别模型，根据输入的扫描图像，该模型会相应的输出一个识别结果，即目标扫描部位的信息。
步骤S24，根据扫描部位信息确定核磁共振成像的梯度编码方向以及梯度编码方向中的相位编码方向；所述梯度编码方向中的相位编码方向相对于预设基准方向旋转预设偏转角度，其中，预设偏转角度由运动型参考目标对象的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。在核磁共振成像时，通常使用三个正交方向的梯度磁场进行空间定位，一个方向的梯度磁场用于射频脉冲选择性地激发一个扫描层面内的质子的核自旋，一个方向的梯度磁场用于对沿扫描层面内的一个方向的回波信号进行相位编码，另一个方向的梯度磁场用于对沿扫描层面内的另一个方向的回波信号进行读出编码。其中，用于相位编码的梯度磁场的方向称为相位编码方向，用于频率编码的梯度磁场的方向称为频率编码方向。
由于相位编码方向完成数据采集的时间远远高于频率编码方向完成数据采集的时间，因此由器官运动所导致的数据差异容易出现在相位编码方向上，从而使得重建出的图像模糊或伪影重叠在感兴趣区。为了避免磁共振图像的感兴趣区叠加有伪影，本实施例编码方向中的相位编码方向相对于预设基准方向偏转预设偏转角度，以降低相位编码方向上的伪影对感兴趣区的影响。其中，预设基准方向可人为设定，比如待扫描对象的左右方向。预设偏转角度由运动型参考目标的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。
步骤S25，控制核磁共振成像设备2激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号，其中，在多个回波信号的采集过程中施加沿梯度编码方向的梯度场。在本实施例中，所述控制核磁共振成像设备2的扫描序列激发目标扫描部位以获取多个回波信号的步骤包括：控制核磁共振成像设备2的射频发射线圈向扫描部位发射射频脉冲以激发扫描部位的核自旋；控制核磁共振成像设备2的梯度线圈产生梯度场，梯度场对扫描部位激发的核自旋进行编码以产生回波信号，梯度场的相位编码方向相对于预设基准方向旋转预设偏转角度；通过核磁共振成像设备2的射频接收线圈接收回波信号。可选地，所述扫描序列包括射频脉冲序列和梯度脉冲序列等，两种序列对应的扫描参数包括回波时间(echo time，TE)、反转时间(inversion time，TI)、射频脉冲翻转角的大小、测量时间(acquisition time，TA)、延时(time delay，TD)中的一种或者多种的组合。
步骤S26，将多个回波信号填充入K空间，以获取目标扫描部位的K空间数据。获取射频接收线圈接收的回波信号，并将多个回波信号填充入K空间以获取扫描部位的K空间数据。可以理解的是，梯度编码方向确定后，K空间的填充轨迹也就确定了，按照预定的填充轨迹填充K空间数据即可获得扫描部位的K空间数据。可选地，扫描部位的K空间数据可以是满采集的或者欠采集的。K空间数据的填充轨迹可以是循序对称填充、中心优先采集填充、迂回填充、螺旋填充、放射状填充中的一种或多种的组合。
步骤S27，根据K空间数据确定初始核磁共振图像，将初始核磁共振图像反向旋转预设偏转角度以生成核磁共振图像；由于相位编码方向相对于扫描部位的感兴趣区在扫描层面上的预设目标方向偏转了预设偏转角度，那么K空间数据相对于人体的左右方向或前后方向偏转了预设偏转角度，因此重建出的初始核磁共振图像相对于人体的左右方向或前后方向偏转了预设偏转角度，因此需要将初始核磁共振图像反向旋转预设偏转角度，以得到临床常用的核磁共振图像，比如，核磁共振图像的左右方向为人体的左右方向，上下方向为人体的前后方向。其中，本实施例对图像重建方法不予限定，采用现有的图像重建方法对采集的K空间数据进行图像重建即可。
步骤S28，从核磁共振成像设备获取生成的核磁共振图像，并显示在显示器13上或者存储在存储器11中。在本实施例中，所述核磁共振成像控制方法还包括如下步骤：从核磁共振成像设备2获取生成的核磁共振图像并显示在显示器13上，或者输出存在存储器11中，以供医生在诊断治疗方面提供参考。
本发明还提供一种计算机可读存储介质，该计算机可读存储介质存储多条计算机程序指令，所述计算机程序指令由计算机装置的处理器加载并执行本发明所述核磁共振成像控制方法的各个步骤。本领域技术人员可以理解，上述实施方式中各种方法的全部或部分步骤可以通过相关程序指令完成，该程序可以存储于计算机可读存储介质中，存储介质可以包括：只读存储器、随机存储器、磁盘或光盘等。
本发明所述核磁共振成像控制方法、装置及计算机可读介质，通过对待扫描对象进行预扫描，将得到的扫描数据输入至神经网络模型进行信息识别，然后根据神经网络模型的输出结果确定校准参数，以完成对核磁共振设备的校准，解决了在核磁共振临床扫描的患者校准过程中，校准效率低且准确度有待提高的问题，实现了在患者校正过程中提高校正效率和校正准确度，同时通过使相位编码方向与感兴趣区在扫描层面上的预设目标方向偏转预设偏转角度，降低由运动型参考器官的运动在相位编码方向上的伪影对感兴趣区的影响，进而提高核磁共振图像的图像质量，有利于提高临床诊断的准确性。
以上仅为本发明的较佳实施例，并非因此限制本发明的专利范围，凡是利用本发明说明书及附图内容所作的等效结构或等效流程变换，或直接或间接运用在其他相关的技术领域，均同理包括在本发明的专利保护范围内。
 工业实用性
相较于现有技术，本发明所述核磁共振成像控制方法、装置及计算机可读介质，通过对待扫描对象进行预扫描，将得到的扫描数据输入至神经网络模型进行信息识别，然后根据神经网络模型的输出结果确定校准参数，以完成对核磁共振设备的校准，实现了在患者校正过程中提高校正效率和校正准确度，同时通过使相位编码方向与感兴趣区在扫描层面上的预设目标方向偏转预设偏转角度，降低由运动型参考器官的运动在相位编码方向上的伪影对感兴趣区的影响，进而提高核磁共振图像的图像质量，有利于提高临床诊断的准确性。

Claims (10)

  1. 一种核磁共振成像控制装置，包括适于实现各种计算机程序指令的处理器以及适于存储多条计算机程序指令的存储器，其特征在于，该装置连接有磁共振成像设备，所述计算机程序指令由处理器加载并执行如下步骤：
    设置预扫描视野FOV，在预设的FOV下控制核磁共振成像设备激发扫描序列对目标扫描部位进行预扫描得到扫描数据；
    将扫描数据输入一个用于识别扫描部位信息的神经网络模型，并从神经网络模型输出扫描数据对应的扫描部位信息；
    根据扫描部位信息确定核磁共振成像的梯度编码方向以及梯度编码方向中的相位编码方向相对于预设基准方向旋转预设偏转角度；
    控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号，其中，在多个回波信号的采集过程中施加沿梯度编码方向的梯度场；
    将多个回波信号填充入K空间以获取目标扫描部位的K空间数据；
    根据K空间数据确定初始核磁共振图像，将初始核磁共振图像反向旋转预设偏转角度以生成目标扫描部位的核磁共振图像。
  2. 如权利要求1所述的核磁共振成像控制装置，其特征在于，所述控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号的步骤包括：
    控制核磁共振成像设备的射频发射线圈向扫描部位发射射频脉冲以激发扫描部位的核自旋；
    控制核磁共振成像设备的梯度线圈产生梯度场，梯度场对扫描部位激发的核自旋进行编码以产生回波信号，梯度场的相位编码方向相对于预设基准方向旋转预设偏转角度；
    通过核磁共振成像设备的射频接收线圈接收回波信号。
  3. 如权利要求2所述的核磁共振成像控制装置，其特征在于，所述预设偏转角度由运动型参考目标对象的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。
  4. 如权利要求1所述的核磁共振成像控制装置，其特征在于，所述计算机程序指令由处理器加载还执行如下步骤：预先训练所述神经网络模型，该神经网络模型训练的具体步骤包括：将样本图像输入至待训练的信息识别模型中，得到与样本图像对应的当前输出识别结果；根据当前输出识别结果和样本图像的扫描部位和组织的识别结果的误差，确定所述神经网络模型的损失函数是否收敛；当所述损失函数收敛时，所述神经网络模型训练结束。
  5. 如权利要求1至4任一项所述的核磁共振成像控制装置，其特征在于，所述计算机程序指令由处理器加载还执行如下步骤：
    从核磁共振成像设备获取生成的核磁共振图像，并显示在该装置的显示器上或者存储在存储器中。
  6. 一种核磁共振成像控制方法，应用于计算机装置中，该计算机装置连接有核磁共振成像设备，其特征在于，该方法包括如下步骤：
    设置预扫描视野FOV，在预设的FOV下控制核磁共振成像设备激发扫描序列对目标扫描部位进行预扫描得到扫描数据；
    将扫描数据输入一个用于识别扫描部位信息的神经网络模型，并从神经网络模型输出扫描数据对应的扫描部位信息；
    根据扫描部位信息确定核磁共振成像的梯度编码方向以及梯度编码方向中的相位编码方向相对于预设基准方向旋转预设偏转角度；
    控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号，其中，在多个回波信号的采集过程中施加沿梯度编码方向的梯度场；
    将多个回波信号填充入K空间以获取目标扫描部位的K空间数据；
    根据K空间数据确定初始核磁共振图像，将初始核磁共振图像反向旋转预设偏转角度以生成目标扫描部位的核磁共振图像。
  7. 如权利要求6所述的核磁共振成像控制方法，其特征在于，所述控制核磁共振成像设备激发扫描序列对目标扫描部位进行核磁共振扫描以获取多个回波信号的步骤包括：
    控制核磁共振成像设备的射频发射线圈向扫描部位发射射频脉冲以激发扫描部位的核自旋；
    控制核磁共振成像设备的梯度线圈产生梯度场，梯度场对扫描部位激发的核自旋进行编码以产生回波信号，梯度场的相位编码方向相对于预设基准方向旋转预设偏转角度；
    通过核磁共振成像设备的射频接收线圈接收回波信号。
  8. 如权利要求7所述的核磁共振成像控制方法，其特征在于，所述预设偏转角度由运动型参考目标对象的预设参考方向与扫描部位的感兴趣区的预设目标方向在扫描层面上的夹角所确定。
  9. 如权利要求6所述的核磁共振成像控制方法，其特征在于，该方法还包括预先训练所述神经网络模型的步骤，该神经网络模型训练的具体步骤包括：将样本图像输入至待训练的信息识别模型中，得到与样本图像对应的当前输出识别结果；根据当前输出识别结果和样本图像的扫描部位和组织的识别结果的误差，确定所述神经网络模型的损失函数是否收敛；当所述损失函数收敛时，所述神经网络模型训练结束。
  10. 一种计算机可读存储介质，该计算机可读存储介质存储多条计算机程序指令，应用于计算机装置中，该计算机装置连接有核磁共振成像设备，其特征在于，所述计算机程序指令由计算机装置的处理器执行并实现如权利要求6至9任一项所述基于核磁共振成像控制方法。
PCT/CN2020/101520 2019-07-22 2020-07-11 核磁共振成像控制方法、装置及计算机可读存储介质 WO2021012972A1 (zh)

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