WO2022228253A1 - 干扰消除方法、介质及设备 - Google Patents

干扰消除方法、介质及设备 Download PDF

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WO2022228253A1
WO2022228253A1 PCT/CN2022/088036 CN2022088036W WO2022228253A1 WO 2022228253 A1 WO2022228253 A1 WO 2022228253A1 CN 2022088036 W CN2022088036 W CN 2022088036W WO 2022228253 A1 WO2022228253 A1 WO 2022228253A1
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signal
channel
calibration data
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magnetic resonance
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PCT/CN2022/088036
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English (en)
French (fr)
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刘懿龙
朱瑞星
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杭州微影医疗科技有限公司
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Priority to US18/270,599 priority Critical patent/US20240061060A1/en
Publication of WO2022228253A1 publication Critical patent/WO2022228253A1/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
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
    • G01R33/5659—Correction of image distortions, e.g. due to magnetic field inhomogeneities caused by a distortion of the RF magnetic field, e.g. spatial inhomogeneities of the RF magnetic field
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
    • 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
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/42—Screening
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
    • A61B5/004—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part
    • A61B5/0042—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part for the brain
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/369—Electroencephalography [EEG]
    • 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
    • G01R33/4806—Functional imaging of brain activation
    • 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
    • G01R33/583—Calibration of signal excitation or detection systems, e.g. for optimal RF excitation power or frequency
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS TECHNIQUES OR SPEECH SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING TECHNIQUES; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Speech or voice signal processing techniques to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/02—Speech enhancement, e.g. noise reduction or echo cancellation
    • G10L21/0208—Noise filtering
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/18—Shielding or protection of sensors from environmental influences, e.g. protection from mechanical damage
    • A61B2562/182—Electrical shielding, e.g. using a Faraday cage

Definitions

  • the present application relates to the technical field of signal processing, and in particular, to an interference cancellation method, medium and device.
  • the collected magnetic resonance imaging signals are usually affected by interference signals such as electromagnetic interference signals (Electromagnetic Interference, EMI) in the environment, which makes magnetic resonance imaging exist.
  • interference signals such as electromagnetic interference signals (Electromagnetic Interference, EMI)
  • EMI Electromagnetic Interference
  • Artifacts or reduced signal-to-noise ratio of magnetic resonance imaging reducing the accuracy of magnetic resonance imaging.
  • the embodiments of the present application provide an interference cancellation method, medium and device, which can eliminate interference signals from measurement signals received based on multiple channels to obtain valid signals, so as to avoid the influence of interference signals on valid signals.
  • an embodiment of the present application provides an interference cancellation method, which is applied to an electronic device including a first-type channel and a second-type channel with a signal receiving function, including: collecting a mixed effective signal from the first-type channel and the measurement signal of the first interference signal, and collect the second interference signal from the second type channel; according to the coupling relationship between the first calibration data and the second calibration data, and based on the second interference signal, estimate the measurement signal.
  • the first interference signal is obtained;
  • the target effective signal is obtained by removing the first interference signal from the measurement signal; wherein, the first calibration data and the second calibration data are obtained from the first type channel and the second type channel respectively when the electronic device is in a preset state
  • the collected interference signal is obtained.
  • the above method may be applied to scenarios such as magnetic resonance imaging, synchronous EEG functional magnetic resonance imaging, and speech signal processing, but is not limited thereto.
  • the first type of channel described above may be used to receive valid signals, as well as to receive or sense interfering signals; while the second type of channel may be used to receive only interfering signals.
  • the above-mentioned first calibration data and second calibration data only include interference signals, which are relatively pure interference signals. Therefore, the first calibration data and the second calibration data can be used to estimate the coupling relationship of the interference signal between the first type channel and the second type channel, and further, to estimate and remove the interference signal in the actual measurement signal based on the coupling relationship , in order to eliminate the influence of the interference signal on the effective signal.
  • the above-mentioned measurement signals include mixed magnetic resonance imaging signals and electromagnetic interference signals, etc.
  • the above-mentioned first calibration data and second calibration data may be the following calibration data 1 and calibration data 2 respectively.
  • the effective signal and the first interference signal in the above measurement signal may be the magnetic resonance imaging signal and the electromagnetic interference signal 1 below, respectively; and the second interference signal may be the electromagnetic interference signal 2 below.
  • the electromagnetic interference signal in the measurement signal can be estimated and removed according to the above interference elimination method, so as to eliminate the influence of the electromagnetic interference signal on the magnetic resonance imaging signal.
  • artifacts existing in the magnetic resonance imaging can be eliminated, the quality of the magnetic resonance imaging can be improved, and the low-field magnetic resonance imaging equipment can be normally operated in an unshielded or partially shielded environment.
  • the above-mentioned coupling relationship is used to represent the frequency-domain correlation between the interference signal in the first-type channel and the second-type channel, and the coupling relationship is continuous and smooth in the frequency domain .
  • the above coupling relationship can be represented by a coupling function related to the frequency domain, and the coupling function can refer to the coupling function F below.
  • the above-mentioned method further includes: according to the formula And the first calibration data and the second calibration data obtain coefficients c i,j , the coefficients c i,j are used to represent the coupling relationship, and the coefficients c i,j are time-invariant convolution kernel coefficients;
  • the size is 2K+1, that is, the size of the convolution kernel is an odd number, K is a natural number, s r, t is the t-th sampled data from the r-th first-type channel in the first calibration data, and s i, j is the th 2.
  • the jth sampling data from the i-th second-type channel in the calibration data the electronic equipment includes M second-type channels and N first-type channels, i is a positive integer from 1 to M in turn, r Takes a positive integer value from 1 to N in order.
  • the size (also called size) of the convolution kernel can be used to represent the product of the number of rows and columns of the matrix corresponding to the convolution kernel.
  • the above formula is (ie formula (1) below) and the first calibration data and the second calibration data to obtain coefficients c i,j , including: according to the formula For each sampled data from the r-th first-type channel in the first calibration data, an equation with the coefficient of the convolution kernel as the unknown is obtained, and the equations corresponding to all the sampled data for the r-th first-type channel are simultaneously combined A linear system of equations is obtained, and the coefficients ci,j are obtained by solving the linear system of equations.
  • the first interference signal in the measurement signal is estimated based on the coupling relationship between the first calibration data and the second calibration data and based on the second interference signal, including: According to the formula (ie formula (2) below) and the coefficients c i,j and the first interference signal, the second interference signal is estimated; wherein, s′ r,t is the channel from the rth first type in the second interference signal The t-th sampled data of s′ i,j is the j-th sampled data from the i-th channel of the second type in the first interference signal.
  • equation (1) and equation (2) have the same coefficients c i,j .
  • the electronic device is a magnetic resonance imaging device
  • the effective signal is a magnetic resonance imaging signal
  • the interference signal includes at least one of an electromagnetic interference signal and thermal noise
  • the first type of channel That is, the receiving coil channel hereinafter
  • the second type of channel that is, the induction coil channel hereinafter
  • the induction coil channel is realized by one or more phased array coils, or is attached to the surface of the detection object (such as human skin) with one or more electrodes.
  • the electronic device is a synchronous EEG-functional magnetic resonance imaging device
  • the effective signal is an EEG signal
  • the interference signal includes radio frequency signals and gradient signals generated by the magnetic resonance imaging device.
  • At least one item; the first type of channel is realized by one or more electrodes attached to the surface of the detection object (such as the human brain); the second type of channel is realized by one or more electrodes attached to the surface of the detection object (such as the scalp or human body) Electrodes, or one or more phased array coils (such as induction coils hereinafter) are implemented.
  • the electronic device is a magnetic resonance imaging device including a transmitting coil, and the preset state is to turn off the transmitting coil; the method further includes: in the preset state, setting the The signal collected from the first type channel is used as the first calibration data, and the signal collected from the second type channel is used as the second calibration data; wherein, the radio frequency signal emitted by the transmitting coil is used to excite the first type channel to receive valid signals.
  • the radio frequency signal emitted by the transmitter coil is used to excite the receiver coil channel to receive the magnetic resonance imaging signal, and the measurement signal is mainly dominated by electromagnetic interference.
  • the transmitting radio frequency coil is turned off, the transmitting radio frequency coil will not generate magnetic resonance imaging signals, so the signals in the first type channel and the second type channel are only electromagnetic interference signals at this time.
  • the above-mentioned preset state is that the signals in the first-type channel and the second-type channel are collected multiple times; the above-mentioned method further includes: in the case of being in the preset state, the The first signal is used as the first calibration data, and the second signal is used as the second calibration data; wherein, the first signal is the difference between the signals collected from the first type channel twice in a row, and the second signal is the first interference signal. The difference between the two consecutive signals collected from the second type of channel. It can be understood that, for the low-field magnetic resonance imaging device, the magnetic resonance signals may be acquired multiple times to improve the signal-to-noise ratio.
  • Electromagnetic interference signals can be retained as calibration data, while magnetic resonance signals can be eliminated to the greatest extent possible.
  • the electronic device is a magnetic resonance imaging device including gradient coils
  • the preset state is in the dead time during the acquisition of the measurement signal and the second interference signal; in the preset state
  • the signal collected from the first type channel is used as the first calibration data
  • the signal collected from the second type channel is used as the second calibration data; wherein, the dead time The time to wait for the transverse or longitudinal magnetization vector to return to its original state when performing magnetic resonance imaging for magnetic resonance imaging equipment.
  • the electronic device is a magnetic resonance imaging device including a transmitting coil
  • the preset state is that the signals collected from the first type channel and the second type channel are in the frequency domain space (That is, the high-frequency part of the signal in the k-space) is dominated by electromagnetic interference
  • the above method also includes: taking the high-frequency part of the signal in the frequency domain space in the measurement signal as the first calibration data, and using the high frequency part of the second interference signal in the frequency domain space.
  • the frequency part signal is used as the second calibration data.
  • the valid signal and the interference signal are both one-dimensional or multi-dimensional data
  • the convolution kernel is a one-dimensional or multi-dimensional convolution kernel.
  • the dimension of the signal is consistent with the dimension of the convolution kernel.
  • an embodiment of the present application provides an interference cancellation device, which is applied to an electronic device including a first-type channel and a second-type channel with a signal receiving function, including: a collection module for extracting data from the first-type channel Collect the measurement signal mixed with the effective signal and the first interference signal, and collect the second interference signal from the second type channel; the estimation module is used for according to the coupling relationship between the first calibration data and the second calibration data, and based on The collected second interference signal is used to estimate the first interference signal in the measurement signal; the removal module is used to remove the first interference signal from the measurement signal to obtain the target effective signal; wherein the first calibration data and the second calibration data are The interference signals collected from the first type channel and the second type channel respectively when the electronic device is in the preset state.
  • the above-mentioned acquisition module, estimation module and removal module can be implemented by a processor having the functions of these modules or units in the electronic device.
  • the above coupling relationship is used to represent the frequency domain correlation of the interference signal in the first type channel and between the second type channel, and the coupling relationship is continuous and smooth in the frequency domain .
  • the foregoing apparatus further includes: a determination module configured to, according to the formula And the first calibration data and the second calibration data obtain coefficients c i,j , the coefficients c i,j are used to represent the coupling relationship, and the coefficients c i,j are time-invariant convolution kernel coefficients;
  • the size is 2K+1, K is a natural number, s r,t is the t-th sampled data from the r-th first-type channel in the first calibration data, and s i,j is the i-th sampled data from the second calibration data.
  • the j-th sampled data of the second-class channel includes M second-class channels and N first-class channels, i is a positive integer from 1 to M in turn, and r is a positive integer from 1 to N in turn Integer.
  • the above determination may be implemented by a processor having the function of the module or unit in the electronic device.
  • the above determining module is specifically configured to For each sampled data from the r-th first-type channel in the first calibration data, an equation with the coefficient of the convolution kernel as the unknown is obtained, and the equations corresponding to all the sampled data for the r-th first-type channel are simultaneously combined A linear system of equations is obtained, and the coefficients ci,j are obtained by solving the linear system of equations.
  • the above-mentioned estimation of the first interference signal in the measurement signal based on the coupling relationship between the first calibration data and the second calibration data and based on the second interference signal includes: According to the formula and the coefficients c i,j and the first interference signal to estimate the second interference signal; wherein, s′ r,t is the t-th sampled data from the r-th first-type channel in the second interference signal, and s′ i , j is the j-th sampled data from the i-th channel of the second type in the first interference signal.
  • the electronic device is a magnetic resonance imaging device
  • the effective signal is a magnetic resonance imaging signal
  • the interference signal includes at least one of an electromagnetic interference signal and thermal noise
  • the first type of channel is composed of One or more phased array coils are implemented
  • the second type of channel is implemented by one or more phased array coils, or one or more electrodes attached to the surface of the detection object.
  • the electronic device is a synchronized EEG-functional magnetic resonance imaging device
  • the effective signal is an EEG signal
  • the interference signal includes radio frequency signals and gradient signals generated by the magnetic resonance imaging device.
  • At least one item; the first type of channel is realized by one or more electrodes attached to the surface of the detection object; the second type of channel is realized by one or more electrodes attached to the surface of the detection object, or one or more phased array coils accomplish.
  • the electronic device is a magnetic resonance imaging device including a transmitter coil, and the preset state is to turn off the transmitter coil; the device further includes: in the preset state, the The signal collected from the first type channel is used as the first calibration data, and the signal collected from the second type channel is used as the second calibration data; wherein, the radio frequency signal emitted by the transmitting coil is used to excite the first type channel to receive valid signals.
  • the above-mentioned preset state is that the signals in the first-type channel and the second-type channel are collected multiple times; the above-mentioned device further includes: in the case of being in the preset state, the The first signal is used as the first calibration data, and the second signal is used as the second calibration data; wherein, the first signal is the difference between the signals collected from the first type channel twice in a row, and the second signal is the first interference signal. The difference between two consecutive signals acquired from the second type of channel.
  • the electronic device is a magnetic resonance imaging device including gradient coils
  • the preset state is in the dead time during the acquisition of the measurement signal and the second interference signal; in the preset state
  • the signal collected from the first type channel is used as the first calibration data
  • the signal collected from the second type channel is used as the second calibration data; wherein, the dead time The time to wait for the transverse or longitudinal magnetization vector to return to its original state when performing magnetic resonance imaging for magnetic resonance imaging equipment.
  • the electronic device is a magnetic resonance imaging device including a transmitting coil
  • the preset state is that the signals collected from the first type channel and the second type channel are in the frequency domain space.
  • the high-frequency part signal is dominated by electromagnetic interference; the above-mentioned device further comprises: taking the high-frequency part signal in the frequency domain space in the measurement signal as the first calibration data, and taking the high-frequency part signal in the frequency domain space in the second interference signal as the first calibration data. 2. Calibration data.
  • the valid signal and the interference signal are both one-dimensional or multi-dimensional data
  • the convolution kernel is a one-dimensional or multi-dimensional convolution kernel.
  • the dimension of the signal is consistent with the dimension of the convolution kernel.
  • an embodiment of the present application provides a computer-readable storage medium, where instructions are stored on the storage medium, and when executed on a computer, the instructions cause the computer to execute the interference cancellation method in the first aspect.
  • embodiments of the present application provide an electronic device, including: one or more processors; one or more memories; the one or more memories store one or more programs, when the one or more memories When executed by the one or more processors, the program causes the electronic device to execute the interference cancellation method in the first aspect.
  • FIG. 1 shows a schematic structural diagram of a magnetic resonance imaging apparatus according to some embodiments of the present application
  • FIG. 2 shows a schematic flowchart of an interference cancellation method according to some embodiments of the present application
  • FIG. 3 shows a schematic diagram of a convolution kernel according to some embodiments of the present application.
  • FIG. 4 shows a block diagram of a computer of a magnetic resonance imaging apparatus according to some embodiments of the present application
  • FIG. 5 shows a block diagram of a mobile phone according to some embodiments of the present application.
  • Illustrative embodiments of the present application include, but are not limited to, interference cancellation methods, media, and apparatus.
  • the interference elimination method provided by the embodiments of the present application can be applied to scenarios such as magnetic resonance imaging (Magnetic Resonance Imaging, MRI), synchronous EEG functional magnetic resonance imaging, and speech signal processing, but is not limited thereto.
  • the electronic device may include multiple channels with a signal receiving function, so as to eliminate interference signals from the measurement signals of the multiple channels, so as to obtain effective signals that are not affected by the interference signals, such as the magnetic resonance imaging signals in the aforementioned applications, EEG signals, voice signals, etc.
  • the effective signal may be a magnetic resonance imaging signal
  • the interference signal may be thermal noise or an electromagnetic interference signal (Electromagnetic Interference, EMI) in the environment, or the like.
  • the electronic device may be a device having a magnetic resonance imaging function, which is referred to as a magnetic resonance imaging device herein.
  • the effective signal may be an EEG signal
  • the interference signal may include magnetic resonance imaging radio frequency signals and gradient signals generated during the operation of the electronic device.
  • the above-mentioned electronic device may be a device with synchronous electroencephalogram functional magnetic resonance imaging, which may be referred to as an electroencephalogram imaging device herein.
  • the effective signal may be the speech signal to be processed, and the interference signal may be ambient noise or the like.
  • the above-mentioned electronic device may be an electronic device having a voice processing function, such as an electronic device installed with voice assistant software.
  • electronic devices in this scenario may include, but are not limited to: mobile phones, smart speakers, tablet computers, laptop computers, desktop computers, ultra-mobile personal computers (UMPCs), netbooks, and cellular phones , personal digital assistant (personal digital assistant, PDA), augmented reality (augmented reality, AR), virtual reality (virtual reality, VR) equipment and so on.
  • the interference cancellation method provided by the embodiments of the present application is mainly described by taking the interference cancellation method performed by the magnetic resonance imaging device in the magnetic resonance imaging scene as an example. Similarly, the implementation details of the interference cancellation method performed by the electronic device in other application scenarios will not be repeated here. For some descriptions, reference may be made to the relevant description of the interference cancellation method performed by the magnetic resonance imaging device.
  • Magnetic resonance imaging technology can generate medical images in medical or clinical application scenarios for disease diagnosis. Specifically, magnetic resonance imaging technology can use the signals generated by the resonance of atomic nuclei in a strong magnetic field to perform image reconstruction, and to make cross-sectional, sagittal, coronal and various oblique tomographic images of objects such as the human body.
  • the magnetic resonance imaging device may be a low-field or ultra-low-field magnetic resonance imaging device, or a mid-field or high-field magnetic resonance imaging device.
  • magnetic resonance imaging systems in clinical applications can generally be divided into high-field (above 1T), mid-field (0.3-1T), low-field (0.1-0.3T), ultra-low-field (0.1 below T).
  • magnetic resonance imaging equipment usually needs to be deployed in specific rooms or areas of hospitals or research institutions to achieve strict electromagnetic shielding. Cannot be used as a general-purpose imaging device.
  • the deployment site is not limited, for example, it is not limited to use in hospitals or research institutions, and a small portable magnetic resonance imaging device with low cost will greatly expand the application scenarios of magnetic resonance imaging.
  • the embodiments of the present application are mainly applied to low-field or ultra-low-field magnetic resonance imaging equipment, to eliminate interference signals such as environmental electromagnetic interference signals in the magnetic resonance imaging process, thereby eliminating artifacts existing in magnetic resonance imaging and improving magnetic resonance imaging.
  • the quality of resonance imaging enabling low-field MRI equipment to function properly in an unshielded or partially shielded environment.
  • the magnetic resonance imaging equipment does not require strict electromagnetic shielding, that is, the magnetic resonance imaging equipment does not need to be placed in the shielding room, there is no need to build a special shielding room, the installation is simple, and the cost can be greatly reduced.
  • the application scenarios of magnetic resonance imaging can be greatly expanded, for example, it can be applied to bedside magnetic resonance imaging (Point-Of-Care MRI, POC MRI), emergency room (ICU), or medical vehicles and ambulances.
  • one or more multi-channel coils eg, phased array coils
  • one or more electrodes that can be attached to the human skin surface can be used to receive signals.
  • the above-mentioned coils or electrodes can be divided into two categories.
  • a type of coil called a receiving coil, is used to receive magnetic resonance signals (specifically, magnetic resonance imaging signals), and should avoid receiving interference signals such as electromagnetic interference signals or thermal noise in the environment.
  • the receiving coil will inevitably be affected by electromagnetic interference, that is, the receiving coil will also receive some electromagnetic interference signals.
  • the other coil called the sensing coil, is used to sense environmental electromagnetic interference signals, and this function can also be achieved with electrodes.
  • the magnetic resonance imaging apparatus 100 may include: a computer 101, a spectrometer 102, a gradient amplifier 103, a gradient coil 104, a transmitting radio frequency amplifier 105, a transmitting radio frequency coil (also referred to as a transmitting coil) 106, a receiving radio frequency coil 107, a receiving radio frequency amplifier ( Also referred to as a receive coil) 108, a magnet 109, an induction coil 101 and a receive radio frequency amplifier 110.
  • the computer 101 is configured to issue an instruction to the spectrometer 102 under the control of the operator, so as to trigger the spectrometer 102 to generate the waveform of the gradient signal and the waveform of the radio frequency signal according to the instruction.
  • the gradient signal generated by the spectrometer 102 is amplified by the gradient amplifier 103, the gradient of the magnetic field is formed by the gradient coil 104, thereby realizing the spatial gradient encoding of the magnetic resonance signal (specifically, the magnetic resonance imaging signal).
  • the spatial gradient coding is used to spatially localize the magnetic resonance signals, ie to distinguish the location of the source of the magnetic resonance signals.
  • the radio frequency signal generated by the spectrometer 102 is amplified by the transmitting radio frequency amplifier 105 and emitted by the transmitting radio frequency coil 106 to excite the protons (hydrogen nuclei) in the imaging area.
  • the excited protons can send out radio frequency signals, which can be received by the receiving coil 108, amplified by the receiving radio frequency amplifier 107, and then converted into digital signals by the spectrometer 102, and then sent to the computer 101 for processing to obtain images and display.
  • magnet 109 may be any suitable type of magnet capable of generating a main magnetic field.
  • the induction coil 101 is used for sensing the electromagnetic interference signal in the environment, and after being amplified by the receiving radio frequency amplifier 110 , it is converted into a digital signal by the spectrometer 102 and sent to the computer 101 for processing.
  • both the receiver coil and the induction coil need to be designed to maximize the signal-to-noise ratio that the coil can provide. That is, the receiving coil should be able to receive magnetic resonance signals (specifically, magnetic resonance imaging signals) as sensitively as possible, and be less affected by electromagnetic interference and thermal noise as much as possible. For the induction coil, it should be able to sense ambient electromagnetic interference as sensitively as possible, receive magnetic resonance signals as little as possible, and be affected by thermal noise as little as possible.
  • the above two types of coils need to reduce the influence of thermal noise as much as possible.
  • some cooling devices can use cooling to minimize coil resistance, thereby reducing thermal effect of noise. It can be understood that, the embodiment of the present application does not specifically describe the cooling device, and reference may be made to any achievable manner in the related art.
  • the EEG imaging device in this embodiment of the present application may also include the transmitting coil 106 and the receiving coil 108 shown in FIG. 1 , which are used to generate magnetic resonance imaging radio frequency signals based on the same process; to generate gradient signals.
  • the above-mentioned receiving coils and induction coils may be implemented using single or multiple phased array coils that are widely used in modern medical magnetic resonance imaging.
  • the above-mentioned induction coil can also be replaced with an electrode attached to the surface of the human skin. Signal.
  • the multiple channels with the signal receiving function involved in the magnetic resonance imaging apparatus 100 may include multiple channels of a single phased array coil, or may include multiple channels of multiple coils.
  • the design and layout (deployment position, deployment direction, etc.) of the receiving coil and the induction coil in the magnetic resonance imaging device 100 are not specifically limited, and may be any achievable solution.
  • the channel in the receiving coil may be referred to as a receiving coil channel.
  • the receiving coils of multiple channels may also be used to enhance the ability to identify and eliminate electromagnetic interference signals.
  • the channels in the induction coil may be referred to as induction coil channels. Among them, the more channels of the induction coil, the more accurately the characteristics of the electromagnetic interference signal can be depicted, so that the electromagnetic interference signal received by the receiving coil can be accurately estimated through the electromagnetic interference signal received by the induction coil.
  • the magnetic resonance imaging apparatus 100 shown in FIG. 1 may provide one receiving coil and one induction coil, and the receiving coil has one channel and the induction coil has two channels, but is not limited thereto.
  • the plurality of channels provided by the magnetic resonance imaging apparatus 100 include a receiving coil channel and an induction coil channel.
  • the multiple channels with signal receiving function provided by the EEG device can be realized by electrodes attached to the scalp.
  • the multiple channels provided by the electronic device may be multiple analog signal channels provided by multiple microphones.
  • the magnetic resonance imaging apparatus 100 shown in FIG. 1 can acquire measurement signals from the receiving coil channel and the induction coil channel, and acquire calibration data from these channels. Furthermore, according to the calibration data, the electromagnetic interference signal in the actually collected measurement signal can be estimated by means of convolution operation, so as to realize the elimination of electromagnetic interference.
  • the calibration data only includes electromagnetic interference signals from the receiving coil channel and the induction coil channel of the magnetic resonance imaging apparatus 100 . That is, the above calibration data are relatively pure electromagnetic interference signals, so that they can be used to estimate the coupling relationship between the electromagnetic interference signals received by different channels.
  • the calibration data is electromagnetic interference signals acquired from the receiving coil channel and the induction coil channel when the magnetic resonance imaging apparatus 100 is in a preset state.
  • the magnetic resonance imaging apparatus 100 may acquire calibration data in the following manners (1) to (4):
  • Pre-scan (pre-scan) method (1) Pre-scan (pre-scan) method:
  • the magnetic resonance imaging apparatus 100 acquires measurement signals from the reception coil channel and the induction coil channel when the transmission coil (ie, the above-mentioned transmission radio frequency coil 106 ) is turned off, and uses these measurement signals as calibration data.
  • the radio frequency signal emitted by the transmitting coil is used to excite atomic nuclei (such as hydrogen nuclei) in the imaging object, and the excited atomic nuclei will emit magnetic resonance imaging signals, which are then received by the receiving coil channel. If the transmitter coil is turned off, the measurement signal received by the receiver coil does not contain the magnetic resonance imaging signal, but consists entirely of electromagnetic interference and thermal noise.
  • the magnetic resonance imaging apparatus 100 may turn off the transmitting radio frequency coil before or after acquiring the magnetic resonance imaging signal (then the receiving radio frequency coil will not receive the magnetic resonance imaging signal) to acquire the above calibration data.
  • this method has two major drawbacks, one is that it will prolong the total scanning time of the magnetic resonance imaging apparatus 100; moreover, if the electromagnetic interference signal in the environment changes, or the signal is in the If the coupling relationship between the channels changes, the calibration data cannot be used to accurately estimate the coupling relationship between the electromagnetic interference signals between the channels during a formal magnetic resonance imaging scan.
  • the above-mentioned preset state is that the transmitting coil 106 of the magnetic resonance imaging apparatus 100 is turned off.
  • the coupling relationship of the electromagnetic interference signal among the multiple channels of the magnetic resonance imaging apparatus 100 is specifically the frequency domain correlation of the electromagnetic interference signal between the multiple channels, and the coupling relationship is continuous and continuous in the frequency domain. smooth. It can be understood that the frequency domain correlation of electromagnetic interference signals among multiple channels can be expressed as a linear relationship of electromagnetic interference signals received by each channel at different frequency points.
  • the above coupling relationship can be represented by a coupling function related to the frequency domain, and the coupling function is continuous and smooth in the frequency domain.
  • the electromagnetic interference signal sensed by the induction coil channel included in the calibration data may be used c sen
  • the difference between the signals acquired from the plurality of channels two consecutive times is used as calibration data.
  • the magnetic resonance imaging apparatus 100 takes the difference between the two consecutively acquired signals from the receiving coil channel as part of the calibration data, and takes the difference between the two consecutively acquired signals from the receiving coil channel as Another part of the calibration data.
  • the low-field magnetic resonance imaging apparatus can acquire magnetic resonance signals multiple times to realize magnetic resonance imaging. Specifically, for the signals acquired by the magnetic resonance imaging device for multiple times, it can be considered that the magnetic resonance signals acquired in the two adjacent acquisitions are theoretically unchanged, while the electromagnetic interference signals are randomly changed; by subtracting the two adjacent acquisitions, Electromagnetic interference signals can be retained as calibration data, while magnetic resonance signals can be eliminated to the greatest extent possible.
  • the magnetic resonance imaging apparatus 100 corrupts the magnetic resonance imaging signal using the corruption gradient from the gradient coil within a deadtime during the actual acquisition of signals from the plurality of channels, and acquires the measurement signals from the plurality of channels, and uses the measurement signals as Calibration data.
  • the dead time is the time for waiting for the transverse or longitudinal magnetization vector to return to the original state when the magnetic resonance imaging device performs the magnetic resonance imaging.
  • the calibration data includes measurement signals collected from the receiver coil channel and measurement signals collected from the induction coil channel.
  • the above-mentioned preset state may be that the magnetic resonance imaging apparatus 100 is in a dead time during signal acquisition.
  • the use of the dead time in the scanning process to collect calibration data can avoid the problems in (1) and (2) above, but the scanning sequence needs to be modified, which will also increase the amount of data collected and increase the follow-up. Calculation difficulty.
  • the gradient coil it is also necessary to turn on the gradient coil to generate the readout gradient.
  • a crusher gradient it is necessary to add a crusher gradient to the gradient coil, which can minimize the components of the magnetic resonance imaging signal in the calibration data.
  • FSE fast spin echo
  • ETL echo train length
  • the transmitting RF coil can be turned off (i.e. turned off 180-degree refocusing of radio frequency pulses), and then collect calibration data.
  • the magnetic resonance imaging apparatus 100 uses the high-frequency part signal in the frequency domain space among the signals acquired from the plurality of channels as calibration data.
  • the calibration data includes the signals collected from the receiver coil channel and the signal collected from the induction coil channel.
  • the high-frequency part of the MRI signal in the frequency domain space ie k-space
  • this part of the data is used as calibration data.
  • the execution body of the interference cancellation method of the present application may be the magnetic resonance imaging apparatus 100 , and specifically the computer 101 in the magnetic resonance imaging apparatus 100 .
  • the flow of an interference cancellation method provided by the present application may include the following steps 201-205:
  • Step 201 The magnetic resonance imaging apparatus 100 acquires calibration data 1 from the receiver line coil channel, and acquires calibration data 2 from the induction coil channel.
  • the entirety of the calibration data 1 and the calibration data 2 is the calibration data acquired by the magnetic resonance imaging apparatus 100 from multiple channels.
  • Step 202 the magnetic resonance imaging apparatus 100 obtains the measurement signal from the receiving line coil channel, and obtains the electromagnetic interference signal 1 from the induction coil channel.
  • the whole of the above-mentioned measurement signal and electromagnetic interference signal 1 is taken as a signal actually acquired by the magnetic resonance imaging apparatus 100 from multiple channels.
  • the above-mentioned measurement signal and electromagnetic interference signal 1 are acquired from multiple channels for multiple times.
  • Step 203 the magnetic resonance imaging apparatus 100 according to the formula (ie formula (1)) and calibration data 1 and calibration data 2 to obtain coefficients c i,j , and the coefficients c i,j are time-invariant convolution kernel coefficients.
  • the coefficients c i,j are used to represent the coupling relationship of the electromagnetic interference signal between the receiving coil channel and the induction coil channel.
  • the size of the convolution kernel corresponding to the coefficients c i,j is 2K+1, that is, the size of the convolution kernel is an odd number, K is a natural number, and s r, t is the calibration data 1 from the rth receiving coil channel.
  • t sampling data, s i,j are the j th sampling data from the i th induction coil channel in the calibration data 2
  • the magnetic resonance imaging apparatus 100 includes M induction coil channels and N receiving coil channels, i is taken sequentially.
  • the value is a positive integer from 1 to M
  • r is a positive integer from 1 to N in turn.
  • the size (also called size) of the convolution kernel can be used to represent the product of the number of rows and columns of the matrix corresponding to the convolution kernel.
  • channel 1 to channel M shown in FIG. 3 are all induction coil channels provided by the induction coil, and channel r is provided by the receiving coil. Receive coil channel.
  • the size of the convolution kernel is 2K+1
  • the convolution kernel is a matrix of (2K+1) ⁇ M.
  • the sampled data corresponding to one convolution kernel in channel 1-channel M corresponds to the t-th sampled data in channel r.
  • the magnetic resonance imaging apparatus 100 operates according to the formula For each sampled data from the rth receiving coil channel in the calibration data 1, an equation with the convolution kernel coefficient as the unknown is obtained separately, and the equations corresponding to all the sampled data for the rth receiving coil channel are simultaneously obtained to obtain an equation A system of linear equations, the coefficients c i,j are obtained by solving the system of linear equations.
  • Step 204 the magnetic resonance imaging apparatus 100 according to the formula (ie formula (2)) and the coefficients c i,j and the electromagnetic interference signal 1, the electromagnetic interference signal 2 in the measurement signal is estimated.
  • s' r,t is the t-th sampling data from the r-th receiving coil channel in the electromagnetic interference signal 2
  • s' i,j is the j-th sampling data from the i-th induction coil channel in the electromagnetic interference signal 1 data.
  • equation (1) and equation (2) have the same coefficients c i,j .
  • Step 205 The magnetic resonance imaging apparatus 100 removes the electromagnetic interference signal 2 from the measurement signal to obtain a magnetic resonance imaging signal.
  • the magnetic resonance imaging apparatus 100 may acquire a convolution kernel from the calibration data, and estimate the electromagnetic interference signal in the receiving coil based on the electromagnetic interference signal measured by the induction coil based on the convolution kernel, and use the Eliminate the influence of the electromagnetic interference signal on the magnetic resonance imaging signal, thereby improving the quality of the magnetic resonance imaging.
  • the electronic device may also implement the interference cancellation method according to steps similar to the above steps 201-205, except that the execution subject is different, the sources of multiple channels are different, and the effective signal and There are different types of interfering signals.
  • the valid signal and the interference signal may also be one-dimensional data or multi-dimensional data (eg, two-dimensional data).
  • the convolution kernel used in the interference elimination method can be a one-dimensional or multi-dimensional convolution kernel, that is, the dimension of the signal is consistent with the dimension of the convolution kernel, and other processes are related to the above steps 201-205. The description is similar and will not be repeated here.
  • FIG. 4 schematically illustrates an example computer 1400 in accordance with various embodiments.
  • the system 1400 may include one or more processors 1404 , system control logic 1408 coupled to at least one of the processors 1404 , system memory 1412 coupled to the system control logic 1408 , coupled to the system control logic 1408 non-volatile memory (NVM) 1416 , and a network interface 1420 to the system control logic 1408 .
  • processors 1404 the system control logic 1408 coupled to at least one of the processors 1404
  • system memory 1412 coupled to the system control logic 1408
  • NVM non-volatile memory
  • processor 1404 may include one or more single-core or multi-core processors. In some embodiments, processor 1404 may include any combination of general purpose processors and special purpose processors (eg, graphics processors, application processors, baseband processors, etc.). In an embodiment in which the computer 1400 adopts an eNB (Evolved Node B, enhanced base station) 101 or a RAN (Radio Access Network, radio access network) controller 102, the processor 1404 may be configured to execute various conforming embodiments, For example, one or more of the various embodiments shown in FIG. 2 . For example, the processor 1404 can estimate the interference signal in the actual measurement signal based on the convolution operation on the calibration data from multiple channels, and then remove the interference signal in the measurement signal to obtain the final effective signal.
  • eNB evolved Node B, enhanced base station
  • RAN Radio Access Network, radio access network
  • system control logic 1408 may include any suitable interface controller to provide any suitable interface to at least one of processors 1404 and/or any suitable device or component in communication with system control logic 1408 .
  • system control logic 1408 may include one or more memory controllers to provide an interface to system memory 1412 .
  • System memory 1412 may be used to load as well as store data and/or instructions.
  • the memory 1412 of the system 1400 in some embodiments may include any suitable volatile memory, such as suitable dynamic random access memory (DRAM).
  • DRAM dynamic random access memory
  • NVM/memory 1416 may include one or more tangible, non-transitory computer-readable media for storing data and/or instructions.
  • the NVM/memory 1416 may include any suitable non-volatile memory such as flash memory and/or any suitable non-volatile storage device, such as HDD (Hard Disk Drive, hard disk drive), CD (Compact Disc) , CD-ROM) drive, at least one of DVD (Digital Versatile Disc, Digital Versatile Disc) drive.
  • NVM/storage 1416 may include a portion of storage resources on the device where system 1400 is installed, or it may be accessed by, but not necessarily be part of, a device. For example, NVM/storage 1416 may be accessed over the network via network interface 1420 .
  • system memory 1412 and NVM/memory 1416 may include a temporary copy and a permanent copy of instructions 1424, respectively.
  • the instructions 1424 may include instructions that when executed by at least one of the processors 1404 cause the computer 1400 to implement the method shown in FIG. 2 .
  • instructions 1424 , hardware, firmware, and/or software components thereof may additionally/alternatively reside in system control logic 1408 , network interface 1420 , and/or processor 1404 .
  • Network interface 1420 may include a transceiver for providing a radio interface for system 1400 to communicate with any other suitable devices (eg, front-end modules, antennas, etc.) over one or more networks.
  • network interface 1420 may be integrated with other components of system 1400 .
  • network interface 1420 may be integrated with at least one of processor 1404, system memory 1412, NVM/memory 1416, and a firmware device (not shown) having instructions when at least one of processors 1404 executes the When instructed, the computer 1400 implements the method shown in FIG. 2 .
  • Network interface 1420 may further include any suitable hardware and/or firmware to provide a multiple-input multiple-output radio interface.
  • network interface 1420 may be a network adapter, wireless network adapter, telephone modem, and/or wireless modem.
  • At least one of the processors 1404 may be packaged with logic for one or more controllers of the system control logic 1408 to form a system-in-package (SiP). In one embodiment, at least one of the processors 1404 may be integrated on the same die with logic for one or more controllers of the system control logic 1408 to form a system on a chip (SoC).
  • SiP system-in-package
  • SoC system on a chip
  • Computer 1400 may further include an input/output (I/O) device 1432 .
  • I/O device 1432 may include a user interface that enables a user to interact with system 1400 ; the peripheral component interface is designed to enable peripheral components to interact with computer 1400 as well.
  • computer 1400 also includes sensors for determining at least one of environmental conditions and location information associated with computer 1400 .
  • the user interface may include, but is not limited to, a display (eg, a liquid crystal display, a touch screen display, etc.), a speaker, a microphone, one or more cameras (eg, a still image camera and/or video camera), a flashlight (eg, a LED flash) and keyboard.
  • a display eg, a liquid crystal display, a touch screen display, etc.
  • a speaker e.g., a speaker
  • a microphone e.g, a microphone
  • one or more cameras eg, a still image camera and/or video camera
  • a flashlight eg, a LED flash
  • peripheral component interfaces may include, but are not limited to, non-volatile memory ports, audio jacks, and power connectors.
  • sensors may include, but are not limited to, gyroscope sensors, accelerometers, proximity sensors, ambient light sensors, and positioning units.
  • the positioning unit may also be part of or interact with the network interface 1420 to communicate with components of the positioning network (eg, global positioning system (GPS) satellites).
  • GPS global positioning system
  • the electronic device for performing interference cancellation in the present application is a mobile phone as an example for illustration, and the structure of the electronic device is described.
  • the mobile phone 10 may include a processor 110 , a power supply module 140 , a memory 180 , a mobile communication module 130 , a wireless communication module 120 , a sensor module 190 , an audio module 150 , a camera 170 , an interface module 160 , buttons 101 and a display screen 102, etc.
  • the structures illustrated in the embodiments of the present invention do not constitute a specific limitation on the mobile phone 10 .
  • the mobile phone 10 may include more or less components than shown, or combine some components, or separate some components, or arrange different components.
  • the illustrated components may be implemented in hardware, software, or a combination of software and hardware.
  • Processor 110 may include one or more processing units.
  • a storage unit may be provided in the processor 110 for storing instructions and data.
  • the storage unit in processor 110 is cache memory 180 .
  • the processor 110 may estimate the interference signal in the actual measurement signal based on the convolution operation on the calibration data from multiple channels, and then remove the interference signal in the measurement signal to obtain the final effective signal.
  • the power module 140 may include power supplies, power management components, and the like.
  • the power source can be a battery.
  • the power management part is used to manage the charging of the power supply and the power supply of the power supply to other modules.
  • the mobile communication module 130 may include, but is not limited to, an antenna, a power amplifier, a filter, an LNA (Low noise amplify, low noise amplifier), and the like.
  • the wireless communication module 120 may include an antenna, and transmit and receive electromagnetic waves via the antenna.
  • the cell phone 10 can communicate with the network and other devices through wireless communication technology.
  • the mobile communication module 130 and the wireless communication module 120 of the handset 10 may also be located in the same module.
  • the display screen 102 is used for displaying human-computer interaction interfaces, images, videos, etc., for example, for displaying semantic information of speech corresponding to the valid signals processed by the processor 110 .
  • Display screen 102 includes a display panel.
  • the sensor module 190 may include a proximity light sensor, a pressure sensor, a gyro sensor, an air pressure sensor, a magnetic sensor, an acceleration sensor, a distance sensor, a fingerprint sensor, a temperature sensor, a touch sensor, an ambient light sensor, a bone conduction sensor, and the like.
  • the audio module 150 is used for converting digital audio information into analog audio signal output, or converting analog audio input into digital audio signal. Audio module 150 may also be used to encode and decode audio signals. In some embodiments, the audio module 150 may be provided in the processor 110 , or some functional modules of the audio module 150 may be provided in the processor 110 . In some embodiments, the audio module 150 may include a speaker, earpiece, microphone, and headphone jack. For example, microphones can be used to provide multiple channels for acquiring calibration data or acquiring measurement signals.
  • the cell phone 10 further includes a button 101, a motor, an indicator, and the like.
  • the key 101 may include a volume key, an on/off key, and the like.
  • Embodiments of the mechanisms disclosed herein may be implemented in hardware, software, firmware, or a combination of these implementation methods.
  • Embodiments of the present application may be implemented as a computer program or program code executing on a programmable system including at least one processor, a storage system (including volatile and nonvolatile memory and/or storage elements) , at least one input device, and at least one output device.
  • Program code may be applied to input instructions to perform the functions described herein and to generate output information.
  • the output information can be applied to one or more output devices in a known manner.
  • a processing system includes any system having a processor such as, for example, a digital signal processor (DSP), microcontroller, application specific integrated circuit (ASIC), or microprocessor.
  • DSP digital signal processor
  • ASIC application specific integrated circuit
  • the program code may be implemented in a high-level procedural language or an object-oriented programming language to communicate with the processing system.
  • the program code may also be implemented in assembly or machine language, if desired.
  • the mechanisms described in this application are not limited in scope to any particular programming language. In either case, the language may be a compiled language or an interpreted language.
  • the disclosed embodiments may be implemented in hardware, firmware, software, or any combination thereof.
  • the disclosed embodiments can also be implemented as instructions carried by or stored on one or more transitory or non-transitory machine-readable (eg, computer-readable) storage media, which can be executed by one or more processors read and execute.
  • the instructions may be distributed over a network or over other computer-readable media.
  • a machine-readable medium can include any mechanism for storing or transmitting information in a form readable by a machine (eg, a computer), including, but not limited to, floppy disks, optical disks, optical disks, read only memories (CD-ROMs), magnetic Optical Disc, Read Only Memory (ROM), Random Access Memory (RAM), Erasable Programmable Read Only Memory (EPROM), Electrically Erasable Programmable Read Only Memory (EEPROM), Magnetic or Optical Cards, Flash Memory, or Tangible machine-readable storage for transmitting information (eg, carrier waves, infrared signal digital signals, etc.) using the Internet in electrical, optical, acoustic, or other forms of propagating signals.
  • machine-readable media includes any type of machine-readable media suitable for storing or transmitting electronic instructions or information in a form readable by a machine (eg, a computer).
  • each unit/module mentioned in each device embodiment of this application is a logical unit/module.
  • a logical unit/module may be a physical unit/module or a physical unit/module.
  • a part of a module can also be implemented by a combination of multiple physical units/modules.
  • the physical implementation of these logical units/modules is not the most important, and the combination of functions implemented by these logical units/modules is the solution to the problem of this application. The crux of the technical question raised.
  • the above-mentioned device embodiments of the present application do not introduce units/modules that are not closely related to solving the technical problems raised in the present application, which does not mean that the above-mentioned device embodiments do not exist. other units/modules.

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Abstract

一种干扰消除方法、介质及设备，可以从基于多个通道接收的测量信号中消除干扰信号得到有效信号，以避免干扰信号对有效信号的影响。方法包括：从第一类通道中采集混合有有效信号和第一干扰信号的测量信号，并从第二类通道中采集第二干扰信号；根据第一校准数据和第二校准数据之间的耦合关系，并基于第二干扰信号，估计出测量信号中的第一干扰信号；从测量信号中去除第一干扰信号得到目标有效信号；其中，第一校准数据和第二校准数据为电子设备处于预设状态时从第一类通道和第二类通道分别采集到的干扰信号。方法具体可以用于消除电磁干扰信号对磁共振成像信号的影响的场景中。

Description

干扰消除方法、介质及设备 技术领域
本申请涉及信号处理技术领域，特别涉及一种干扰消除方法、介质及设备。
背景技术
随着电气、电子设备的大量应用，人们对于电子设备接收到的信号的质量的要求越来越高。通常电子设备所处的环境存在干扰(Interference)，并且电子设备的运行过程以及馈线系统也会产生干扰，这使得电子设备接收到的有效信号会受到其他干扰信号的影响。也就是说，干扰信号会对有效信号的接收造成损害，从而导致电子设备获取的有效信号失真或者信噪比(signal-to-noise ratio，SNR)降低。
例如，对于磁共振成像(Magnetic Resonance Imaging，MRI)设备而言，采集的磁共振成像信号通常会受到环境中的电磁干扰信号(ElectromagneticInterference，EMI)等干扰信号的影响，进而使得磁共振成像中存在伪影或者降低磁共振成像的信噪比，降低了磁共振成像的准确性。为了避免电磁干扰信号对磁共振成像质量的影响，通常需要对磁共振成像设备进行严格的电磁屏蔽，如将磁共振成像设备放置于特定的房间内，而电磁屏蔽将会极大地限制磁共振成像的应用场景。
发明内容
本申请实施例提供了一种干扰消除方法、介质及设备，可以从基于多个通道接收的测量信号中消除干扰信号得到有效信号，以避免干扰信号对有效信号的影响。
第一方面，本申请实施例提供了一种干扰消除方法，应用于包括具有信号接收功能的第一类通道和第二类通道的电子设备，包括：从第一类通道中采集混合有有效信号和第一干扰信号的测量信号，并从第二类通道中采集第二干扰信号；根据第一校准数据和第二校准数据之间的耦合关系，并基于第二干扰信号，估计出测量信号中的第一干扰信号；从测量信号中去除第一干扰信号得到目标有效信号；其中，第一校准数据和第二校准数据为电子设备处于预设状态时从第一类通道和第二类通道分别采集到的干扰信号。作为一种示例，上述方法可以应用于磁共振成像、同步脑电功能磁共振成像以及语音信号处理等场景中，但不限于此。例如，上述第一类通道可以用于接收有效信号，以及接收或感应干扰信号；而第 二类通道可以仅用于接收干扰信号。而上述第一校准数据和第二校准数据中仅包含干扰信号，即为较为纯粹的干扰信号。从而，可以使用第一校准数据和第二校准数据来估计干扰信号在第一类通道和第二类通道之间的耦合关系，进而，实现基于该耦合关系估计并去除实际测量信号中的干扰信号，以消除干扰信号对有效信号的影响。例如，在磁共振成像场景中，上述测量信号包括混合的磁共振成像信号和电磁干扰信号等，例如，上述第一校准数据和第二校准数据可以分别为下文中的校准数据1和校准数据2；上述测量信号中的有效信号和第一干扰信号，可以分别为下文中的磁共振成像信号和电磁干扰信号1；而第二干扰信号可以为下文中的电磁干扰信号2。具体地，在磁共振成像场景中，按照上述干扰消除方法可以估计并去除测量信号中的电磁干扰信号，以消除电磁干扰信号对磁共振成像信号的影响。进而，可以消除磁共振成像中存在的伪影，提高磁共振成像的质量，实现在未屏蔽或部分屏蔽的环境中正常运行低场磁共振成像设备。
在上述第一方面的一种可能的实现中，上述耦合关系用于表示干扰信号在第一类通道中和第二类通道之间的频域相关性，且耦合关系在频域上连续且平滑。例如，上述耦合关系可以通过频域相关的耦合函数表示，该耦合函数可以参照下文中的耦合函数F。
在上述第一方面的一种可能的实现中，上述方法还包括：根据公式
Figure PCTCN2022088036-appb-000001
以及第一校准数据和第二校准数据得到系数c i,j，系数c i,j用于表示耦合关系，且系数c i,j为时不变的卷积核系数；其中，卷积核的尺寸为2K+1，即卷积核的尺寸为奇数，K为自然数，s r,t为第一校准数据中来自第r个第一类通道的第t个采样数据，s i,j为第二校准数据中来自第i个第二类通道的第j个采样数据，电子设备中包括M个第二类通道和N个第一类通道，i依次取值为1到M的正整数，r依次取值为1到N的正整数。例如，卷积核的尺寸(也称大小)可以用于表示卷积核对应的矩阵的行数和列数的乘积。
在上述第一方面的一种可能的实现中，上述根据公式
Figure PCTCN2022088036-appb-000002
(即下文中的公式(1))以及第一校准数据和第二校准数据得到系数c i,j，包括：根据公式
Figure PCTCN2022088036-appb-000003
针对第一校准数据中来自第r个第一类通道的每个采样数据分别得到一个以卷积核系数为未知数的方程，并将针对r个第一类通道的所有采样数据对应的方程联立得到一个线性方程组，求解线性方程组得到系数c i,j。
在上述第一方面的一种可能的实现中，上述根据第一校准数据和第二校准数据之间的耦合关系，并基于第二干扰信号，估计出测量信号中的第一干扰信号，包括：根据公式
Figure PCTCN2022088036-appb-000004
(即下文中的公式(2))以及系数c i,j和第一干扰信号，估计出第二干扰信号；其中，s′ r,t为第二干扰信号中来自第r个第一类通道的第t个采样数据，s′ i,j为第一干扰信号中来自第i个第二类通道的第j个采样数据。可以理解的是，由于第二干扰信号和第一干扰信号在各个通道之间耦合关系，与第一校准数据和第二校准数据在各个通道之间耦合关系是一致的。因此，公式(1)和公式(2)中具有相同的系数c i,j。
在上述第一方面的一种可能的实现中，上述电子设备为磁共振成像设备，有效信号为磁共振成像信号，干扰信号包括电磁干扰信号和热噪声中的至少一项；第一类通道(即下文中的接收线圈通道)由一个或多个相控阵线圈实现；第二类通道(即下文中的感应线圈通道)由一个或多个相控阵线圈，或者贴附于检测对象表面(如人体皮肤)的一个或多个电极实现。
在上述第一方面的一种可能的实现中，上述电子设备为同步脑电-功能磁共振成像设备，有效信号为脑电信号，干扰信号包括磁共振成像设备产生的射频信号和梯度信号中的至少一项；第一类通道由贴附在检测对象(如人脑)表面的一个或多个电极实现；第二类通道由贴附在检测对象(如头皮或人体)表面的一个或多个电极，或者一个或多个相控阵线圈(如下文中的感应线圈)实现。
在上述第一方面的一种可能的实现中，上述电子设备为包括发射线圈的磁共振成像设备，且预设状态为关闭发射线圈；上述方法还包括：在处于预设状态的情况下，将从第一类通道采集的信号作为第一校准数据，并从第二类通道采集的信号作为第二校准数据；其中，发射线圈发射的射频信号用于激发第一类通道接收有效信号。其中，发射线圈发射的射频信号用于激发接收线圈通道接收磁共振成像信号，该测量信号主要由电磁干扰主导。而关闭发射射频线圈时发射射频线圈将不会产生磁共振成像信号，因此此时第一类通道和第二类通道中的信号均仅为电磁干扰信号。
在上述第一方面的一种可能的实现中，上述预设状态为第一类通道和第二类通道中的信号被多次采集；上述方法还包括：在处于预设状态的情况下，将第一信号作为第一校准数据，第二信号作为第二校准数据；其中，第一信号为连续两次从第一类通道采集的信号之间的差值，第二信号为第一干扰信号中该连续两次从第二类通道采集的信号之间的差值。可以理解的是，对于低场磁共振成像设备可以多次采集磁共振信号以提高信噪比。具体地，对于磁共振成像设备多次采集的信号，可以认为相近两次采集的磁共振信号理论上是不变的，而电磁干扰信号则是随机变化的；通过对相近两次采集相减，可以保留电磁干扰信号作为校准数据，而最大程度地消去磁共振信号。
在上述第一方面的一种可能的实现中，上述电子设备为包括梯度线圈的磁共振成像设备，且预设状态为处于获取测量信号和第二干扰信号期间的死时间内；在处于预设状态的情况下，使用来自梯度线圈的损毁梯度损毁有效信号，将从第一类通道采集的信号作为第一校准数据，并从第二类通道采集的信号作为第二校准数据；其中，死时间为磁共振成像设备执行磁共振成像时用于等待横向或纵向磁化矢量恢复到原有状态的时间。
在上述第一方面的一种可能的实现中，上述电子设备为包括发射线圈的磁共振成像设备，且预设状态为从第一类通道和第二类通道采集的信号中在频域空间(即k空间)的高频部分信号由电磁干扰主导；上述方法还包括：将测量信号中在频域空间的高频部分信号作为第一校准数据，将第二干扰信号中在频域空间的高频部分信号作为第二校准数据。
在上述第一方面的一种可能的实现中，上述有效信号和干扰信号均为一维或者多维数据，上述卷积核为一维或者多维卷积核。并且，信号的维度与卷积核的维度一致。
第二方面，本申请实施例提供了一种干扰消除装置，应用于包括具有信号接收功能的第一类通道和第二类通道的电子设备，包括：采集模块，用于从第一类通道中采集混合有有效信号和第一干扰信号的测量信号，并从第二类通道中采集第二干扰信号；估计模块，用于根据第一校准数据和第二校准数据之间的耦合关系，并基于采集得到的第二干扰信号，估计出测量信号中的第一干扰信号；去除模块，用于从测量信号中去除第一干扰信号得到目标有效信号；其中，第一校准数据和第二校准数据为电子设备处于预设状态时从第一类通道和第二类通道分别采集到的干扰信号。例如，上述采集模块、估计模块和去除模块可以通过电子设备中具有这些模块或单元功能的处理器实现。
在上述第二方面的一种可能的实现中，上述耦合关系用于表示干扰信号在第一类通道中和第二类通道之间的频域相关性，且耦合关系在频域上连续且平滑。
在上述第二方面的一种可能的实现中，上述装置还包括：确定模块，用于根据公式
Figure PCTCN2022088036-appb-000005
以及第一校准数据和第二校准数据得到系数c i,j，系数c i,j用于表示耦合关系，且系数c i,j为时不变的卷积核系数；其中，卷积核的尺寸为2K+1，K为自然数，s r,t为第一校准数据中来自第r个第一类通道的第t个采样数据，s i,j为第二校准数据中来自第i个第二类通道的第j个采样数据，电子设备中包括M个第二类通道和N个第一类通道，i依次取值为1到M的正整数，r依次取值为1到N的正整数。例如，上述确定可以通过电子设备中具有该模块或单元功能的处理器实现。
在上述第二方面的一种可能的实现中，上述确定模块，具体用于根据公式
Figure PCTCN2022088036-appb-000006
针对第一校准数据中来自第r个第一类通道的每个采样数据分别得到一个以卷积核系数为未知数的方程，并将针对r个第一类通道的所有采样数据对应的方程联立得到一个线性方程组，求解线性方程组得到系数c i,j。
在上述第二方面的一种可能的实现中，上述根据第一校准数据和第二校准数据之间的耦合关系，并基于第二干扰信号，估计出测量信号中的第一干扰信号，包括：根据公式
Figure PCTCN2022088036-appb-000007
以及系数c i,j和第一干扰信号，估计出第二干扰信号；其中，s′ r,t为第二干扰信号中来自第r个第一类通道的第t个采样数据，s′ i,j为第一干扰信号中来自第i个第二类通道的第j个采样数据。
在上述第二方面的一种可能的实现中，上述电子设备为磁共振成像设备，有效信号为磁共振成像信号，干扰信号包括电磁干扰信号和热噪声中的至少一项；第一类通道由一个或多个相控阵线圈实现；第二类通道由一个或多个相控阵线圈，或者贴附于检测对象表面的一个或多个电极实现。
在上述第二方面的一种可能的实现中，上述电子设备为同步脑电-功能磁共振成像设备，有效信号为脑电信号，干扰信号包括磁共振成像设备产生的射频信 号和梯度信号中的至少一项；第一类通道由贴附在检测对象表面的一个或多个电极实现；第二类通道由贴附在检测对象表面的一个或多个电极，或者一个或多个相控阵线圈实现。
在上述第二方面的一种可能的实现中，上述电子设备为包括发射线圈的磁共振成像设备，且预设状态为关闭发射线圈；上述装置还包括：在处于预设状态的情况下，将从第一类通道采集的信号作为第一校准数据，并从第二类通道采集的信号作为第二校准数据；其中，发射线圈发射的射频信号用于激发第一类通道接收有效信号。
在上述第二方面的一种可能的实现中，上述预设状态为第一类通道和第二类通道中的信号被多次采集；上述装置还包括：在处于预设状态的情况下，将第一信号作为第一校准数据，第二信号作为第二校准数据；其中，第一信号为连续两次从第一类通道采集的信号之间的差值，第二信号为第一干扰信号中连续两次从第二类通道采集的信号之间的差值。
在上述第二方面的一种可能的实现中，上述电子设备为包括梯度线圈的磁共振成像设备，且预设状态为处于获取测量信号和第二干扰信号期间的死时间内；在处于预设状态的情况下，使用来自梯度线圈的损毁梯度损毁有效信号，将从第一类通道采集的信号作为第一校准数据，并从第二类通道采集的信号作为第二校准数据；其中，死时间为磁共振成像设备执行磁共振成像时用于等待横向或纵向磁化矢量恢复到原有状态的时间。
在上述第二方面的一种可能的实现中，上述电子设备为包括发射线圈的磁共振成像设备，且预设状态为从第一类通道和第二类通道采集的信号中在频域空间的高频部分信号由电磁干扰主导；上述装置还包括：将测量信号中在频域空间的高频部分信号作为第一校准数据，将第二干扰信号中在频域空间的高频部分信号作为第二校准数据。
在上述第二方面的一种可能的实现中，上述有效信号和干扰信号均为一维或者多维数据，上述卷积核为一维或者多维卷积核。并且，信号的维度与卷积核的维度一致。
第三方面，本申请实施例提供了一种计算机可读存储介质，该存储介质上存储有指令，该指令在计算机上执行时使该计算机执行上述第一方面中的干扰消除方法。
第四方面，本申请实施例提供了一种电子设备，包括：一个或多个处理器；一个或多个存储器；该一个或多个存储器存储有一个或多个程序，当该一个或者多个程序被该一个或多个处理器执行时，使得该电子设备执行上述第一方面中的干扰消除方法。
附图说明
图1根据本申请的一些实施例，示出了一种磁共振成像设备的结构示意图；
图2根据本申请的一些实施例，示出了一种干扰消除方法的流程示意图；
图3根据本申请的一些实施例，示出了一种卷积核的示意图；
图4根据本申请的一些实施例，示出了一种磁共振成像设备的计算机的框图；
图5根据本申请的一些实施例，示出了一种手机的框图。
具体实施方式
本申请的说明性实施例包括但不限于干扰消除方法、介质及设备。
本申请实施例提供的干扰消除方法，可以应用于磁共振成像(Magnetic Resonance Imaging，MRI)、同步脑电功能磁共振成像以及语音信号处理等场景中，但不限于此。具体地，电子设备可以包括具有信号接收功能的多个通道，以从多个通道的测量信号中消除干扰信号，从而得到不受干扰信号影响的有效信号，如前述应用中的磁共振成像信号、脑电信号、语音信号等。
作为一种示例，在磁共振成像场景中，有效信号可以为磁共振成像信号，而干扰信号可以为热噪声或者环境中的电磁干扰信号(ElectromagneticInterference，EMI)等。此时，电子设备可以为具有磁共振成像功能的设备，本文中将其称为磁共振成像设备。
作为另一种示例，在同步脑电功能磁共振成像场景中，有效信号可以为脑电信号，而干扰信号可以包括电子设备运行过程产生的磁共振成像射频信号和梯度信号等。此时，上述电子设备可以为具有同步脑电功能磁共振成像的设备，本文中可以将其称为脑电成像设备。
作为又一种示例，在语音信号处理场景中，有效信号可以为待处理语音信号，而干扰信号可以为环境噪音等。此时，上述电子设备可以为具有语音处理功能，如安装有语音助手软件的电子设备。作为一种示例，该场景下的电子设备可以包括但不限于：手机、智能音箱、平板电脑、笔记本电脑、台式电脑、超级移动个人计算机(ultra-mobile personal computer，UMPC)、上网本，以及蜂窝电话、个人数字助理(personal digital assistant，PDA)、增强现实(augmentedreality，AR)、虚拟现实(virtual reality，VR)设备等。
以下实施例中主要以磁共振成像场景中磁共振成像设备执行干扰消除方法为例，对本申请实施例提供的干扰消除方法进行说明。类似的，本文中对于其他应用场景中电子设备执行干扰消除方法的实施细节将不做一一赘述，一些描述可以参照对磁共振成像设备执行消干扰方法的相关描述。
磁共振成像技术可以在医疗或临床应用场景中生成医学影像，以进行疾病诊断。具体地，磁共振成像技术可以利用原子核在强磁场内发生共振产生的信号进行图像重建，对人体等对象作出横断面、矢状面、冠状面和各种斜面的体层图像。
本申请实施中，磁共振成像设备可以为低场、超低场磁共振成像设备，也可以为中场、高场磁共振成像设备。作为一种示例，通常可以按磁场强度将临床应用中的磁共振成像系统划分为高场(1T以上)、中场(0.3-1T)、低场(0.1-0.3T)、超低场(0.1T以下)。
可以理解的是，通常磁共振成像设备需要部署在医院或者研究机构的特定的 房间或区域内，以实现严格的电磁屏蔽，为成本较高且结构较为复杂的大型设备，受限于使用场地而无法作为通用成像设备。而不限定部署的场地，例如不限于在医院或者研究机构中使用，为可移动且成本较低的小型磁共振成像设备将极大地扩展磁共振成像的应用场景。
更具体地，本申请实施例主要应用于低场或超低场磁共振成像设备，在磁共振成像过程中消除环境电磁干扰信号等干扰信号，进而消除磁共振成像中存在的伪影，提高磁共振成像的质量，实现在未屏蔽或部分屏蔽的环境中正常运行低场磁共振成像设备。这样一来，由于磁共振成像设备不需要严格的电磁屏蔽，即不需要将磁共振成像设备放置于屏蔽间内，从而无需专门搭建屏蔽间，安装简便，可以极大地降低成本。并且，可以极大地扩展磁共振成像的应用场景，例如可以应用于床旁磁共振成像(Point-Of-Care MRI，POC MRI)，急诊室(ICU)或者医疗车和救护车等场景。
根据本申请的一些实施例，可以使用一个或者多个磁共振并行成像中常用的多通道线圈(如相控阵线圈)，或者一个或者多个可以贴于人体皮肤表面的电极来接收信号。从功能上，可以将上述线圈或者电极划分为两类。一类线圈，称为接收线圈(receiving coil)，用于接收磁共振信号(具体为磁共振成像信号)，而应避免接收到环境中的电磁干扰信号或者热噪声等干扰信号。具体地，在实际应用过程中，由于低场磁共振成像设备缺少电磁屏蔽，因此接收线圈不可避免地会受到电磁干扰的影响，即接收线圈也会接收到一些电磁干扰信号等。而另一线圈，称为感应线圈(sensing coil)，用于感应环境电磁干扰信号，这一功能也可以用电极来实现。
下面将结合附图对本申请的实施例作进一步地详细描述。
如图1所示，为本申请实施例提供的一种磁共振成像设备可能的结构示意图。该磁共振成像设备100可以包括：计算机101、谱仪102、梯度放大器103、梯度线圈104、发射射频放大器105、发射射频线圈(也称为发射线圈)106、接收射频线圈107、接收射频放大器(也称为接收线圈)108、磁体109、感应线圈101和接收射频放大器110。
具体地，计算机101用于在操作人员的控制下向谱仪102发出指令，以触发谱仪102根据该指令生成梯度信号的波形和射频信号的波形。谱仪102生成的梯度信号经过梯度放大器103进行放大以后，由梯度线圈104形成磁场的梯度，从而实现针对磁共振信号(具体为磁共振成像信号)的空间梯度编码。具体地，空间梯度编码用于对磁共振信号进行空间定位，即区分磁共振信号的来源的位置。而谱仪102生成的射频信号经发射射频放大器105进行放大，由发射射频线圈106发射，从而激发成像区域内的质子(氢原子核)。其中，被激发的质子可以发出射频信号，该射频信号可以被接收线圈108接收到，并经过接收射频放大器107放大以后，再由谱仪102转化为数字信号，进而传送到计算机101进行处理获得图像并显示。此外，磁体109可以是能够生成主磁场的任何合适类型的磁体。而感应线圈101用于感应环境中的电磁干扰信号，并经过接收射频放大器110 放大后，再由谱仪102转化为数字信号并传送到计算机101进行处理。
在一些实施例中，在设计接收线圈和感应线圈时，都需要尽可能提高线圈所能提供的信噪比。即，对于接收线圈而言，应能够尽量灵敏地接收磁共振信号(具体为磁共振成像信号)，而尽可能少地受电磁干扰及热噪声的影响。对于感应线圈而言，应能够尽量灵敏地感知环境电磁干扰，而尽可能少地接收到磁共振信号，以及也尽可能少地受热噪声的影响。
此外，在一些实施例中，上述两类线圈都需要尽可能地减少热噪声的影响，例如，在实际应用中，可以通过一些冷却装置使用冷却的方式最大程度地减小线圈电阻，从而减少热噪声的影响。可以理解的是，本申请实施例对冷却装置不进行具体描述，可以参照相关技术中任意可实现的方式。
类似的，本申请实施例中的脑电成像设备也可以包括图1示出的发射线圈106和接收线圈108，用于基于相同的流程产生磁共振成像射频信号；还可以包括梯度线圈104，用于产生梯度信号。
在一些实施例中，上述接收线圈和感应线圈可以使用单个或多个广泛应用于现代医学磁共振成像中的相控阵线圈来实现。此外，扫描对象为人体，上述感应线圈还可以替换为贴于人体皮肤表面的电极，该电极可以用于感应人体所接收到的电磁干扰信号，从而用于消除接收线圈的测量信号中的电磁干扰信号。
可以理解的是，本申请实施例中，磁共振成像设备100涉及的具有信号接收功能的多个通道可以包括单个相控阵线圈的多个通道，也可以包括多个线圈的多个通道，本申请对此不作具体限定。此外，本申请实施例中，对磁共振成像设备100中的接收线圈和感应线圈的设计、布局(部署位置、部署方向等)不做具体限定，可以为任意可实现的方案。
更具体地，本申请的一些实施例中，针对磁共振成像设备100，接收线圈中的通道可以称为接收线圈通道。其中，接收线圈的通道的数量越多，将有利于提高接收线圈接收得到磁共振信号的信噪比(signal-to-noiseratio，SNR)，或者使得接收线圈可以提供并行成像的能力。在本申请实施例中，多个通道的接收线圈还可以用于增强其对电磁干扰信号的识别与消除能力。感应线圈中的通道可以称为感应线圈通道。其中，感应线圈的通道的数目越多，越能够准确刻画出电磁干扰信号的特征，从而准确通过感应线圈接收的到电磁干扰信号估计出接收线圈所接收到的电磁干扰信号。
例如，图1示出的磁共振成像设备100可以提供一个接收线圈和一个感应线圈，且接收线圈具有一个通道，而感应线圈具有两个通道，但不限于此。此时，磁共振成像设备100提供的多个通道包括接收线圈通道和感应线圈通道。
类似的，在同步脑电功能磁共振成像场景中，脑电成像设备提供的具有信号接收功能的多个通道可以由贴附于头皮的电极实现。以及，在语音信号处理场景中，电子设备提供的多个通道可以为多个麦克风提供的多个模拟信号通道。
本申请实施例中，图1示出的磁共振成像设备100，可以从接收线圈通道和感应线圈通道中采集测量信号，并从这些通道中获取校准数据。进而，可以根据 校准数据，采用卷积运算的方式估计出实际采集的测量信号中的电磁干扰信号，以实现电磁干扰消除。
其中，校准数据中仅包括来自磁共振成像设备100的接收线圈通道和感应线圈通道的电磁干扰信号。即上述校准数据为较为纯粹的电磁干扰信号，从而可以用来估计被不同通道接收到的电磁干扰信号之间的耦合关系。
在一些实施例中，校准数据为磁共振成像设备100在处于预设状态时从接收线圈通道和感应线圈通道采集得到电磁干扰信号。
本申请的一些实施例中，磁共振成像设备100可以通过以下方式(1)至(4)获取校准数据：
(1)预扫描(pre-scan)方式：
磁共振成像设备100在关闭发射线圈(即上述发射射频线圈106)的情况下，获取来自接收线圈通道和感应线圈通道中的测量信号，并将这些测量信号作为校准数据。其中，发射线圈发射的射频信号用于激发成像对象中的原子核(比如氢原子核)，被激发的原子核则会发出磁共振成像信号，进而被接收线圈通道接收到。如果关闭发射线圈，那么接收线圈所接收的测量信号则不包含磁共振成像信号，完全由电磁干扰及热噪声组成。具体地，磁共振成像设备100可以在采集磁共振成像信号之前或之后，关闭发射射频线圈(则接收射频线圈不会接收到磁共振成像信号)，以采集上述校准数据。但是，这一方式有两大缺陷，一是会延长磁共振成像设备100的总扫描时间；而且，如果环境中的电磁干扰信号发生改变，或者由于被扫描对象(如人体)的运动使得信号在各通道之间的耦合关系发生改变，则将导致校准数据无法用于准确估计正式磁共振成像扫描时电磁干扰信号在各通道之间的耦合关系。此时，上述预设状态为磁共振成像设备100在关闭的发射线圈106。
需要说明的是，电磁干扰信号在磁共振成像设备100的多个通道之间的耦合关系，具体为电磁干扰信号在多个通道之间的频域相关性，该耦合关系在频域上连续且平滑。可以理解的是，电磁干扰信号在多个通道之间的频域相关性，可以表示为各个通道接收的电磁干扰信号在不同频点上的线性关系。
具体地，上述耦合关系可以通过频域相关的耦合函数表示，且该耦合函数在频域上连续且平滑。作为一种示例，本申请实施例中，在磁共振成像设备100的多个通道包括接收线圈通道和感应线圈通道的情况下，可以通过校准数据中包含的感应线圈通道所感应到的电磁干扰信号c sen，以及接收线圈通道所接收的电磁干扰信号c rec，估计出上述耦合函数F，使得F(c sen)＝c rec。随后，在磁共振成像设备100正式从接收线圈通道采集信号时，可以由感应线圈通道所感应到的电磁干扰信号s sen和耦合函数F估计出接收线圈通道所接收到的电磁干扰信号s rec，使得s rec＝F(c sen)。
(2)多次采集求差值方式：
在磁共振成像设备100的多个通道中的信号被多次采集的情况下，将连续两次(或者更多次)从多个通道采集的信号之间的差值作为校准数据。具体地，磁共振成像设备100，将连续两次从接收线圈通道采集的信号之间的差值作为校准 数据的一部分，并将该连续两次从接收线圈通道采集的信号之间的差值作为校准数据的另一部分。
可以理解的是，低场磁共振成像设备可以多次采集磁共振信号以实现磁共振成像。具体地，对于磁共振成像设备多次采集的信号，可以认为相近两次采集的磁共振信号理论上是不变的，而电磁干扰信号则是随机变化的；通过对相近两次采集相减，可以保留电磁干扰信号作为校准数据，而最大程度地消去磁共振信号。
然而，如果存在磁场漂移(进而导致相位发生改变)，或者被扫描对象(或称检测对象)运动，或者是采用相位循环(phasecycling)的快速自旋回波(fast spin echo,FSE)成像中自由感应衰减(freeinduction decay，FID)信号的存在，这些都将导致多次扫描获得的磁共振信号无法被最大程度地消去，从而影响上述耦合关系的估计。
(3)内置扫描(intra-scan)方式：
磁共振成像设备100在从多个通道实际采集信号期间的死时间(deadtime)内，使用来自梯度线圈的损毁梯度损毁磁共振成像信号，并获取来自多个通道的测量信号，并将测量信号作为校准数据。其中，死时间为磁共振成像设备执行磁共振成像时用于等待横向或纵向磁化矢量恢复到原有状态的时间。具体地，校准数据包括从接收线圈通道采集的测量信号以及从感应线圈通道采集的测量信号。上述预设状态可以为磁共振成像设备100处于采集信号期间的死时间内。
可以理解的是，利用扫描过程中的死时间采集校准数据，这样可以避免上述(1)和(2)中的问题，但是需要对扫描序列进行修改，也会增加采集的数据量，增大后续计算难度。具体来说，对在死时间阶段的数据采集，同样需要打开梯度线圈产生读出梯度。而在正式的数据采集前，则需要对梯度线圈添加毁损梯度(crushergradient)，这样都能够最大限度地减少校准数据中的磁共振成像信号的成分。作为一种示例，对于快速回波成像(fast spin echo,FSE)，可以延长回波链长度(echo train length,ETL)，对于上述时间比较靠后的读出，可以关闭发射射频线圈(即关闭180度重聚射频脉冲)，进而采集得到校准数据。
(4)采用k空间高频部分的方式：
磁共振成像设备100将从多个通道采集的信号中在频域空间的高频部分信号作为校准数据。此时，校准数据包括从接收线圈通道采集的信号以及从感应线圈通道采集的信号。
可以理解的是，频域空间(即k空间)高频部分磁共振成像信号较弱，可以认为这一部分的信号由电磁干扰主导，从而将这一部分数据用作校准数据。
基于上面的描述，下面具体介绍核磁共振成像设备100执行干扰消除方法的主要工作流程。具体地，上述对图1示出的磁共振成像设备100中描述的技术细节在下述方法流程中依然适用，为了避免重复，有些将不再赘述。在一些实施例中，本申请的干扰消除方法的执行主体可以为磁共振成像设备100，具体为该磁共振成像设备100中的计算机101。如图2所示，为本申请提供的一种干扰消除方法流程，可以包括下述步骤201-步骤205：
步骤201：磁共振成像设备100从接收线线圈通道获取校准数据1，并从感应线圈通道获取校准数据2。
可以理解的是，校准数据1和校准数据2的整体作为磁共振成像设备100从多个通道获取的校准数据。
步骤202：磁共振成像设备100从接收线线圈通道获取测量信号，并从感应线圈通道获取电磁干扰信号1。
可以理解的是，上述测量信号和电磁干扰信号1的整体作为磁共振成像设备100从多个通道实际采集的信号。
在一些实施例中，对于低场(或超低场)磁共振成像设备100，上述测量信号和电磁干扰信号1为从多个通道多次采集得到的。
步骤203：磁共振成像设备100根据公式
Figure PCTCN2022088036-appb-000008
(即公式(1))以及校准数据1和校准数据2得到系数c i,j，且系数c i,j为时不变的卷积核系数。
其中，系数c i,j用于表示电磁干扰信号在接收线圈通道和感应线圈通道之间的耦合关系。
其中，系数c i,j对应的卷积核的尺寸为2K+1，即卷积核的尺寸为奇数，K为自然数，s r,t为校准数据1中来自第r个接收线圈通道的第t个采样数据，s i,j为校准数据2中来自第i个感应线圈通道的第j个采样数据，磁共振成像设备100中包括M个感应线圈通道和N个接收线圈通道，i依次取值为1到M的正整数，r依次取值为1到N的正整数。其中，卷积核的尺寸(也称大小)可以用于表示卷积核所对应的矩阵的行数和列数的乘积。
例如，如图3所示，为本申请提供的一种卷积核的示意图，图3中示出的通道1-通道M均为感应线圈提供的感应线圈通道，而通道r为接收线圈提供的接收线圈通道。具体地，卷积核的大小为2K+1，则卷积核为(2K+1)×M的矩阵。假设M＝3，K＝2，则卷积核的矩阵大小为5×3。此外，通道1-通道M中对应一个卷积核的采样数据与通道r中的第t个采样数据相对应。
在一些实施例中，磁共振成像设备100根据公式
Figure PCTCN2022088036-appb-000009
针对校准数据1中来自第r个接收线圈通道的每个采样数据分别得到一个以卷积核系数为未知数的方程，并将针对第r个接收线圈通道的所有采样数据对应的方程联立得到一个线性方程组，求解该线性方程组得到系数c i,j。
步骤204：磁共振成像设备100根据公式
Figure PCTCN2022088036-appb-000010
(即公式(2))以及系数c i,j和电磁干扰信号1，估计出测量信号中的电磁干扰信号2。
其中，s′ r,t为电磁干扰信号2中来自第r个接收线圈通道的第t个采样数据，s′ i,j为电磁干扰信号1中来自第i个感应线圈通道的第j个采样数据。
可以理解的是，由于电磁干扰信号2和电磁干扰信号1在各个通道之间耦合关系，与校准数据1和校准数据2在各个通道之间耦合关系是一致的。因此，公式(1)和公式(2)中具有相同的系数c i,j。
步骤205：磁共振成像设备100从测量信号去除电磁干扰信号2，得到磁共振成像信号。
如此，本申请实施例中，磁共振成像设备100可以由校准数据获取获取卷积 核，并基于卷积核由感应线圈所测量的电磁干扰信号估计出接收线圈中的电磁干扰信号，并将其消去，以消除电磁干扰信号对磁共振成像信号的影响，进而提高磁共振成像的质量。
类似的，对于本申请实施例应用的其他场景，电子设备也可以按照与上述步骤201-205相似的步骤实施干扰消除方法，区别在于，执行主体不同，多个通道的来源不同，以及有效信号和干扰信号的类型不同。
此外，在其他一些实施例中，有效信号和干扰信号还可以为一维数据或者多维数据(如二维数据)。此时，干扰消除方法中所使用的卷积核可以为一维或多维卷积核，即信号的维数与卷积核的维数一致，其他过程与上述步骤201-步骤205中的相关描述类似，不再赘述。
现在参考图4，所示为根据本申请的一个实施例的磁共振成像设备100中的计算机的框图。图4示意性地示出了根据多个实施例的示例计算机1400。在一个实施例中，系统1400可以包括一个或多个处理器1404，与处理器1404中的至少一个连接的系统控制逻辑1408，与系统控制逻辑1408连接的系统内存1412，与系统控制逻辑1408连接的非易失性存储器(NVM)1416，以及与系统控制逻辑1408连接的网络接口1420。
在一些实施例中，处理器1404可以包括一个或多个单核或多核处理器。在一些实施例中，处理器1404可以包括通用处理器和专用处理器(例如，图形处理器，应用处理器，基带处理器等)的任意组合。在计算机1400采用eNB(Evolved Node B，增强型基站)101或RAN(Radio Access Network，无线接入网)控制器102的实施例中，处理器1404可以被配置为执行各种符合的实施例，例如，如图2所示的多个实施例中的一个或多个。例如，处理器1404可以对来自多个通道的校准数据，基于卷积运算估计出实际测量信号中的干扰信号，进而去除测量信号中的干扰信号得到最终的有效信号。
在一些实施例中，系统控制逻辑1408可以包括任意合适的接口控制器，以向处理器1404中的至少一个和/或与系统控制逻辑1408通信的任意合适的设备或组件提供任意合适的接口。
在一些实施例中，系统控制逻辑1408可以包括一个或多个存储器控制器，以提供连接到系统内存1412的接口。系统内存1412可以用于加载以及存储数据和/或指令。在一些实施例中系统1400的内存1412可以包括任意合适的易失性存储器，例如合适的动态随机存取存储器(DRAM)。
NVM/存储器1416可以包括用于存储数据和/或指令的一个或多个有形的、非暂时性的计算机可读介质。在一些实施例中，NVM/存储器1416可以包括闪存等任意合适的非易失性存储器和/或任意合适的非易失性存储设备，例如HDD(Hard Disk Drive，硬盘驱动器)，CD(Compact Disc，光盘)驱动器，DVD(Digital Versatile Disc，数字通用光盘)驱动器中的至少一个。
NVM/存储器1416可以包括安装系统1400的装置上的一部分存储资源，或者它可以由设备访问，但不一定是设备的一部分。例如，可以经由网络接口1420 通过网络访问NVM/存储1416。
特别地，系统内存1412和NVM/存储器1416可以分别包括：指令1424的暂时副本和永久副本。指令1424可以包括：由处理器1404中的至少一个执行时导致计算机1400实施如图2所示的方法的指令。在一些实施例中，指令1424、硬件、固件和/或其软件组件可另外地/替代地置于系统控制逻辑1408，网络接口1420和/或处理器1404中。
网络接口1420可以包括收发器，用于为系统1400提供无线电接口，进而通过一个或多个网络与任意其他合适的设备(如前端模块，天线等)进行通信。在一些实施例中，网络接口1420可以集成于系统1400的其他组件。例如，网络接口1420可以集成于处理器1404的，系统内存1412，NVM/存储器1416，和具有指令的固件设备(未示出)中的至少一种，当处理器1404中的至少一个执行所述指令时，计算机1400实现如图2所示的方法。
网络接口1420可以进一步包括任意合适的硬件和/或固件，以提供多输入多输出无线电接口。例如，网络接口1420可以是网络适配器，无线网络适配器，电话调制解调器和/或无线调制解调器。
在一个实施例中，处理器1404中的至少一个可以与用于系统控制逻辑1408的一个或多个控制器的逻辑封装在一起，以形成系统封装(SiP)。在一个实施例中，处理器1404中的至少一个可以与用于系统控制逻辑1408的一个或多个控制器的逻辑集成在同一管芯上，以形成片上系统(SoC)。
计算机1400可以进一步包括：输入/输出(I/O)设备1432。I/O设备1432可以包括用户界面，使得用户能够与系统1400进行交互；外围组件接口的设计使得外围组件也能够与计算机1400交互。在一些实施例中，计算机1400还包括传感器，用于确定与计算机1400相关的环境条件和位置信息的至少一种。
在一些实施例中，用户界面可包括但不限于显示器(例如，液晶显示器，触摸屏显示器等)，扬声器，麦克风，一个或多个相机(例如，静止图像照相机和/或摄像机)，手电筒(例如，发光二极管闪光灯)和键盘。
在一些实施例中，外围组件接口可以包括但不限于非易失性存储器端口、音频插孔和电源接口。
在一些实施例中，传感器可包括但不限于陀螺仪传感器，加速度计，近程传感器，环境光线传感器和定位单元。定位单元还可以是网络接口1420的一部分或与网络接口1420交互，以与定位网络的组件(例如，全球定位系统(GPS)卫星)进行通信。
类似的，对于本申请实施例应用的语音处理场景，在一些实施例中，以本申请执行干扰消除的电子设备为手机为例进行说明，描述电子设备的结构。
如图5所示，手机10可以包括处理器110、电源模块140、存储器180，移动通信模块130、无线通信模块120、传感器模块190、音频模块150、摄像头170、接口模块160、按键101以及显示屏102等。
可以理解的是，本发明实施例示意的结构并不构成对手机10的具体限定。 在本申请另一些实施例中，手机10可以包括比图示更多或更少的部件，或者组合某些部件，或者拆分某些部件，或者不同的部件布置。图示的部件可以以硬件，软件或软件和硬件的组合实现。
处理器110可以包括一个或多个处理单元。处理器110中可以设置存储单元，用于存储指令和数据。在一些实施例中，处理器110中的存储单元为高速缓冲存储器180。例如，处理器110可以对来自多个通道的校准数据，基于卷积运算估计出实际测量信号中的干扰信号，进而去除测量信号中的干扰信号得到最终的有效信号。
电源模块140可以包括电源、电源管理部件等。电源可以为电池。电源管理部件用于管理电源的充电和电源向其他模块的供电。
移动通信模块130可以包括但不限于天线、功率放大器、滤波器、LNA(Low noise amplify，低噪声放大器)等。
无线通信模块120可以包括天线，并经由天线实现对电磁波的收发。手机10可以通过无线通信技术与网络以及其他设备进行通信。
在一些实施例中，手机10的移动通信模块130和无线通信模块120也可以位于同一模块中。
显示屏102用于显示人机交互界面、图像、视频等，例如，用于显示处理器110处理得到的有效信号对应的语音表示语义信息。显示屏102包括显示面板。
传感器模块190可以包括接近光传感器、压力传感器，陀螺仪传感器，气压传感器，磁传感器，加速度传感器，距离传感器，指纹传感器，温度传感器，触摸传感器，环境光传感器，骨传导传感器等。
音频模块150用于将数字音频信息转换成模拟音频信号输出，或者将模拟音频输入转换为数字音频信号。音频模块150还可以用于对音频信号编码和解码。在一些实施例中，音频模块150可以设置于处理器110中，或将音频模块150的部分功能模块设置于处理器110中。在一些实施例中，音频模块150可以包括扬声器、听筒、麦克风以及耳机接口。例如，麦克风可以用于提供多个通道，用于获取校准数据或者采集测量信号。
在一些实施例中，手机10还包括按键101、马达以及指示器等。其中，按键101可以包括音量键、开/关机键等。
本申请公开的机制的各实施例可以被实现在硬件、软件、固件或这些实现方法的组合中。本申请的实施例可实现为在可编程系统上执行的计算机程序或程序代码，该可编程系统包括至少一个处理器、存储系统(包括易失性和非易失性存储器和/或存储元件)、至少一个输入设备以及至少一个输出设备。
可将程序代码应用于输入指令，以执行本申请描述的各功能并生成输出信息。可以按已知方式将输出信息应用于一个或多个输出设备。为了本申请的目的，处理系统包括具有诸如例如数字信号处理器(DSP)、微控制器、专用集成电路(ASIC)或微处理器之类的处理器的任何系统。
程序代码可以用高级程序化语言或面向对象的编程语言来实现，以便与处理 系统通信。在需要时，也可用汇编语言或机器语言来实现程序代码。事实上，本申请中描述的机制不限于任何特定编程语言的范围。在任一情形下，该语言可以是编译语言或解释语言。
在一些情况下，所公开的实施例可以以硬件、固件、软件或其任何组合来实现。所公开的实施例还可以被实现为由一个或多个暂时或非暂时性机器可读(例如，计算机可读)存储介质承载或存储在其上的指令，其可以由一个或多个处理器读取和执行。例如，指令可以通过网络或通过其他计算机可读介质分发。因此，机器可读介质可以包括用于以机器(例如，计算机)可读的形式存储或传输信息的任何机制，包括但不限于，软盘、光盘、光碟、只读存储器(CD-ROMs)、磁光盘、只读存储器(ROM)、随机存取存储器(RAM)、可擦除可编程只读存储器(EPROM)、电可擦除可编程只读存储器(EEPROM)、磁卡或光卡、闪存、或用于利用因特网以电、光、声或其他形式的传播信号来传输信息(例如，载波、红外信号数字信号等)的有形的机器可读存储器。因此，机器可读介质包括适合于以机器(例如，计算机)可读的形式存储或传输电子指令或信息的任何类型的机器可读介质。
在附图中，可以以特定布置和/或顺序示出一些结构或方法特征。然而，应该理解，可能不需要这样的特定布置和/或排序。而是，在一些实施例中，这些特征可以以不同于说明性附图中所示的方式和/或顺序来布置。另外，在特定图中包括结构或方法特征并不意味着暗示在所有实施例中都需要这样的特征，并且在一些实施例中，可以不包括这些特征或者可以与其他特征组合。
需要说明的是，本申请各设备实施例中提到的各单元/模块都是逻辑单元/模块，在物理上，一个逻辑单元/模块可以是一个物理单元/模块，也可以是一个物理单元/模块的一部分，还可以以多个物理单元/模块的组合实现，这些逻辑单元/模块本身的物理实现方式并不是最重要的，这些逻辑单元/模块所实现的功能的组合才是解决本申请所提出的技术问题的关键。此外，为了突出本申请的创新部分，本申请上述各设备实施例并没有将与解决本申请所提出的技术问题关系不太密切的单元/模块引入，这并不表明上述设备实施例并不存在其它的单元/模块。
需要说明的是，在本专利的示例和说明书中，诸如第一和第二等之类的关系术语仅仅用来将一个实体或者操作与另一个实体或操作区分开来，而不一定要求或者暗示这些实体或操作之间存在任何这种实际的关系或者顺序。而且，术语“包括”、“包含”或者其任何其他变体意在涵盖非排他性的包含，从而使得包括一系列要素的过程、方法、物品或者设备不仅包括那些要素，而且还包括没有明确列出的其他要素，或者是还包括为这种过程、方法、物品或者设备所固有的要素。在没有更多限制的情况下，由语句“包括一个”限定的要素，并不排除在包括所述要素的过程、方法、物品或者设备中还存在另外的相同要素。
虽然通过参照本申请的某些优选实施例，已经对本申请进行了图示和描述，但本领域的普通技术人员应该明白，可以在形式上和细节上对其作各种改变，而不偏离本申请的精神和范围。

Claims (14)

  1. 一种干扰消除方法，应用于包括具有信号接收功能的第一类通道和第二类通道的电子设备，其特征在于，包括：
    从所述第一类通道中采集混合有有效信号和第一干扰信号的测量信号，并从所述第二类通道中采集第二干扰信号；
    根据第一校准数据和第二校准数据之间的耦合关系，并基于所述第二干扰信号，估计出所述测量信号中的所述第一干扰信号；
    从所述测量信号中去除所述第一干扰信号得到目标有效信号；
    其中，所述第一校准数据和第二校准数据为所述电子设备处于预设状态时从所述第一类通道和所述第二类通道分别采集到的干扰信号。
  2. 根据权利要求1所述的方法，其特征在于，所述耦合关系用于表示干扰信号在所述第一类通道中和所述第二类通道之间的频域相关性，且所述耦合关系在频域上连续且平滑。
  3. 根据权利要求1或2所述的方法，其特征在于，所述方法还包括：
    根据公式
    Figure PCTCN2022088036-appb-100001
    以及所述第一校准数据和所述第二校准数据得到系数c i,j，所述系数c i,j用于表示所述耦合关系，且所述系数c i,j为时不变的卷积核系数；
    其中，所述卷积核的尺寸为2K+1，K为自然数，s r,t为所述第一校准数据中来自第r个所述第一类通道的第t个采样数据，s i,j为所述第二校准数据中来自第i个所述第二类通道的第j个采样数据，所述电子设备中包括M个所述第二类通道和N个所述第一类通道，i依次取值为1到M的正整数，r依次取值为1到N的正整数。
  4. 根据权利要求3所述的方法，其特征在于，所述根据公式
    Figure PCTCN2022088036-appb-100002
    Figure PCTCN2022088036-appb-100003
    以及所述第一校准数据和所述第二校准数据得到系数c i,j，包括：
    根据所述公式
    Figure PCTCN2022088036-appb-100004
    针对所述第一校准数据中来自所述r个所述第一类通道的每个采样数据分别得到一个以卷积核系数为未知数的方程，并将针对所述r个所述第一类通道的所有采样数据对应的方程联立得到一个线性方程组，求解所述线性方程组得到所述系数c i,j。
  5. 根据权利要求3或4所述的方法，其特征在于，所述根据第一校准数据和第二校准数据之间的耦合关系，并基于所述第二干扰信号，估计出所述测量信号中的所述第一干扰信号，包括：
    根据公式
    Figure PCTCN2022088036-appb-100005
    以及系数c i,j和所述第一干扰信号，估计出所述第二干扰信号；
    其中，s′ r,t为所述第二干扰信号中来自第r个所述第一类通道的第t个采样数据，s′ i,j为所述第一干扰信号中来自所述第i个所述第二类通道的第j个采样数据。
  6. 根据权利要求1至5中任一项所述的方法，其特征在于，所述电子设备为 磁共振成像设备，所述有效信号为磁共振成像信号，所述干扰信号包括电磁干扰信号和热噪声中的至少一项；
    所述第一类通道由一个或多个相控阵线圈实现；所述第二类通道由一个或多个相控阵线圈，或者贴附于检测对象表面的一个或多个电极实现。
  7. 根据权利要求1至5中任一项所述的方法，其特征在于，所述电子设备为同步脑电-功能磁共振成像设备，所述有效信号为脑电信号，所述干扰信号包括所述磁共振成像设备产生的射频信号和梯度信号中的至少一项；
    所述第一类通道由贴附在检测对象表面的一个或多个电极实现；所述第二类通道由贴附在检测对象表面的一个或多个电极，或者一个或多个相控阵线圈实现。
  8. 根据权利要求1至7中任一项所述的方法，其特征在于，所述电子设备为包括发射线圈的磁共振成像设备，且所述预设状态为关闭所述发射线圈；
    所述方法还包括：
    在处于所述预设状态的情况下，将从所述第一类通道采集的信号作为所述第一校准数据，并从所述第二类通道采集的信号作为所述第二校准数据；
    其中，所述发射线圈发射的射频信号用于激发所述第一类通道接收有效信号。
  9. 根据权利要求1至7中任一项所述的方法，其特征在于，所述预设状态为所述第一类通道和所述第二类通道中的信号被多次采集；
    所述方法还包括：
    在处于所述预设状态的情况下，将第一信号作为所述第一校准数据，第二信号作为所述第二校准数据；
    其中，所述第一信号为连续两次从所述第一类通道采集的信号之间的差值，所述第二信号为所述第一干扰信号中所述连续两次从所述第二类通道采集的信号之间的差值。
  10. 根据权利要求1至7中任一项所述的方法，其特征在于，所述电子设备为包括梯度线圈的磁共振成像设备，且所述预设状态为处于获取所述测量信号和所述第二干扰信号期间的死时间内；
    在处于所述预设状态的情况下，使用来自所述梯度线圈的损毁梯度损毁有效信号，将从所述第一类通道采集的信号作为所述第一校准数据，并从所述第二类通道采集的信号作为所述第二校准数据；
    其中，所述死时间为所述磁共振成像设备执行磁共振成像时用于等待横向或纵向磁化矢量恢复到原有状态的时间。
  11. 根据权利要求1至7中任一项所述的方法，其特征在于，所述电子设备为包括发射线圈的磁共振成像设备，且所述预设状态为从所述第一类通道和所述第二类通道采集的信号中在频域空间的高频部分信号由电磁干扰主导；
    所述方法还包括：
    将所述测量信号中在频域空间的高频部分信号作为所述第一校准数据，将所述第二干扰信号中在频域空间的高频部分信号作为所述第二校准数据。
  12. 根据权利要求3所述的方法，其特征在于，所述测量信号为一维或者多 维数据，所述卷积核为一维或者多维卷积核。
  13. 一种计算机可读存储介质，其特征在于，所述存储介质上存储有指令，所述指令在计算机上执行时使所述计算机执行权利要求1至12中任一项所述的干扰消除方法。
  14. 一种电子设备，其特征在于，包括：一个或多个处理器；一个或多个存储器；所述一个或多个存储器存储有一个或多个程序，当所述一个或者多个程序被所述一个或多个处理器执行时，使得所述电子设备执行权利要求1至12中任一项所述的干扰消除方法。
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