WO2022227618A1 - Procédé d'élimination d'interférence, milieu et dispositif - Google Patents

Procédé d'élimination d'interférence, milieu et dispositif Download PDF

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WO2022227618A1
WO2022227618A1 PCT/CN2021/138949 CN2021138949W WO2022227618A1 WO 2022227618 A1 WO2022227618 A1 WO 2022227618A1 CN 2021138949 W CN2021138949 W CN 2021138949W WO 2022227618 A1 WO2022227618 A1 WO 2022227618A1
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matrix
signal
signals
magnetic resonance
resonance imaging
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PCT/CN2021/138949
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Chinese (zh)
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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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    • 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
    • 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

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 multiple channels with a signal receiving function, including: acquiring measurement signals from multiple channels, and mixing effective signals and interference signals in the measurement signals ; According to the pre-acquired calibration data, the interference signal is removed from the measurement signal based on the null space to obtain the target effective signal; wherein the calibration data is the interference signal collected from multiple channels when the electronic device is in a preset state.
  • 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 above calibration data only includes interference signals, which are relatively pure interference signals. Therefore, the calibration data can be used to remove the interference signal in the measurement signal based on the null space, and finally an effective signal with a high signal-to-noise ratio can be obtained.
  • the above-mentioned measurement signals include mixed magnetic resonance imaging signals and electromagnetic interference signals, and the like.
  • 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 coupling relationship between the multiple channels of the interference signal has a frequency domain correlation, 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. It can be understood that since the above coupling relationship is continuous and smooth in the frequency domain, the coupling relationship in the time domain is reflected as, for a signal in a certain channel, the sampling data of the adjacent time points of the channel can be used, and The current and adjacent time points of other channels are used for linear representation, and the linear coefficients of these linear relationships are time-invariant.
  • the interference signal is removed from the measurement signal based on the null space to obtain the target effective signal, including: using a sliding time window to construct the calibration data as the first Block Hankel matrix Hc; use the sliding time window to construct the data in the measurement signal as the second block Hankel matrix H; according to the first block Hankel matrix Hc, remove the interference signal in the second block Hankel matrix H based on the null space
  • the target effective signal is obtained; wherein, in any one of the first block Hankel matrix Hc and the second block Hankel matrix H: the data in the same column are sampled from multiple channels in the same sliding time window The data in different columns is the data sampled from multiple channels in different sliding time windows.
  • a sliding time window includes at least two sampling time points, and there is a sampling time interval between two adjacent sliding time windows. point. It can be understood that, based on the characteristic that the coupling relationship of the interference signal between multiple channels has a time-invariant linear coefficient in the time domain, it is possible to use a sliding time window to construct the calibration data into the first Hankel matrix, and measure the calibration data as the first Hankel matrix.
  • the data in the signal is constructed as a second block Hankel matrix to process the first Hankel matrix and the second block Hankel matrix based on null space to achieve interference cancellation.
  • j (t-a+1) ⁇ p
  • t is the sampling times of acquiring measurement signals based on multiple channels
  • p is the number of phase encoding lines during data acquisition (or the number of repeated data acquisitions).
  • m is the number of phase encoding lines during data acquisition (or the number of repeated data acquisitions).
  • each channel in the above-mentioned multiple channels is a first-type channel, or, the multiple channels include at least one first-type channel and at least one second-type channel;
  • the first type of channel is used for receiving valid signals and receiving or inducing interference signals
  • the second type of channel is only used for receiving or inducing interference signals.
  • the first type of channel is the receiving coil channel hereinafter
  • the second type of channel is the induction coil channel hereinafter.
  • 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 (hereinafter referred to as receiving coil channels) are implemented
  • the second type of channel is implemented by one or more phased array coils (hereinafter referred to as induction coil channels), or 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 a radio frequency signal initiated by the synchronous EEG-functional magnetic resonance imaging device and at least one of gradient signals
  • the first type of channel is realized by one or more electrodes attached to the surface of the detection object (such as human scalp)
  • the second type of channel is realized by the surface of the detection object (such as human skin)
  • One or more electrodes, or one or more phased array coils 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 Signals collected from multiple class channels are used as calibration data; wherein, the radio frequency signal emitted by the transmitter coil is used to excite multiple channels to receive valid signals, and the preset state is to close the transmitter coil.
  • 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 radio frequency signals, and the receiving coil will not receive the magnetic resonance imaging signal, so the signals in the first type channel and the second type channel are only electromagnetic interference signals at this time. .
  • the preset state is that signals in multiple channels are collected multiple times; the method further includes: in the preset state, The difference between the signals acquired by the channels is used as calibration data.
  • the magnetic resonance signals may be acquired multiple times to improve the signal-to-noise ratio.
  • 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 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 effective signal from the gradient coil is used to destroy the gradient, and the signals collected from multiple channels are used as calibration data; wherein, the dead time is used for waiting for the transverse or longitudinal magnetization vector when the magnetic resonance imaging device performs magnetic resonance imaging. The time to restore to the original state.
  • the above-mentioned electronic device is a magnetic resonance imaging device including a transmitting coil, and the preset state is a high frequency domain space (ie k-space) of signals collected from multiple channels The frequency part signal is dominated by electromagnetic interference; the above method further includes: taking the high frequency part signal in the frequency domain space in the measurement signal as calibration data.
  • the valid signal and the interference signal are both one-dimensional or multi-dimensional data
  • the first block Hankel matrix and the second block Hankel matrix are one-dimensional or multi-dimensional sliding time windows. built. It can be understood that the dimension of the measurement signal is consistent with the dimension of the sliding time window of the constructed first block Hankel matrix.
  • an embodiment of the present application provides an interference cancellation device, which is applied to an electronic device including multiple channels with a signal receiving function, including: an acquisition module for acquiring measurement signals from multiple channels, and mixing the measurement signals with Effective signal and interference signal; the removal module is used to remove the interference signal from the measurement signal obtained by the acquisition module based on the null space according to the pre-acquired calibration data, and obtain the target effective signal; wherein, the calibration data is when the electronic device is in a preset state Interference signals acquired from multiple channels.
  • the above acquisition module and removal module can be implemented by a processor having the functions of these modules or units in the electronic device.
  • the coupling relationship between the interference signals in the multiple channels has a frequency domain correlation, and the coupling relationship is continuous and smooth in the frequency domain.
  • the above-mentioned removal module is specifically configured to use a sliding time window to construct the calibration data into the first block Hankel matrix Hc; Two-block Hankel matrix H; according to the first block Hankel matrix Hc, remove the data corresponding to the interference signal in the second block Hankel matrix H based on the null space to obtain the target effective signal; wherein, in the first block Hankel matrix Hc and any one of the second block Hankel matrix H: the data in the same column is the data sampled from multiple channels in the same sliding time window, and the data in different columns is sampled from multiple channels in different sliding time windows Data, a sliding time window includes at least two sampling time points, and a sampling time point is separated between two adjacent sliding time windows.
  • each of the above-mentioned multiple channels is a first-type channel, or, the multiple channels include at least one first-type channel and at least one second-type channel; Among them, the first type of channel is used for receiving valid signals and receiving or inducing interference signals, and the second type of channel is only used for receiving or inducing interference signals.
  • 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 synchronous EEG-functional magnetic resonance imaging device
  • the effective signal is an EEG signal
  • the interference signal includes a radio frequency signal initiated by the synchronous EEG-functional magnetic resonance imaging device and at least one of gradient signals
  • 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 A phased array coil is implemented.
  • 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 Signals collected from multiple class channels are used as calibration data; wherein, the radio frequency signal emitted by the transmitter coil is used to excite multiple channels to receive valid signals, and the preset state is to close the transmitter coil.
  • the preset state is that signals in multiple channels are collected multiple times; the device further includes: in the preset state, The difference between the signals acquired by the channels is used as calibration data.
  • 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 effective signal from the gradient coil is used to destroy the gradient, and the signals collected from multiple channels are used as calibration data; wherein, the dead time is used for waiting for the transverse or longitudinal magnetization vector when the magnetic resonance imaging device performs magnetic resonance imaging. The time to restore to the original state.
  • the above-mentioned electronic device is a magnetic resonance imaging device including a transmitting coil, and the preset state is that the high-frequency part of the signal in the frequency-domain space in the signals collected from multiple channels is determined by electromagnetic The interference dominates; the above-mentioned device further includes: taking the high-frequency part of the signal in the frequency domain space in the measurement signal as calibration data.
  • the valid signal and the interference signal are both one-dimensional or multi-dimensional data
  • the first block Hankel matrix and the second block Hankel matrix are one-dimensional or multi-dimensional sliding time windows. built.
  • an embodiment of the present application provides a computer-readable storage medium, where an instruction is stored on the storage medium, and when the instruction is executed on a computer, the computer executes 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 structural diagram of a magnetic resonance imaging apparatus according to some embodiments of the present application
  • FIG. 3 shows a schematic flowchart of an interference cancellation method according to some embodiments of the present application.
  • FIG. 4 shows a schematic diagram of constructing a block Hankel matrix according to some embodiments of the present application
  • FIG. 5 shows a schematic diagram of a process of performing singular value decomposition of a block Hankel matrix according to some embodiments of the present application
  • Fig. 6 shows a block diagram of a computer of a magnetic resonance imaging apparatus according to some embodiments of the present application
  • FIG. 7 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 synchronized EEG-functional magnetic resonance imaging, which may be referred to as an EEG 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 ie, magnetic resonance imaging equipment
  • in clinical applications can be generally divided into high-field (above 1T), mid-field (0.3-1T), and low-field (0.1-0.3T) according to the strength of the magnetic field. ), ultra-low field (below 0.1T).
  • 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 surface of human skin may 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 called receive coil) 108 and magnet 109.
  • 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.
  • FIG. 2 shows a schematic diagram of another possible magnetic resonance imaging apparatus 100 . Comparing FIG. 2 with FIG. 1 , the difference is that an induction coil 111 and a corresponding receiving RF amplifier 110 are newly added to the magnetic resonance imaging apparatus 100 shown in FIG. 2 , and other components are the same as those shown in FIG. 1 .
  • the induction coil 111 is used for sensing the electromagnetic interference signal in the environment, and after being amplified by the receiving RF 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. interfere with the 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 greater the number of channels of the receiving coil the better the signal-to-noise ratio (SNR) of the magnetic resonance signal received by the receiving coil, or the ability of the receiving coil to provide parallel imaging.
  • 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 the receiving coil has multiple channels, or provide multiple receiving coils and each receiving coil channel has one or more channels, but not limited thereto .
  • the multiple channels provided by the magnetic resonance imaging apparatus 100 are all receiving coil channels.
  • the magnetic resonance imaging apparatus 100 shown in FIG. 2 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 electromagnetic interference signal has a coupling relationship between multiple channels of the magnetic resonance imaging apparatus 100 , and the coupling relationship is specifically the frequency domain correlation of the electromagnetic interference signal between the multiple channels, and the coupling relationship is in the frequency domain. continuous and 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 coupling relationship in the time domain is reflected as: the signal for a certain channel can be sampled by the adjacent time points of the channel; and other The sampling of the current and adjacent time points of the channel is used for linear representation, and the linear coefficients of these linear relationships are time-invariant.
  • measurement signals may be acquired from multiple receiving coil channels, and calibration signals may be acquired from the multiple receiving coil channels.
  • measurement signals may be acquired from the receiver coil channel and the induction coil channel, and calibration signals may be acquired from these channels.
  • the calibration data and the actual measurement signal can be respectively constructed into a matrix, and then the two matrices can be processed by operating on the null space. processing to achieve EMI cancellation.
  • the calibration data only includes electromagnetic interference signals from multiple channels 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 multiple receiving coil channels when the magnetic resonance imaging apparatus 100 in FIG. 1 is in a preset state, or the magnetic resonance imaging apparatus 100 in FIG. 2 is in a preset state.
  • the electromagnetic interference signal is collected from the receiving coil channel and the induction coil channel.
  • the magnetic resonance imaging apparatus 100 may acquire calibration signals 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 a plurality of channels 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 the electromagnetic interference signal among the multiple channels may be the linear relationship of the electromagnetic interference signal received by each channel at different frequency points.
  • the above-mentioned 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 difference between the two consecutively acquired signals from the receiving coil channel is used as part of the calibration data, and the difference between the two consecutively acquired signals from the receiving coil channel The difference is used 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 acquired from the receiving coil channel and measurement signals acquired from the induction coil channel.
  • the above-mentioned preset state may be a state in which 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 signals acquired from the receiving coil channel and signals acquired 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 a method for eliminating electromagnetic interference provided by the present application may include the following steps 301 to 309:
  • Step 301 The magnetic resonance imaging apparatus 100 acquires calibration data from multiple channels.
  • the above-mentioned multiple channels are all receiving coil channels.
  • the above-mentioned multiple channels include a receiving coil channel and an induction coil channel.
  • Step 302 The magnetic resonance imaging apparatus 100 receives measurement signals from a plurality of channels, where the measurement signals include mixed magnetic resonance imaging signals and electromagnetic interference signals.
  • the above-mentioned measurement signals are acquired from multiple channels multiple times.
  • the magnetic resonance imaging signal in the above measurement signals comes from the receiving coil channel, and the electromagnetic interference signal comes from the receiving coil and/or the induction coil.
  • Step 303 The magnetic resonance imaging apparatus 100 constructs the calibration data into a first block Hankel matrix Hc using a sliding time window.
  • any one of the first block Hankel matrix Hc and the second block Hankel matrix H the data in the same column is the data sampled from multiple channels in the same sliding time window, and the data in different columns are different
  • one sliding time window includes at least two sampling time points, and two adjacent sliding time windows are separated by one sampling time point.
  • Step 304 the magnetic resonance imaging apparatus 100 constructs the data in the measurement signal into a second block Hankel matrix H using a sliding time window.
  • the vector of data sampled from multiple channels in a sliding time window in the above measurement signal is used as a column of data in the first block Hankel matrix, and the measurement signal is obtained by sampling in different sliding time windows.
  • the vector of is corresponding to the data of different columns in the first block Hankel matrix, one sliding time window includes at least two sampling time points, and two adjacent sliding time windows are separated by one sampling time point.
  • the calibration data can be constructed as the first calibration data using the sliding time window in the above-mentioned manner.
  • the matrix Hc is the first block Hankel matrix, and the rank of the matrix Hc is r.
  • the matrix Hc is of order k ⁇ j
  • the matrix Uc is of order k ⁇ n
  • the matrix Sc is a diagonal matrix of order n ⁇ n
  • the matrix Vc is the source signal matrix corresponding to the electromagnetic interference signal and is of order n ⁇ j
  • the matrix Vc * is the conjugate transposed matrix of the matrix Vc and is of order j ⁇ n
  • each column of the matrix Vc is a component of a signal source corresponding to the electromagnetic interference signal
  • k m ⁇ a
  • m is the above-mentioned magnetic resonance imaging device
  • the number of multiple channels in , a is the number of data sampled in one channel in a sliding time window, and j is the total number of sliding time windows.
  • j (t-a+1) ⁇ p
  • t is the sampling times of acquiring measurement signals based on multiple channels
  • p is the number of phase encoding lines during data acquisition (or the number of repeated data acquisitions).
  • m is the number of phase encoding lines during data acquisition (or the number of repeated data acquisitions).
  • Figure 4 shows an example graph for building a block Hankel matrix.
  • 4 shows the data acquired by the magnetic resonance imaging apparatus 100 based on multiple channels.
  • the block Hankel matrix is the above-mentioned first block Hankel matrix Hc.
  • the block Hankel matrix is the above-mentioned second block Hankel matrix H.
  • a dotted box shown in FIG. 4 is a sliding time window, each sliding time window includes 3 sampling time points, and a circle in the sliding time window represents a piece of data sampled from a channel.
  • the N channels are the multiple channels in the magnetic resonance imaging apparatus 100, and the data sampled in each channel are sorted in the order of sampling time.
  • channel 1 to channel N-1 are all induction coil channels
  • channel N is a receiving coil channel
  • N may be 3.
  • the magnetic resonance imaging apparatus 100 may also perform step 304 first and then perform step 305, which is not limited in this application.
  • the matrix H is of order k ⁇ j
  • the matrix U is of order k ⁇ n.
  • the matrix U includes the column space of order k ⁇ r and the left null space of order k ⁇ (jr), and the matrix Vc * includes the row space of order r ⁇ n and the null space of order (kr) ⁇ j.
  • FIG. 5 shows a schematic diagram of the process of performing singular value decomposition of a block Hankel matrix
  • FIG. 5 includes a block matrix H of order k ⁇ j order (such as the above-mentioned first block Hankel matrix Hc or second block
  • the Hankel matrix H) is a schematic diagram of the position and order of the column space and left null space in the matrix U obtained after Singular Value Decomposition (SVD), and the row space and null space in the matrix Vc * .
  • Step 307 The magnetic resonance imaging apparatus 100 sets the row space of the matrix Vc to 0 to obtain the matrix Vc'.
  • setting the row space of the matrix Vc to 0 can be regarded as setting the component corresponding to the electromagnetic interference signal to 0, that is, eliminating the electromagnetic interference signal.
  • the components included in the matrix H' are all components corresponding to the magnetic resonance imaging signals, that is, the matrix H' only includes data corresponding to the magnetic resonance imaging signals.
  • Step 309 The magnetic resonance imaging apparatus 100 transforms the matrix H' into the frequency domain space to obtain the target magnetic resonance imaging signal.
  • the above-mentioned frequency domain space may be k-space, wherein the magnetic resonance imaging process directly collects data in k-space. It can be understood that, by transforming the matrix H' into k-space, the target magnetic resonance imaging signals from the receiving coil channels in the above-mentioned multiple channels can be obtained.
  • the embodiment of the present application can eliminate the electromagnetic interference of the actually collected measurement signals by using the calibration data obtained from multiple channels to obtain the null space based on singular value decomposition, so as to improve the quality of magnetic resonance imaging.
  • the interference cancellation has a wide range of adaptability and stability.
  • the electronic device may also implement the interference cancellation method according to steps similar to the above steps 301-309, except that the execution subjects are different, and the types of valid signals and interference signals are different.
  • the effective signal and the interference signal in the measurement signal may be one-dimensional or multi-dimensional (eg, two-dimensional) data.
  • the interference cancellation method can use a one-dimensional or multi-dimensional sliding time window to construct a block Hankel matrix, and the dimension of the signal is consistent with the dimension of the sliding time window.
  • Other processes are similar to the relevant descriptions in the above steps 301-309 ,No longer.
  • FIG. 6 shown is a block diagram of a computer in a magnetic resonance imaging apparatus 100 according to one embodiment of the present application.
  • FIG. 6 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. 3 . For example, the processor 1404 may construct matrices for calibration data and actual measurement signals from multiple channels, perform singular value decomposition on the matrices to obtain a null space, and then remove interference signals in the measurement signals to obtain a 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 can 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.
  • 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 computer 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. 3 .
  • 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.
  • the system 1400 also includes sensors for determining at least one of environmental conditions and location information associated with the 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
  • keyboard e.g, a keyboard
  • the user interface described above may be used to display imaging images of a magnetic resonance imaging procedure or the like.
  • 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 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 construct matrices for calibration data and actual measurement signals from multiple channels, perform singular value decomposition on the matrix to obtain a null space, and then remove interference signals in the measurement signals to obtain a 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

Procédé d'élimination d'interférence, milieu et dispositif, qui se rapportent au domaine du traitement de signaux, et peut éliminer des signaux d'interférence à partir de signaux de mesure reçus sur la base de multiples canaux pour obtenir des signaux efficaces, de manière à éviter l'influence des signaux d'interférence sur les signaux efficaces. Le procédé consiste à : acquérir des signaux de mesure à partir de multiples canaux, des signaux efficaces et des signaux d'interférence étant mélangés dans les signaux de mesure ; selon des données d'étalonnage pré-acquises ; et éliminer les signaux d'interférence des signaux de mesure sur la base d'un espace nul pour obtenir un signal efficace cible, les données d'étalonnage étant les signaux d'interférence collectés à partir des multiples canaux lorsqu'un dispositif électronique est dans un état prédéfini. Le procédé d'élimination d'interférence peut être utilisé dans un scénario dans lequel l'influence de signaux d'interférence électromagnétique sur des signaux d'imagerie par résonance magnétique est éliminée.
PCT/CN2021/138949 2021-04-29 2021-12-16 Procédé d'élimination d'interférence, milieu et dispositif WO2022227618A1 (fr)

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CN113203969B (zh) * 2021-04-29 2022-08-16 杭州微影医疗科技有限公司 干扰消除方法、介质及设备
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CN117095073A (zh) * 2023-08-23 2023-11-21 浙江大学 一种基于深度学习的医学图像的去噪方法及装置
CN117575936B (zh) * 2023-11-07 2024-07-19 浙江大学 一种基于通道相关性的磁共振图像去噪方法、装置及设备

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030083570A1 (en) * 2001-10-31 2003-05-01 Cho Yong Kyun Alternative sensing method for implantable medical device in magnetic resonance imaging device
WO2017155364A1 (fr) * 2016-03-11 2017-09-14 성균관대학교산학협력단 Dispositif imageur à résonance magnétique et procédé de traitement d'imagerie à résonance magnétique l'utilisant
CN111386470A (zh) * 2017-10-05 2020-07-07 西门子医疗有限公司 具有主动干扰抑制的磁共振断层成像设备以及磁共振断层成像设备中的干扰抑制方法
CN111839514A (zh) * 2019-04-26 2020-10-30 西门子(深圳)磁共振有限公司 呼吸导航中的干扰校正方法和装置以及存储介质
CN112305478A (zh) * 2019-07-25 2021-02-02 西门子医疗有限公司 用于在噪声抑制中考虑磁共振信号的方法和设备
CN112415452A (zh) * 2019-08-22 2021-02-26 西门子(深圳)磁共振有限公司 去除信号中干扰的方法和装置、磁共振系统和存储介质
CN113203969A (zh) * 2021-04-29 2021-08-03 杭州微影医疗科技有限公司 干扰消除方法、介质及设备

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN103856306B (zh) * 2012-12-05 2017-10-17 华为技术有限公司 处理干扰的方法及装置
CN106559117B (zh) * 2015-09-28 2020-07-28 联芯科技有限公司 K用户系统及其干扰消除方法
CN105680995B (zh) * 2016-02-23 2019-03-15 北京邮电大学 一种信号传输方法、装置及系统
CA3055749A1 (fr) * 2017-03-08 2018-09-13 Saudi Arabian Oil Company Systeme et procedes automatises de debruitage robuste adaptatif d'ensembles de donnees sismiques a grande echelle
US10823805B2 (en) * 2017-09-21 2020-11-03 Centre National De La Recherche Scientifique (Cnrs) Method and magnetic resonance apparatus for image reconstruction with trimmed autocalibrating k-space estimation based on structured matrix completion

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030083570A1 (en) * 2001-10-31 2003-05-01 Cho Yong Kyun Alternative sensing method for implantable medical device in magnetic resonance imaging device
WO2017155364A1 (fr) * 2016-03-11 2017-09-14 성균관대학교산학협력단 Dispositif imageur à résonance magnétique et procédé de traitement d'imagerie à résonance magnétique l'utilisant
CN111386470A (zh) * 2017-10-05 2020-07-07 西门子医疗有限公司 具有主动干扰抑制的磁共振断层成像设备以及磁共振断层成像设备中的干扰抑制方法
CN111839514A (zh) * 2019-04-26 2020-10-30 西门子(深圳)磁共振有限公司 呼吸导航中的干扰校正方法和装置以及存储介质
CN112305478A (zh) * 2019-07-25 2021-02-02 西门子医疗有限公司 用于在噪声抑制中考虑磁共振信号的方法和设备
CN112415452A (zh) * 2019-08-22 2021-02-26 西门子(深圳)磁共振有限公司 去除信号中干扰的方法和装置、磁共振系统和存储介质
CN113203969A (zh) * 2021-04-29 2021-08-03 杭州微影医疗科技有限公司 干扰消除方法、介质及设备

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