WO2021169339A1 - 信号测量方法及装置 - Google Patents

信号测量方法及装置 Download PDF

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Publication number
WO2021169339A1
WO2021169339A1 PCT/CN2020/123695 CN2020123695W WO2021169339A1 WO 2021169339 A1 WO2021169339 A1 WO 2021169339A1 CN 2020123695 W CN2020123695 W CN 2020123695W WO 2021169339 A1 WO2021169339 A1 WO 2021169339A1
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signal
lead
electrode
mode
threshold
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PCT/CN2020/123695
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English (en)
French (fr)
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刘翔宇
杨斌
张�杰
陈宜欣
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华为技术有限公司
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Priority to US17/802,764 priority Critical patent/US20230084533A1/en
Priority to EP20921112.7A priority patent/EP4091548A4/en
Priority to JP2022551723A priority patent/JP7551763B2/ja
Publication of WO2021169339A1 publication Critical patent/WO2021169339A1/zh

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    • 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
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/251—Means for maintaining electrode contact with the body
    • A61B5/256—Wearable electrodes, e.g. having straps or bands
    • 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
    • A61B5/30—Input circuits therefor
    • A61B5/305—Common mode rejection
    • 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
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/271—Arrangements of electrodes with cords, cables or leads, e.g. single leads or patient cord assemblies
    • A61B5/273—Connection of cords, cables or leads to electrodes
    • 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
    • A61B5/30—Input circuits therefor
    • A61B5/307—Input circuits therefor specially adapted for particular uses
    • A61B5/308—Input circuits therefor specially adapted for particular uses for electrocardiography [ECG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A61B5/6803—Head-worn items, e.g. helmets, masks, headphones or goggles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
    • A61B5/721—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts using a separate sensor to detect motion or using motion information derived from signals other than the physiological signal to be measured
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7221—Determining signal validity, reliability or quality
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7225—Details of analog processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6814—Head
    • A61B5/6815—Ear
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6822—Neck

Definitions

  • This application relates to the field of medical electronics technology, and in particular to a signal measurement method and device.
  • cardiovascular diseases The prevalence of cardiovascular diseases in my country is on a continuous rise, and the death rate of cardiovascular diseases ranks first, higher than that of tumors and other diseases.
  • Electrocardiography is the most common detection method in cardiology, and it is the best method for measuring and diagnosing cardiovascular diseases.
  • the medical standard 12-lead electrocardiograph is large in size and limited in testing places, so it is not suitable for families or individuals.
  • wearable devices such as ECG watches or bracelets have been introduced.
  • the I-lead ECG can be measured.
  • the specific measurement method is to make the 1 or 2 electrodes arranged on the back of the watch (band) contact the skin of the wrist by wearing, while the fingers of the other hand actively touch the remaining electrode to form the I lead measurement.
  • the measurement requires the coordination of the left and right hands, and it is difficult to realize real-time measurement; and only a single-lead measurement can be formed between the left and right hands.
  • Another solution is to set up 2-3 electrodes on the earphone to realize real-time ECG measurement while wearing the earphone.
  • the current schemes for setting electrodes on the earphones for ECG measurement are currently single-lead schemes, and less information is obtained.
  • the present application provides a signal measurement method and device to improve the quality of the measured signal.
  • a signal measurement method which is applied to a signal measurement device, the method includes: turning on a multi-lead measurement mode, acquiring a multi-lead signal and a user's status; extracting characteristics of the multi-lead signal, And according to the characteristics of the multi-lead signal, the quality of the multi-lead signal is obtained; if the quality of the multi-lead signal is greater than the first threshold, or when the user is in a static state, output the extracted multi-lead signal.
  • the characteristics of the lead signal if the quality of the multi-lead signal is less than or equal to the first threshold and the user is in motion, switch to the single-lead mode with right leg drive to obtain the single-lead signal ; Eliminate the common mode signal in the single-lead signal; extract and output the characteristics of the eliminated single-lead signal.
  • the automatic switching between the multi-lead ECG measurement mode of the three-electrode ECG system and the single-lead ECG measurement mode with the right leg drive electrode is realized.
  • the quality of the multi-lead signal is better. When it is high, output the features of the extracted multi-lead signal or eliminate the common mode signal in the single-lead signal before extracting and outputting the features of the eliminated single-lead signal, thereby obtaining a higher quality ECG Signal, to achieve accurate measurement of the user's ECG signal.
  • the signal measurement device includes a left ear electrode, a right ear electrode, a neck electrode, a preamplifier corresponding to the three electrodes, a Wilson network circuit, a common mode generating circuit, a mode selection switch, and a processor.
  • the left ear electrode is connected to the left ear measurement component
  • the right ear electrode is connected to the right ear measurement component
  • the mode selection switch is connected to the neck measurement component
  • the common mode generating circuit includes a right leg drive electrode and a common mode amplifier
  • the left ear electrode, the right ear electrode, and the neck electrode are respectively connected to the positive electrode of the corresponding preamplifier and the Wilson network circuit, and the central electrical terminal of the Wilson network circuit is respectively connected to the negative electrode of the preamplifier of the three electrodes
  • the preamplifiers corresponding to the three electrodes are connected to the processor; the central electrical terminal of the Wilson network circuit is also connected to the negative electrode of the common mode amplifier;
  • the enabling of the multi-lead measurement mode includes: The mode selection switch is controlled to be connected to the neck electrode to turn on the multi-lead measurement mode.
  • the circuit of the signal measurement device is simple to implement, and the measurement mode is convenient to switch.
  • the acquiring a multi-lead signal includes: measuring the signal between the left ear electrode and the right ear electrode to obtain a lead I signal; measuring the right ear electrode and the neck The signal between the electrodes is used to obtain the lead II signal; the signal between the left ear electrode and the neck electrode is measured to obtain the lead III signal; and based on the lead I signal, the lead II signal and all According to the signal of lead III, lead aVR signal, aVL lead signal and avF lead signal are obtained.
  • six-lead signals can be obtained through three measuring electrodes and Wilson network.
  • User measurement operation is simple.
  • the extracting the characteristics of the multi-lead signal includes: obtaining the average value of the multi-lead signal; and according to the signal of each lead in the multi-lead signal and the The average value of the multi-lead signal is obtained, and the correlation coefficient corresponding to the signal of each lead is obtained as the characteristic of the signal of each lead.
  • the correlation coefficient corresponding to the lead signal can accurately represent the characteristics of the lead signal.
  • the method further includes: obtaining the average value of the correlation coefficient corresponding to the multi-lead signal according to the correlation coefficient corresponding to the signal of each lead, as the quality of the multi-lead signal If the average value of the correlation coefficient corresponding to the multi-lead signal is greater than the first threshold, or the acceleration signal is less than or equal to the second threshold, then the step of extracting the features of the multi-lead signal is performed; And if the average value of the correlation coefficient corresponding to the multi-lead signal is less than or equal to the first threshold, and the acceleration signal is greater than or equal to the third threshold, the switch to the single-lead drive with right leg is performed Steps of the pattern.
  • the measured multi-lead signal is unstable and cannot be output as a measurement result. Therefore, by switching to the single-lead measurement mode with right-leg drive, the common-mode signal of the single-lead signal can be eliminated through the negative feedback of the right-leg drive electrode, so that a better quality single-lead signal can be obtained.
  • the method further includes: screening signals with signals greater than a fourth threshold in the multi-lead signals; and extracting features of the filtered signals.
  • signals with better signal quality can be screened from the multi-lead signals as needed, and then the features of the screened signals can be extracted, thereby improving the quality of the output result.
  • the method includes: if the multi-lead signal is less than or equal to the first threshold value and the user is in an exercise state, controlling the mode selection switch to switch to the right leg driving electrode to turn on the single-lead mode; the acquisition
  • the single-lead signal includes: acquiring the single-lead signal according to the signals of the left ear electrode, the right ear electrode and the central electrical terminal; and removing the common mode signal in the single-lead signal , Including: obtaining the common mode signal of the user through the negative feedback of the right leg drive electrode according to the signal of the central electrical terminal and the reference level signal; eliminating the common mode signal in the single-lead signal.
  • the measured multi-lead signal is unstable and cannot be output as a measurement result. Therefore, by switching to the single-lead measurement mode with right-leg drive, the common-mode signal of the single-lead signal can be eliminated through the negative feedback of the right-leg drive electrode, so that a better quality single-lead signal can be obtained.
  • the acquiring the user's status includes: acquiring an acceleration signal; if the acceleration signal is less than or equal to the second threshold, determining that the user is at a static state; and if the acceleration signal is greater than or It is equal to the third threshold, and it is determined that the user is in an exercise state.
  • the state of the user has a greater impact on the measurement of the signal. Therefore, through the judgment of the acceleration signal, an accurate user state can be obtained.
  • a signal measurement device in a second aspect, includes: a mode selection switch for turning on a multi-lead measurement mode; a signal acquisition module for acquiring a multi-lead signal and user status; a feature extraction module, It is used to extract the characteristics of the multi-lead signal; a signal quality acquisition module is used to acquire the quality of the multi-lead signal according to the characteristics of the multi-lead signal; an output module is used to When the signal is greater than the first threshold, or when the user is in a static state, output the extracted characteristics of the multi-lead signal; the mode selection switch is also used for if the multi-lead signal is less than or equal to the first Threshold value, and when the user is in motion, switch to the single-lead mode with right leg drive; the signal acquisition module is also used to acquire single-lead signals; the common-mode signal cancellation module is used to eliminate the single-lead The common mode signal in the lead signal; the feature extraction module is also used to extract
  • the signal acquisition module includes a left ear electrode, a right ear electrode, a neck electrode, a preamplifier corresponding to the three electrodes, a Wilson network circuit, and a processor
  • the common mode signal cancellation module includes The right leg drive electrode and the common mode amplifier; wherein the left ear electrode is connected to the left ear measurement part, the right ear electrode is connected to the right ear measurement part, and the mode selection switch is connected to the neck measurement part; the left ear electrode , The right ear electrode, and the neck electrode are respectively connected to the positive pole of the corresponding preamplifier and the Wilson network circuit, the central electrical terminal of the Wilson network circuit is respectively connected to the negative pole of the three electrode preamplifier, the three electrodes
  • the corresponding preamplifiers are connected to the processor; the central electrical terminal of the Wilson network circuit is also connected to the negative electrode of the common mode amplifier; and the module selection switch is used to connect to the neck electrode to Turn on the multi-lead measurement mode.
  • the signal acquisition module is used to: measure the signal between the left ear electrode and the right ear electrode to obtain a lead I signal; measure the difference between the right ear electrode and the neck electrode To obtain the lead II signal; measure the signal between the left ear electrode and the neck electrode to obtain the lead III signal; and obtain the lead III signal according to the lead I signal, the II lead signal and the III Lead signal, get aVR lead signal, aVL lead signal and avF lead signal.
  • the feature extraction module is configured to obtain the average value of the multi-lead signal; and according to the signal of each lead in the multi-lead signal and the value of the multi-lead signal The average value is obtained, and the correlation coefficient corresponding to the signal of each lead is obtained as the characteristic of the signal of each lead.
  • the signal quality acquisition module is configured to acquire the average value of the correlation coefficient corresponding to the multi-lead signal according to the correlation coefficient corresponding to the signal of each lead, as a multi-lead signal The quality of the signal; the output module is configured to output the multi-lead signal if the average value of the correlation coefficient corresponding to the multi-lead signal is greater than the first threshold, or the acceleration signal is less than the second threshold And the mode selection switch is used to if the average value of the correlation coefficient corresponding to the multi-lead signal is less than or equal to the first threshold, and the acceleration signal is greater than or equal to the second threshold, Then switch to single-lead mode with right leg drive.
  • the device further includes: a signal screening module, which is used to screen the multi-lead signals whose signals are greater than a fourth threshold; the feature extraction module, which is used to extract the screened signals The characteristics of the signal.
  • the mode selection switch is used to switch to the right leg drive electrode if the multi-lead signal is less than or equal to the first threshold and the user is in an exercise state, and switch on the single Lead mode;
  • the signal acquisition module is configured to acquire the single-lead signal according to the signals of the left ear electrode, the right ear electrode and the central electrical terminal;
  • the common mode signal cancellation module is used According to the signal of the central electrical terminal and the reference level signal, through the negative feedback of the right leg drive electrode, the common mode signal of the user is obtained, and the common mode signal in the single-lead signal is eliminated.
  • the signal acquisition module is further configured to acquire an acceleration signal; the device further includes: a determination module configured to determine that the user is in a static state if the acceleration signal is less than or equal to a second threshold; And the determining module is further configured to determine that the user is in a motion state if the acceleration signal is greater than or equal to a third threshold.
  • a signal measurement device including an input device, an output device, a memory, and a processor.
  • the memory stores program instructions
  • the processor is configured to call the program instructions to perform the following operations:
  • the output device is controlled to output the extracted features of the multi-lead signal; if the quality of the multi-lead signal is less than or equal to The first threshold and when the user is in an exercise state, switch to the single-lead mode with right leg drive to obtain a single-lead signal; eliminate the common-mode signal in the single-lead signal; extract the signal The features of the processed single-lead signal are eliminated, and the output device is controlled to output the extracted features of the single-lead signal.
  • the processor is further configured to perform the following operations: controlling the mode selection switch to be connected to the neck electrode to turn on the multi-lead measurement mode.
  • the processor executes the operation of acquiring multi-lead signals, including: measuring the signal between the left ear electrode and the right ear electrode to obtain a lead I signal; and measuring the right ear electrode.
  • the lead II signal and the III lead signal are used to obtain aVR lead signal, aVL lead signal and avF lead signal.
  • the processor executes the aVR lead signal, aVL lead signal and avF lead signal according to the lead I signal, the lead II signal and the lead III signal.
  • the processor executes the operation of extracting the characteristics of the multi-lead signal, including: obtaining an average value of the multi-lead signal; and according to each of the multi-lead signals The signal of each lead and the average value of the multi-lead signal are obtained, and the correlation coefficient corresponding to the signal of each lead is obtained as the characteristic of the signal of each lead.
  • the processor further performs the following operation: according to the correlation coefficient corresponding to the signal of each lead, obtain the average value of the correlation coefficient corresponding to the multi-lead signal as a multi-lead signal The quality of the signal; if the average value of the correlation coefficient corresponding to the multi-lead signal is greater than the first threshold, or the acceleration signal is less than or equal to the second threshold, then the feature extraction of the multi-lead signal is performed And if the average value of the correlation coefficient corresponding to the multi-lead signal is less than or equal to the first threshold value, and the acceleration signal is greater than or equal to the third threshold value, execute the switch to the drive with right leg Single-lead mode operation.
  • the processor further performs the following operations: screening signals with signals greater than a fourth threshold in the multi-lead signals; and extracting features of the screened signals.
  • the processor executes the switch to the single-lead mode with right leg drive if the multi-lead signal is less than or equal to the first threshold and the user is in a motion state
  • the operation of obtaining a single-lead signal includes: if the multi-lead signal is less than or equal to the first threshold and the user is in a motion state, controlling the mode selection switch to switch to the right leg drive electrode, Turn on the single-lead mode;
  • the processor executes the operation of acquiring the single-lead signal, including: acquiring the single-lead signal according to the signals of the left ear electrode, the right ear electrode, and the central electrical terminal
  • the processor performing the operation of eliminating the common mode signal in the single-lead signal includes: according to the signal of the central electrical terminal and the reference level signal, through the negative feedback of the right leg drive electrode, Obtain the user's common mode signal; eliminate the common mode signal in the single-lead signal.
  • the processor performing the operation of acquiring the user's status includes: acquiring an acceleration signal; if the acceleration signal is less than or equal to the second threshold, determining that the user is static; and If the acceleration signal is greater than or equal to the third threshold, it is determined that the user is in a motion state.
  • a computer-readable storage medium stores instructions that, when run on a computer, cause the computer to perform any of the above-mentioned first aspect or any of the first aspects. Implement the described method.
  • a computer program product containing instructions, which when running on a computer, enables the computer to execute the method described in the first aspect or any one of the first aspects described above.
  • FIG. 1 is a schematic structural diagram of a neck-mounted earphone provided by an embodiment of the application
  • FIG. 2 is a schematic structural diagram of a signal measurement device provided by an embodiment of the application.
  • FIG. 3 is a schematic flowchart of a signal measurement method provided by an embodiment of this application.
  • FIG. 5 is a schematic diagram of using the neck-mounted earphone shown in FIG. 1 to measure in a multi-lead measurement mode
  • FIG. 6 is a schematic diagram of the internal circuit structure of the exemplary signal measurement device when it is in a multi-lead measurement mode
  • FIG. 7 is a schematic diagram of the internal circuit structure of the exemplary signal measurement device in the single-lead measurement mode
  • FIG. 8 is a schematic diagram of a scene in which a user uses a signal measuring device to perform measurement
  • FIG. 9 is a schematic structural diagram of another signal measurement device provided by an embodiment of the application.
  • Fig. 1 a schematic diagram of the structure of the neck-mounted earphone provided by the embodiment of the application.
  • the electrode On the neck-mounted earphone, the electrode is arranged in the left ear (LE) machine housing part measuring component 1 (connected to LE electrode), right ear (right ear, RE) machine housing part measuring part 2 (connected with RE electrode) are respectively used to contact the user's left and right ear auricle skin.
  • N measurement component 3 (connected to N electrode) is used as the third electrode in the six-lead solution and the "right leg drive electrode" in the single-lead solution.
  • 4 is a processing circuit, which includes an analog front end (AFE), an accelerometer (ACC), and a micro control unit (MCU), where the AFE includes the foregoing electrodes, an operational amplifier (amplifier) , AMP) and analog-to-digital converter (ADC), etc.
  • AFE analog front end
  • ACC accelerometer
  • MCU micro control unit
  • AFE includes the foregoing electrodes, an operational amplifier (amplifier) , AMP) and analog-to-digital converter (ADC), etc.
  • the neck-mounted earphone can process the measured signal by itself; in another embodiment, the neck-mounted earphone measures the signal of each electrode, and then it can also be sent to the terminal wirelessly connected to the earphone, and the terminal To process.
  • the circuit 4 may also include a communication module, such as a Bluetooth transmission module, and the communication mode of the communication module may be a wireless or wired connection mode.
  • the aforementioned terminal may be a mobile phone, a smart watch, a smart bracelet, a computer, etc.
  • the neck-mounted headset of this embodiment can work in a multi-lead measurement mode and a single-lead measurement mode.
  • the signals measured by the electrodes 1, 2, and 3 can be used to obtain multi-lead signals after processing.
  • the quality of the multi-lead signals is good or the user is relatively static, the characteristics of the multi-lead signals can be extracted; If the quality of the connection signal is poor or the user is in motion, you can switch to the single-lead measurement mode.
  • the neck electrode serves as the right leg driving electrode, and the common mode component of the electrical signal on the surface of the left and right ear electrodes is transmitted to the right leg Drive the electrode, through the negative feedback of the right leg drive, so as to force the human body common mode voltage to approach the reference level, so that the center of all electrode inputs is located in the center of the input range, which can reduce the common mode noise of the system and improve the signal quality of the single-lead signal .
  • the signal measurement device 1000 includes: a mode selection switch 11 for turning on a multi-lead measurement mode; a signal acquisition module 12 for acquiring a multi-lead Signal and user status; feature extraction module 13 for extracting features of the multi-lead signal; signal quality acquiring module 14 for acquiring the quality of the multi-lead signal according to the features of the multi-lead signal
  • the output module 15 is configured to output the extracted characteristics of the multi-lead signal if the quality of the multi-lead signal is greater than the first threshold, or when the user is in a static state; the mode selection switch 11, also If the quality of the multi-lead signal is less than or equal to the first threshold and the user is in a motion state, switch to the single-lead mode with right leg drive; the signal acquisition module 12 also uses To obtain a single-lead signal; a common-mode signal elimination module 16 for eliminating common-mode signals in the single-lead
  • the signal acquisition module 12 includes a left ear electrode, a right ear electrode, a neck electrode, a preamplifier corresponding to the three electrodes, a Wilson network circuit, and a processor
  • the common mode signal cancellation module 16 includes a right leg drive electrode and a common mode amplifier; wherein the left ear electrode is connected to a left ear measurement component, the right ear electrode is connected to a right ear measurement component, and the mode selection switch 11 is connected to a neck measurement component;
  • the left ear electrode, the right ear electrode, and the neck electrode are respectively connected to the positive pole of the corresponding preamplifier and the Wilson network circuit, and the central electrical terminal of the Wilson network circuit is respectively connected to the negative pole of the three electrode preamplifier.
  • the preamplifiers corresponding to the three electrodes are connected to the processor; the central electrical terminal of the Wilson network circuit is also connected to the negative electrode of the common mode amplifier; and the module selection switch 11 is used to connect to the neck Part of the electrode to open the multi-lead measurement mode.
  • the signal acquisition module 12 is used to: measure the signal between the left ear electrode and the right ear electrode to obtain a lead I signal; measure the right ear electrode and the neck electrode To obtain the lead II signal; measure the signal between the left ear electrode and the neck electrode to obtain the lead III signal; and according to the lead I signal, the II lead signal and the III lead signal, get aVR lead signal, aVL lead signal and avF lead signal.
  • the feature extraction module 13 is configured to obtain the average value of the multi-lead signal; and according to the signal of each lead in the multi-lead signal and the multi-lead signal The correlation coefficient corresponding to the signal of each lead is obtained as the characteristic of the signal of each lead.
  • the signal quality obtaining module 14 is configured to obtain the average value of the correlation coefficient corresponding to the multi-lead signal according to the correlation coefficient corresponding to the signal of each lead; the output Module 15 is configured to output the extracted multi-lead signal if the average value of the correlation coefficient corresponding to the multi-lead signal is greater than the first threshold value, or the acceleration signal is less than the second threshold value Features; and the mode selection switch 11 is used to switch if the average value of the correlation coefficient corresponding to the multi-lead signal is less than or equal to the first threshold, and the acceleration signal is greater than or equal to the second threshold To single-lead mode with right leg drive.
  • the device further includes: a signal screening module 18, which is used to screen the multi-lead signals whose signals are greater than a fourth threshold; and the feature extraction module 13 is used to extract the screening signals. The characteristics of the output signal.
  • the mode selection switch 11 is used to switch to the right leg drive electrode if the multi-lead signal is less than or equal to the first threshold and the user is in an exercise state, and turn on Single-lead mode; the signal acquisition module 12 for acquiring the single-lead signal according to the signals of the left ear electrode, the right ear electrode and the central electrical terminal; and the common mode signal cancellation module 16. According to the signal of the central electrical terminal and the reference level signal, through the negative feedback of the right leg drive electrode, the common mode signal of the user is obtained, and the common mode signal in the single-lead signal is eliminated.
  • the signal acquisition module 12 is also used to acquire an acceleration signal; the device further includes: a determination module 17, which is used to determine that the user is Static; and the determining module is further configured to determine that the user is in a motion state if the acceleration signal is greater than or equal to a third threshold.
  • FIG. 3 is a schematic flowchart of a signal measurement method provided by an embodiment of the application, and the method may include:
  • the mode selection switch turns on the multi-lead measurement mode, and the signal acquisition module acquires the multi-lead signal and the state of the user.
  • the signal measurement device includes multiple measurement electrodes (for example, the LE, RE, and N electrodes of the neck-mounted earphone as shown in FIG. 1), and can measure multiple measurement components (LE, RE, and N measurement components). )signal of.
  • the signal measuring device also includes a right leg drive electrode.
  • the right leg drive circuit including the right leg drive electrode is essentially a negative feedback.
  • the function of the right leg drive circuit is to remove the common mode signal in the input amplifier and improve the common mode rejection ratio (CMRR); Reversely amplify the common mode signal to the human body to eliminate the common mode.
  • the driving function of the right leg is mainly to reduce the common mode voltage in the bioelectric acquisition.
  • Right leg drive is a necessary method to reduce common mode drying.
  • One end of the mode selection unit is connected to one of the measurement components (such as the aforementioned N measurement component), and the other end can be connected to a measurement electrode (such as the N electrode), or connected to the right leg drive electrode.
  • a measurement electrode such as the N electrode
  • the signal measuring device starts multi-lead measurement mode; when the other end of the mode selection unit is connected to the right leg drive electrode, the signal measuring device starts single-lead measurement model.
  • the mode selection unit may receive an instruction sent by the terminal or according to the default configuration of the signal measurement device, turn on the multi-lead measurement mode.
  • the instruction sent by the terminal is used to instruct the signal measurement device to turn on the multi-lead measurement mode; or the signal measurement device is configured to turn on the multi-lead measurement mode when it is turned on by default. Further, if the signal measurement device is in the single-lead mode before the multi-lead mode is turned on, it can be switched to the multi-lead measurement mode according to the switching control signal of the mode selection unit.
  • the multi-lead may be six-lead.
  • the signal measuring device can include three measuring electrodes, and the six-lead signal can be obtained through the Wilson network.
  • the feature extraction module extracts features of the multi-lead signal.
  • the obtained multi-lead signal is a relatively complete ECG signal of the user.
  • the electrocardiogram signal can generally be embodied by the electrocardiogram.
  • Each heart cycle cycle in the electrocardiogram consists of a series of regular waveforms, which are P wave, QRS complex wave and T wave, and the start, end, peak, trough, and interval of these waveforms record the heart activity.
  • the detailed information of the state is an important analysis basis for the diagnosis provider of heart disease. Therefore, after acquiring the multi-lead signal, the characteristics of the multi-lead signal can be extracted.
  • the P wave represents the excitement of the atrium
  • the first half represents the excitement of the right atrium
  • the second half represents the excitement of the left atrium
  • the PR interval represents the time required for the excitement generated by the sinoatrial node to reach the ventricle through the atrium, the atrioventricular junction and the atrioventricular bundle and cause the ventricular muscle to start to excite, so it is also called the atrioventricular conduction time.
  • the QRS complex represents the depolarization of the ventricle, and the activation time limit is less than 0.11 seconds.
  • the QRS complex appears to be widened, deformed, and time-frame prolonged.
  • Point J is the intersection between the end of the QRS wave and the beginning of the ST segment. It means that all ventricular myocytes have been completely depolarized. The depolarization of the ventricular muscles is complete, and the repolarization has not yet begun for a period of time. At this time, the ventricular muscles in all parts are in a state of depolarization, and there is no potential difference between the cells. Therefore, the ST segment should be on the equipotential line under normal circumstances.
  • the subsequent T wave represents the repolarization of the ventricle.
  • the T wave In the lead up to the main QRS wave, the T wave should be in the same direction as the main QRS wave.
  • the U wave is related to the repolarization of the ventricle.
  • the QT interval represents the time from depolarization to repolarization of the ventricle.
  • the signal quality acquisition module acquires the quality of the multi-lead signal according to the characteristics of the multi-lead signal.
  • the quality of the acquired multi-lead signal determines whether the characteristics of the multi-lead signal can be used as the measurement result. According to the characteristics of each lead signal, the overall quality of the multi-lead signal can be obtained. For example, based on the average value of the characteristics of each lead signal, the quality of the multi-lead signal can be obtained.
  • the mode selection switch determines whether the quality of the multi-lead signal is greater than the first threshold. If the quality of the multi-lead signal is greater than the first threshold, proceed to step S106; if the quality of the multi-lead signal is less than or equal to the first threshold, Then proceed to step S105.
  • the quality of the multi-lead signal is greater than the first threshold, it indicates that the quality of the multi-lead signal is good, and the multi-lead signal can be used as the measurement result; if the quality of the multi-lead signal is less than or equal to the first threshold, it indicates that the multi-lead signal is less than or equal to the first threshold.
  • the quality of the connected signal is poor, and the multi-lead signal cannot be used as the measurement result, and the mode selection switch needs to switch the mode.
  • the first threshold can be set based on experience.
  • the mode selection switch judges whether the user is in a static state. If the user is in a static state, proceed to step S106; if the user is in an exercise state, proceed to step S107.
  • the measured multi-lead signal is relatively stable, and the multi-lead signal measured in the multi-lead measurement mode can be used as the measurement result; but if the user is in motion, it will cause common mode interference to the measurement. And when the quality of the multi-lead signal is poor, you need to switch to the single-lead measurement mode with right leg drive for measurement.
  • the mode selection switch can first determine whether the quality of the multi-lead signal is greater than the first threshold, and then determine whether the user is static; it can also determine whether the user is static first, Then determine whether the quality of the multi-lead signal is greater than the first threshold; or at the same time determine whether the quality of the multi-lead signal is greater than the first threshold, and whether the user is in a static state.
  • the mode The selector switch is switched to the single-lead mode with right leg drive for measurement.
  • the output module outputs the extracted feature of the multi-lead signal.
  • the extracted features of the multi-lead signal can be output through voice, screen display, etc.
  • the mode selection switch determines that the quality of the multi-lead signal is less than or equal to the first threshold and the user is in an exercise state, then switch to the single-lead mode with right leg drive.
  • the signal acquisition module acquires single-lead signals.
  • the mode selection switch is switched to the single-lead mode with right leg drive.
  • the signal acquisition module acquires single-lead signals. Specifically, the signal acquisition module uses two electrodes other than the measurement electrode connected to the mode selection switch for measurement to obtain a single-lead signal.
  • the common mode signal elimination module eliminates the common mode signal in the single-lead signal.
  • the common mode components of the electrical signals on the two electrode surfaces are transmitted to the right leg drive circuit, and the negative feedback of the right leg drive forces the human body common mode voltage to be close to the reference level, so that the center of all electrode inputs is located in the center of the input range, which can reduce
  • the common mode noise of the system can eliminate the common mode signal in the single-lead signal and improve the signal quality of the system.
  • the feature extraction module extracts the feature of the single-lead signal after the elimination processing.
  • the feature extraction module can extract features of single-lead signals that have been eliminated.
  • the single-lead signal may be filtered.
  • S110 Output the extracted characteristics of the single-lead signal.
  • the characteristics of the extracted single-lead signal can be output through voice, screen display, etc.
  • the automatic switching between the multi-lead ECG measurement mode of the three-electrode ECG system and the single-lead ECG measurement mode with the right leg drive electrode is realized through the judgment of the signal quality and the user's motion state.
  • the quality of the multi-lead signal is high, output the features of the extracted multi-lead signal or eliminate the common mode signal in the single-lead signal before extracting and outputting the features of the eliminated single-lead signal. It can obtain a higher quality ECG signal, and realize the accurate measurement of the user's ECG signal.
  • FIG. 4 is a schematic flowchart of another signal measurement method provided by an embodiment of the application, and the method may include:
  • the mode selection switch is connected to the neck electrode to turn on the multi-lead measurement mode.
  • the signal measuring device may be a neck-mounted earphone as shown in FIG. 1.
  • the mode selection switch is connected to the neck electrode to turn on the multi-lead measurement mode.
  • the mode selection switch is connected to the neck electrode, it is disconnected from the right leg drive electrode.
  • the signal acquisition module measures the signal between the left ear electrode and the right ear electrode to obtain a lead I signal; measures the signal between the right ear electrode and the neck electrode to obtain a lead II signal; and measures the left ear electrode and the neck
  • the signal between the two electrodes is the third lead signal.
  • the signal acquisition module obtains the aVR lead signal, the aVL lead signal and the avF lead signal according to the lead I signal, the lead II signal and the lead III signal.
  • FIG. 5 it is a schematic diagram of measuring in multi-lead measurement mode using the neck-mounted earphone shown in Figure 1.
  • the LE electrode of the left ear, the RE electrode of the right ear and the N electrode of the neck are all connected to the central electrical terminal.
  • the internal circuit diagram of the signal measurement device in the multi-lead measurement mode is exemplified.
  • the circuit structure of the signal measurement is not limited to this.
  • the three electrodes of left ear (LE), right ear (RE), and neck (neck, N) are used to collect the electrocardiographic signals on the skin surface.
  • the electrical signals on the surface of the three electrodes pass through the multiplexer , MUX) circuit and Wilson (Wilson) network to form a six-lead system, and through a two-stage adjustable gain operational amplifier (for example, AD761) for amplification and filtering, after amplification, filtering, analog-to-digital converter (analog-to-digital converter) converter, ADC)
  • the converted signal is transmitted to the MCU.
  • the Wilson network is a resistance network.
  • the three electrodes LE, RE, and N are connected together through three equal resistances to form a central end of the average potential, which is called the Wilson central electrical terminal, the central potential end or the Wilson central
  • the electric terminal, the voltage at the center electric terminal represents the average voltage of the body.
  • the acceleration signal measured by the accelerometer is processed by the ADC and transmitted to the MCU.
  • the MCU processes the signals of the above-mentioned LE, RE, N and the central electrical terminal to obtain a multi-lead signal. Specifically, when the measurement mode is selected and measured, the internal switch of the multiplexer is switched to ECG3, so that the neck (N) electrode is connected to the ECG3 input of the AFE module. At this time, the connection with the right leg drive circuit (RLD) is disconnected, and the right leg drive circuit does not work.
  • the three electrode signals are input to the positive electrode of operational amplifier A, the common-mode voltage of the human body is input to operational amplifier A through the three electrode channels, and the output of operational amplifier A is the Wilson center electrical terminal Vcm.
  • Vcm is input to three ECG preamplifiers (ie ECG1 Preamplifier, ECG2 preamplifier, ECG3 preamplifier) negative pole. Thereby, a six-lead system with three-electrode input can be formed.
  • leads refer to lead I, lead II, lead III, lead aVR, lead aVL and lead avF.
  • Electrode LE and electrode RE form lead I
  • electrode N and electrode RE form lead II
  • electrode N and electrode LE form lead III.
  • Electrode LE and electrode RE form lead I
  • electrode N and electrode RE form lead II
  • electrode N and electrode LE constitutes lead III.
  • the central electrical terminal is input to the negative electrode of the preamplifier of the 3 ECG electrodes to form a six-lead, that is, lead aVR, lead aVL and lead avF can be calculated based on the above-mentioned lead I, lead II and lead III.
  • Lead aVR RE-0.5*(LE+N)
  • lead aVL LE-0.5*(N+RE)
  • lead avF N-0.5*(LE+RE).
  • the feature extraction module obtains the average value of the multi-lead signal.
  • the feature extraction module obtains a correlation coefficient corresponding to the signal of each lead as a feature of the signal of each lead according to the signal of each lead in the multi-lead signal and the average value of the multi-lead signal.
  • the signals of the electrodes LE, RE, and N are input to the MCU.
  • the MCU can obtain the six-lead signals A1 to A6. Further, after the signals of the respective electrodes are acquired, and before being transmitted to the MCU, the signals can be filtered.
  • Feature extraction includes extraction of correlation coefficients such as Pearson correlation coefficient and Spearman correlation coefficient in multi-lead signals.
  • Correlation coefficient is a statistical indicator used to reflect the close degree of correlation between variables.
  • the Pearson correlation coefficient (Pearson correlation coefficient) is used to measure whether the two data sets are on a line, and it is used to measure the linear relationship between the distance variables.
  • the Spearman rank correlation coefficient named after Charles Spearman is the Spearman correlation coefficient. It is often represented by the Greek letter ⁇ . It is a non-parametric indicator that measures the dependence of two variables. It uses a monotonic equation to evaluate the correlation between two statistical variables. If there are no repeated values in the data, and when the two variables are completely monotonously related, the Spearman correlation coefficient is +1 or -1.
  • the six correlation coefficients can be calculated according to the signal of each lead and the average value of the six leads.
  • the average value of the six leads A ( ⁇ A1 ⁇ + ⁇ A2 ⁇ + ⁇ A3 ⁇ + ⁇ A4 ⁇ + ⁇ A5 ⁇ + ⁇ A6 ⁇ )/6
  • the signal quality obtaining module obtains the average value of the correlation coefficient corresponding to the multi-lead signal according to the correlation coefficient corresponding to the signal of each lead, as the quality of the multi-lead signal.
  • the average of the six correlation coefficients Feat1 ( ⁇ 1 ⁇ + ⁇ 2 ⁇ + ⁇ 3 ⁇ + ⁇ 4 ⁇ + ⁇ 5 ⁇ + ⁇ ⁇ 6 ⁇ )/6, it reflects the overall signal quality of the multi-lead signal.
  • the quality of the signal can also be determined based on the multiple lead signals themselves.
  • the signal quality can be a specific signal value.
  • the mode selection switch judges whether the average value of the correlation coefficient corresponding to the multi-lead signal is greater than the first threshold, if yes, proceed to step S209; otherwise, proceed to step S208.
  • the mode selection switch determines whether the quality of the multi-lead signal is greater than the first threshold. Specifically, the mode selection switch determines whether the average value is greater than the first threshold value according to the average value of the correlation coefficients corresponding to the multi-lead signals obtained above.
  • the determining module determines whether the acceleration signal is less than or equal to the second threshold, and if yes, proceed to step S209; otherwise, proceed to step S211.
  • the signal acquisition module can also acquire the acceleration signal.
  • the acceleration signal of the user can be collected by the acceleration sensor. And transmit the acceleration signal to the MCU.
  • the acceleration sensor may specifically be a gravity sensor or the like.
  • the determination module determines that when the acceleration signal is less than or equal to the second threshold, the user is in a static state; when the acceleration signal is greater than or equal to the third threshold, the user is in a motion state.
  • the determination module outputs the judgment result to the mode selection switch.
  • S207 and S208 are in no order.
  • S209 is executed.
  • the signal screening module screens the multi-lead signal whose signal is greater than the fourth threshold.
  • the quality of the multi-lead signal is greater than the first threshold, it means that the overall signal quality of the multi-lead system obtained above is greater than the first threshold, and the overall signal quality is good; or the acceleration signal is less than or equal to the second threshold, it means The user is currently basically in a static state, and the quality of the multi-lead signal obtained by the multi-lead system is better.
  • the required lead signal can be screened as needed. For example, for diseases that require observation of specific leads to be diagnosed, such as coronary heart disease, the required lead signals are screened. For another example, the signal of each lead is compared with the fourth threshold, and the lead signal whose signal is greater than or equal to the fourth threshold is screened out.
  • the filtered lead signal can be filtered.
  • the characteristics of the filtered signal can be output according to the filtered lead signal.
  • the determining module determines whether the acceleration signal is greater than or equal to the third threshold, and if yes, proceed to step S212; otherwise, proceed to step S208.
  • the determination module determines that the acceleration signal is greater than or equal to the third threshold, that is, the user is in a motion state, then output The judgment result is given to the mode switch.
  • the mode switch is switched to the single-lead mode with right leg drive.
  • the mode switch determines that the quality of the multi-lead signal is poor and the user is in an exercise state, it switches to the single-lead mode with right leg drive.
  • the signal acquisition module acquires a single-lead signal according to the signals of the left ear electrode, the right ear electrode and the central electrical terminal.
  • FIG. 7 it is a schematic diagram of the internal circuit structure of the exemplary signal measurement device when it is in the single-lead measurement mode. If the quality of the multi-lead signal is less than or equal to the first threshold, and the acceleration signal is greater than or equal to the second threshold, the internal switch of the multiplexer is switched to RLD, so that the neck (N) electrode is connected to the RLD of the AFE module and disconnected at the same time. Open the connection with the ECG3 of the AFE module, the ECG3 channel of the AFE module does not work.
  • the two electrode signals (LE, RE) are input to the positive electrode of the ECG preamplifier, and the human body common mode voltage (the common mode component of the electrical signals on the two electrode surfaces) is input to the operational amplifier A through the two electrode channels (LE, RE), and the operation is performed
  • the output of the amplifier A gets the Wilson center electric terminal Vm, which is input to the negative pole of the two ECG preamplifiers, and input to the negative pole of the right leg drive circuit operational amplifier B at the same time, and is fed back to the human body through the right leg drive circuit.
  • the positive input of operational amplifier B is 1.3V reference level, and the negative feedback of the right leg drive forces the human body common-mode voltage to approach the reference level, so that the center of all electrode inputs is located in the center of the input range, forming a "right leg drive" Single-lead circuit.
  • the common mode signal in the single-lead signal can be eliminated, and a better-quality single-lead signal can be obtained.
  • the characteristics of the single-lead signal after the elimination process can be extracted.
  • the extraction process refer to steps S204 and S205.
  • the automatic switching between the multi-lead ECG measurement mode of the three-electrode ECG system and the single-lead ECG measurement mode with the right leg drive electrode is realized through the judgment of the signal quality and the user's motion state.
  • the quality of the multi-lead signal is high, output the features of the extracted multi-lead signal or eliminate the common mode signal in the single-lead signal before extracting and outputting the features of the eliminated single-lead signal. It can obtain a higher quality ECG signal, and realize the accurate measurement of the user's ECG signal.
  • FIG 8 it is a schematic diagram of a user using a signal measuring device to perform a measurement.
  • the user wears the above neck-mounted headset, and when the headset is turned on to measure the ECG signal, the headset defaults to enter multi-conductor Joint measurement mode.
  • the acceleration sensor in the headset uses the acceleration sensor in the headset to measure the acceleration signal, and judge that the user is in a relatively static state.
  • the signals measured by the three electrodes of the left ear, right ear, and neck are processed to obtain a multi-lead signal.
  • the characteristics of the multi-lead signal are extracted.
  • the neck electrode serves as the right leg driving electrode, and the common mode component of the electrical signal on the surface of the left and right ear electrodes is transmitted Drive the electrode to the right leg, and through the negative feedback of the right leg drive, the human body common mode voltage is forced to be close to the reference level, so that the center of all electrode inputs is located in the center of the input range, which can reduce the common mode noise of the system and improve the single-lead signal Signal quality.
  • the earphone After the earphone measures the signals of the foregoing electrodes, the earphone can process the foregoing signals to obtain multi-lead signals or single-lead signals, and extract the characteristics of the lead signals. And can output the characteristics of the above-mentioned lead signal through a headphone player. After the earphone measures the signal of the above electrode, it can also transmit the above signal to a terminal that establishes a wireless connection with the earphone, such as a user's mobile phone or other wearable device, and the mobile phone or other wearable device processes the above signal to obtain a multi-lead signal Or single-lead signal, and extract the characteristics of the lead signal, and output it on the mobile phone or other wearable devices. Therefore, the requirements on the calculation capability and signal output capability of the signal measurement device can be reduced.
  • a structural schematic diagram of a signal measurement device is also provided, and the signal measurement device is used to implement the above-mentioned signal measurement method.
  • Part or all of the above methods can be implemented by hardware, and can also be implemented by software or firmware.
  • the signal measuring device may be a chip or an integrated circuit in specific implementation.
  • the signal measuring device 2000 may include:
  • the memory 23 and the processor 24 may be one or more, and one processor is taken as an example in FIG. 9
  • the input device 21, the output device 22, the memory 23, and the processor 24 may be connected by a bus or other methods, wherein the connection by a bus is taken as an example in FIG. 9.
  • the processor 24 is used to execute the method steps executed in FIG. 3 and FIG. 4.
  • the processor 24 is configured to call the program instructions to perform the following operations:
  • the output device is controlled to output the extracted features of the multi-lead signal; if the quality of the multi-lead signal is less than or equal to The first threshold and when the user is in an exercise state, switch to the single-lead mode with right leg drive to obtain a single-lead signal; eliminate the common-mode signal in the single-lead signal; extract the signal The features of the processed single-lead signal are eliminated, and the output device is controlled to output the extracted features of the single-lead signal.
  • the processor 24 is further configured to perform the following operations: controlling the mode selection switch to be connected to the neck electrode to turn on the multi-lead measurement mode.
  • the processor 24 executes the operation of acquiring multi-lead signals, including: measuring the signal between the left ear electrode and the right ear electrode to obtain the lead I signal; and measuring the right ear The signal between the electrode and the neck electrode to obtain a lead II signal; measure the signal between the left ear electrode and the neck electrode to obtain a lead III signal; and according to the lead I signal, the The lead II signal and the III lead signal are obtained by aVR lead signal, aVL lead signal and avF lead signal.
  • the processor 24 executes the aVR lead signal, aVL lead signal, and avF lead signal according to the lead I signal, the lead II signal, and the lead III signal.
  • the processor 24 performs the operation of extracting the characteristics of the multi-lead signal, including: obtaining the average value of the multi-lead signal; and according to each of the multi-lead signals The signal of each lead and the average value of the multi-lead signal are obtained, and the correlation coefficient corresponding to the signal of each lead is obtained as the characteristic of the signal of each lead.
  • the processor 24 also performs the following operations: according to the correlation coefficient corresponding to the signal of each lead, obtain the average value of the correlation coefficient corresponding to the multi-lead signal as a multi-lead signal If the average value of the correlation coefficient corresponding to the multi-lead signal is greater than the first threshold, or the acceleration signal is less than or equal to the second threshold, then perform the extraction of the characteristics of the multi-lead signal Operation; and if the average value of the correlation coefficient corresponding to the multi-lead signal is less than or equal to the first threshold value, and the acceleration signal is greater than or equal to the third threshold value, execute the switch to a single drive with a right leg Operation in lead mode.
  • the processor 24 further performs the following operations: screening the multi-lead signals whose signals are greater than the fourth threshold; and extracting the features of the filtered signals.
  • the processor 24 executes the switch to the single-lead mode with right leg drive if the multi-lead signal is less than or equal to the first threshold and the user is in a motion state
  • the operation of obtaining a single-lead signal includes: if the multi-lead signal is less than or equal to the first threshold and the user is in a motion state, controlling the mode selection switch to switch to the right leg driving electrode, and turning on Single-lead mode;
  • the processor 24 executes the operation of acquiring the single-lead signal, including: acquiring the single-lead signal according to the signals of the left ear electrode, the right ear electrode, and the central electrical terminal; and
  • the processor 24 executes the operation of eliminating the common mode signal in the single-lead signal, including: obtaining the user's information through the negative feedback of the right leg drive electrode according to the signal of the central electrical terminal and the reference level signal.
  • Common mode signal eliminate the common mode signal in the single-lead signal.
  • the processor 24 performs the operation of acquiring the user's status, including: acquiring an acceleration signal; if the acceleration signal is less than or equal to the second threshold, determining that the user is in a static state; and if the acceleration signal is less than or equal to the second threshold; If the acceleration signal is greater than or equal to the third threshold, it is determined that the user is in a motion state.
  • the program of the above-mentioned signal measurement method may be stored in the memory 23.
  • the memory 23 may be a physically independent unit, or may be integrated with the processor 24.
  • the memory 23 can also be used to store data.
  • the signal measurement device may also only include a processor.
  • the memory for storing the program is located outside the signal measuring device, and the processor is connected to the memory through a circuit or wire for reading and executing the program stored in the memory.
  • the processor may be a central processing unit (CPU), a network processor (NP), or a WLAN device.
  • CPU central processing unit
  • NP network processor
  • WLAN device a WLAN device
  • the processor may further include a hardware chip.
  • the above-mentioned hardware chip may be an application-specific integrated circuit (ASIC), a programmable logic device (PLD) or a combination thereof.
  • the above-mentioned PLD may be a complex programmable logic device (CPLD), a field-programmable gate array (FPGA), a generic array logic (GAL), or any combination thereof.
  • the memory may include volatile memory (volatile memory), such as random-access memory (RAM); the memory may also include non-volatile memory (non-volatile memory), such as flash memory (flash memory) , A hard disk drive (HDD) or a solid-state drive (solid-state drive, SSD); the memory may also include a combination of the foregoing types of memory.
  • volatile memory such as random-access memory (RAM)
  • non-volatile memory such as flash memory (flash memory)
  • flash memory flash memory
  • HDD hard disk drive
  • solid-state drive solid-state drive
  • the disclosed system, device, and method can be implemented in other ways.
  • the division of the unit is only a logical function division. In actual implementation, there can be other divisions.
  • multiple units or components can be combined or integrated into another system, or some features can be ignored or not. implement.
  • the displayed or discussed mutual coupling, or direct coupling, or communication connection may be indirect coupling or communication connection through some interfaces, devices or units, and may be in electrical, mechanical, or other forms.
  • the units described as separate components may or may not be physically separated, and the components displayed as units may or may not be physical units, that is, they may be located in one place, or they may be distributed on multiple network units. Some or all of the units may be selected according to actual needs to achieve the objectives of the solutions of the embodiments.
  • the above embodiments it may be implemented in whole or in part by software, hardware, firmware, or any combination thereof.
  • software it can be implemented in the form of a computer program product in whole or in part.
  • the computer program product includes one or more computer instructions.
  • the computer may be a general-purpose computer, a special-purpose computer, a computer network, or other programmable devices.
  • the computer instructions can be stored in a computer-readable storage medium or transmitted through the computer-readable storage medium.
  • the computer instructions can be sent from a website, computer, server, or data center to another via wired (such as coaxial cable, optical fiber, digital subscriber line (DSL)) or wireless (such as infrared, wireless, microwave, etc.) A website, computer, server or data center for transmission.
  • the computer-readable storage medium may be any available medium that can be accessed by a computer or a data storage device such as a server or data center integrated with one or more available media.
  • the usable medium can be read-only memory (ROM), or random access memory (RAM), or magnetic media, such as floppy disks, hard disks, magnetic tapes, magnetic disks, or optical media, for example, Digital versatile disc (DVD), or semiconductor media, for example, solid state disk (SSD), etc.

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Abstract

一种信号测量方法及信号测装置（1000），模式选择开关（11）可以开启多导联测量模式，获取多导联信号及用户的状态，当多导联信号的质量较好时，或者用户处于静态时，则输出提取出的多导联信号的特征；当多导联信号较差，且用户处于运动状态时，模式选择开关（11）切换到带右腿驱动的单导联模式，获取单导联信号，并且通过右腿驱动电极的负反馈，消除单导联信号中的共模信号，输出经消除处理的单导联信号的特征。通过信号质量与用户运动状态的判断，实现多导联测量与带右腿驱动的单导联测量模式之间的自动切换，可输出质量较高的信号，从而实现用户心电信号的准确测量。

Description

信号测量方法及装置
本申请要求于2020年02月29日提交中国国家知识产权局、申请号为202010132725.1、发明名称为“信号测量方法及装置”的中国专利申请的优先权，其全部内容通过引用结合在本申请中。
技术领域
本申请涉及医疗电子技术领域，尤其涉及一种信号测量方法及装置。
背景技术
我国心血管病患病率处于持续上升阶段，心血管病死亡率居首位，高于肿瘤及其他疾病。
心电描记术(electrocardiography，ECG)是心内科最常见的检测手段，是测量和诊断心血管病最好的方法。但医用标准12导联心电图机体积庞大、检测场所受限，不适用于家庭或个人。
目前推出了心电手表或者手环等可穿戴式设备，通过在表体设置3个电极，测量左右手之间的电势，可测量I导联ECG。具体测量方式为通过佩戴使设置在手表(手环)背面的1～2个电极与手腕皮肤接触，同时另一只手的手指主动触摸剩余一个电极，形成I导联的测量。但是测量需要左右手协同，难以实现实时测量；且左右手之间只能形成单导联测量。
还有一种方案是通过在耳机上设置2-3个电极，佩戴耳机时可实现ECG实时测量。但是，当前耳机上设置电极进行ECG测量的方案，目前都为单导联方案，获取的信息较少。
另外，目前也没有关于用户在静态测量心电图信息时进入运动状态，如何保证心电图的信号质量的方案。
有鉴于此，如何提高测量的心电信号的质量，是本申请需要解决的问题。
发明内容
本申请提供一种信号测量方法及装置，以提高测量的信号的质量。
第一方面，提供了一种信号测量方法，应用于信号测量装置，所述方法包括：开启多导联测量模式，获取多导联信号及用户的状态；提取所述多导联信号的特征，并根据所述多导联信号的特征，获取所述多导联信号的质量；若所述多导联信号的质量大于第一阈值，或所述用户处于静态时，输出提取出的所述多导联信号的特征；若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态时，切换到带右腿驱动的单导联模式，获取单导联信号；消除所述单导联信号中的共模信号；提取并输出所述经消除处理的单导联信号的特征。
在该方面中，通过信号质量与用户运动状态的判断，实现三电极ECG系统多导联ECG测量与带右腿驱动电极单导联ECG测量模式之间的自动切换，在多导联信号质量较高时，输出提取的多导联信号的特征，或者消除单导联信号中的共模信号后，才提取并输出经消 除处理的单导联信号的特征，从而可以获取更高质量的心电信号，实现用户心电信号的准确测量。
在一个可能的实现中，所述信号测量装置包括左耳电极、右耳电极、颈部电极、三个电极分别对应的前置放大器、威尔逊网络电路、共模产生电路、模式选择开关和处理器，所述左耳电极连接左耳测量部件，所述右耳电极连接右耳测量部件，以及所述模式选择开关连接颈部测量部件；所述共模产生电路包括右腿驱动电极和共模放大器；所述左耳电极、右耳电极、颈部电极分别连接至对应的前置放大器的正极以及威尔逊网络电路，所述威尔逊网络电路的中心电端分别连接至三个电极的前置放大器的负极，所述三个电极分别对应的前置放大器连接至所述处理器；所述威尔逊网络电路的中心电端还连接至所述共模放大器的负极；所述开启多导联测量模式，包括：控制所述模式选择开关连接至所述颈部电极，以开启多导联测量模式。
在该实现中，该信号测量装置的电路实现简单，测量模式切换方便。
在又一个可能的实现中，所述获取多导联信号，包括：测量所述左耳电极和右耳电极之间的信号，得到Ⅰ导联信号；测量所述右耳电极和所述颈部电极之间的信号，得到Ⅱ导联信号；测量所述左耳电极和颈部电极之间的信号，得到Ⅲ导联信号；以及根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
在该实现中，通过三个测量电极和威尔逊网络，就可以获得六导联的信号。用户测量操作简单。
在又一个可能的实现中，所述根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号，包括：所述aVR导联信号满足：aVR导联＝RE-0.5*(LE+N)；所述aVL导联信号满足：aVL导联＝LE-0.5*(N+RE)，以及所述avF导联信号满足：avF导联＝N-0.5*(LE+RE)；其中，RE为右耳电极信号，LE为左耳电极信号，N为颈部电极信号。
在又一个可能的实现中，所述提取所述多导联信号的特征，包括：获取所述多导联信号的平均值；以及根据所述多导联信号中每个导联的信号以及所述多导联信号的平均值，获得所述每个导联的信号对应的相关系数作为所述每个导联的信号的特征。
在该实现中，导联信号对应的相关系数可以准确地表示导联信号的特征。
在又一个可能的实现中，所述方法还包括：根据所述每个导联的信号对应的相关系数，获取所述多导联信号对应的相关系数的平均值，作为多导联信号的质量；若所述多导联信号对应的相关系数的平均值大于所述第一阈值，或所述加速度信号小于或等于第二阈值，则执行所述提取所述多导联信号的特征的步骤；以及若所述多导联信号对应的相关系数的平均值小于或等于所述第一阈值，且所述加速度信号大于或等于第三阈值，则执行所述切换到带右腿驱动的单导联模式的步骤。
在该实现中，当多导联信号的质量较差且用户处于运动状态时，测量得到的多导联信号不稳定，不能作为测量结果输出。因此，切换到带右腿驱动的单导联测量模式，可以通过右腿驱动电极的负反馈消除单导联信号的共模信号，从而可以得到质量较好的单导联信号。
在又一个可能的实现中，所述方法还包括：筛选所述多导联信号中信号大于第四阈值的信号；以及提取所述筛选出的信号的特征。
在该实现中，可以根据需要在多导联信号中筛选信号质量较好的信号，再提取筛选后的信号的特征，从而提高输出结果的质量。
在又一个可能的实现中，若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，切换到带右腿驱动的单导联模式，获取单导联信号，包括：若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，控制所述模式选择开关切换至所述右腿驱动电极，开启单导联模式；所述获取单导联信号，包括：根据所述左耳电极、所述右耳电极和所述中心电端的信号，获取所述单导联信号；以及所述消除所述单导联信号中的共模信号，包括：根据所述中心电端的信号和基准电平信号，经过所述右腿驱动电极的负反馈，获取用户的共模信号；消除所述单导联信号中的共模信号。
在该实现中，当多导联信号的质量较差且用户处于运动状态时，测量得到的多导联信号不稳定，不能作为测量结果输出。因此，切换到带右腿驱动的单导联测量模式，可以通过右腿驱动电极的负反馈消除单导联信号的共模信号，从而可以得到质量较好的单导联信号。
在又一个可能的实现中，所述获取用户的状态，包括：获取加速度信号；若所述加速度信号小于或等于所述第二阈值，确定所述用户处于静态；以及若所述加速度信号大于或等于所述第三阈值，确定所述用户处于运动状态。
在该实现中，用户的状态对信号的测量具有较大的影响，因此，通过加速度信号的判断，可以得到准确的用户状态。
第二方面，提供了一种信号测量装置，所述装置包括：模式选择开关，用于开启多导联测量模式；信号获取模块，用于获取多导联信号及用户的状态；特征提取模块，用于提取所述多导联信号的特征；信号质量获取模块，用于根据所述多导联信号的特征，获取所述多导联信号的质量；输出模块，用于若所述多导联信号大于第一阈值，或所述用户处于静态时，输出提取出的所述多导联信号的特征；所述模式选择开关，还用于若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态时，切换到带右腿驱动的单导联模式；所述信号获取模块，还用于获取单导联信号；共模信号消除模块，用于消除所述单导联信号中的共模信号；所述特征提取模块，还用于提取所述经消除处理的单导联信号的特征；以及所述输出模块，还用于输出提取出的所述单导联信号的特征。
在一个可能的实现中，所述信号获取模块包括左耳电极、右耳电极、颈部电极、三个电极分别对应的前置放大器、威尔逊网络电路和处理器，所述共模信号消除模块包括右腿驱动电极和共模放大器；其中，所述左耳电极连接左耳测量部件，所述右耳电极连接右耳测量部件，以及所述模式选择开关连接颈部测量部件；所述左耳电极、右耳电极、颈部电极分别连接至对应的前置放大器的正极以及威尔逊网络电路，所述威尔逊网络电路的中心电端分别连接至三个电极的前置放大器的负极，所述三个电极分别对应的前置放大器连接至所述处理器；所述威尔逊网络电路的中心电端还连接至所述共模放大器的负极；以及所述模块选择开关用于连接至所述颈部电极，以开启多导联测量模式。
在又一个可能的实现中，所述信号获取模块用于：测量所述左耳电极和右耳电极之间 的信号，得到Ⅰ导联信号；测量所述右耳电极和所述颈部电极之间的信号，得到Ⅱ导联信号；测量所述左耳电极和颈部电极之间的信号，得到Ⅲ导联信号；以及根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
在又一个可能的实现中，所述aVR导联信号满足：aVR导联＝RE-0.5*(LE+N)；所述aVL导联信号满足：aVL导联＝LE-0.5*(N+RE)，以及所述avF导联信号满足：avF导联＝N-0.5*(LE+RE)；其中，RE为右耳电极信号，LE为左耳电极信号，N为颈部电极信号。
在又一个可能的实现中，所述特征提取模块，用于获取所述多导联信号的平均值；以及根据所述多导联信号中每个导联的信号以及所述多导联信号的平均值，获得所述每个导联的信号对应的相关系数作为所述每个导联的信号的特征。
在又一个可能的实现中，所述信号质量获取模块，用于根据所述每个导联的信号对应的相关系数，获取所述多导联信号对应的相关系数的平均值，作为多导联信号的质量；所述输出模块，用于若所述多导联信号对应的相关系数的平均值大于所述第一阈值，或所述加速度信号小于所述第二阈值，则输出所述多导联信号的特征；以及所述模式选择开关用于若所述多导联信号对应的相关系数的平均值小于或等于所述第一阈值，且所述加速度信号大于或等于所述第二阈值，则切换到带右腿驱动的单导联模式。
在又一个可能的实现中，所述装置还包括：信号筛选模块，用于筛选所述多导联信号中信号大于第四阈值的信号；所述特征提取模块，用于提取所述筛选出的信号的特征。
在又一个可能的实现中，所述模式选择开关用于若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，切换至所述右腿驱动电极，开启单导联模式；所述信号获取模块，用于根据所述左耳电极、所述右耳电极和所述中心电端的信号，获取所述单导联信号；以及所述共模信号消除模块，用于根据所述中心电端的信号和基准电平信号，经过所述右腿驱动电极的负反馈，获取用户的共模信号，以及消除所述单导联信号中的共模信号。
在又一个可能的实现中，所述信号获取模块还用于获取加速度信号；所述装置还包括：确定模块，用于若所述加速度信号小于或等于第二阈值，确定所述用户处于静态；以及所述确定模块，还用于若所述加速度信号大于或等于第三阈值，确定所述用户处于运动状态。
第三方面，提供了一种信号测量装置，包括输入装置、输出装置、存储器和处理器，所述存储器中存储有程序指令，所述处理器用于调用所述程序指令执行如下操作：
开启多导联测量模式，获取多导联信号及用户的状态；提取所述多导联信号的特征，并根据所述多导联信号的特征，获取所述多导联信号的质量；若所述多导联信号的质量大于第一阈值，或所述用户处于静态时，控制所述输出装置输出提取出的所述多导联信号的特征；若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态时，切换到带右腿驱动的单导联模式，获取单导联信号；消除所述单导联信号中的共模信号；提取所述经消除处理的单导联信号的特征，并控制所述输出装置输出提取的单导联信号的特征。
在一个可能的实现中，所述处理器还用于执行如下操作：控制所述模式选择开关连接 至所述颈部电极，以开启多导联测量模式。
在又一个可能的实现中，所述处理器执行所述获取多导联信号的操作，包括：测量所述左耳电极和右耳电极之间的信号，得到Ⅰ导联信号；测量所述右耳电极和所述颈部电极之间的信号，得到Ⅱ导联信号；测量所述左耳电极和颈部电极之间的信号，得到Ⅲ导联信号；以及根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
在又一个可能的实现中，所述处理器执行所述根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号的操作，包括：所述aVR导联信号满足：aVR导联＝RE-0.5*(LE+N)；所述aVL导联信号满足：aVL导联＝LE-0.5*(N+RE)，以及所述avF导联信号满足：avF导联＝N-0.5*(LE+RE)；其中，RE为右耳电极信号，LE为左耳电极信号，N为颈部电极信号。
在又一个可能的实现中，所述处理器执行所述提取所述多导联信号的特征的操作，包括：获取所述多导联信号的平均值；以及根据所述多导联信号中每个导联的信号以及所述多导联信号的平均值，获得所述每个导联的信号对应的相关系数作为所述每个导联的信号的特征。
在又一个可能的实现中，所述处理器还执行如下操作：根据所述每个导联的信号对应的相关系数，获取所述多导联信号对应的相关系数的平均值，作为多导联信号的质量；若所述多导联信号对应的相关系数的平均值大于所述第一阈值，或所述加速度信号小于或等于第二阈值，则执行所述提取所述多导联信号的特征的操作；以及若所述多导联信号对应的相关系数的平均值小于或等于所述第一阈值，且所述加速度信号大于或等于第三阈值，则执行所述切换到带右腿驱动的单导联模式的操作。
在又一个可能的实现中，所述处理器还执行如下操作：筛选所述多导联信号中信号大于第四阈值的信号；以及提取所述筛选出的信号的特征。
在又一个可能的实现中，所述处理器执行所述若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，切换到带右腿驱动的单导联模式，获取单导联信号的操作，包括：若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，控制所述模式选择开关切换至所述右腿驱动电极，开启单导联模式；所述处理器执行所述获取单导联信号的操作，包括：根据所述左耳电极、所述右耳电极和所述中心电端的信号，获取所述单导联信号；以及所述处理器执行所述消除所述单导联信号中的共模信号的操作，包括：根据所述中心电端的信号和基准电平信号，经过所述右腿驱动电极的负反馈，获取用户的共模信号；消除所述单导联信号中的共模信号。
在又一个可能的实现中，所述处理器执行所述获取用户的状态的操作，包括：获取加速度信号；若所述加速度信号小于或等于所述第二阈值，确定所述用户处于静态；以及若所述加速度信号大于或等于所述第三阈值，确定所述用户处于运动状态。
第四方面，提供了一种计算机可读存储介质，所述计算机可读存储介质中存储有指令，当其在计算机上运行时，使得计算机执行上述第一方面或第一方面的任一个可能的实现所述的方法。
第五方面，提供了一种包含指令的计算机程序产品，当其在计算机上运行时，使得计 算机执行上述第一方面或第一方面的任一个可能的实现所述的方法。
附图说明
图1为本申请实施例提供的颈挂式耳机的结构示意图；
图2为本申请实施例提供的一种信号测量装置的结构示意图；
图3为本申请实施例提供的一种信号测量方法的流程示意图；
图4为本申请实施例提供的又一种信号测量方法的流程示意图；
图5为利用图1所示的颈挂式耳机在多导联测量模式下测量的示意图；
图6为示例的信号测量装置处于多导联测量模式时的内部电路结构示意图；
图7为示例的信号测量装置处于单导联测量模式时的内部电路结构示意图；
图8为用户使用信号测量装置进行测量的场景示意图；
图9为本申请实施例提供的又一种信号测量装置的结构示意图。
具体实施方式
下面结合本申请实施例中的附图对本申请实施例进行描述。
目前存在这样的方案：通过在耳机上设置2-3个电极，佩戴耳机时可实现ECG实时测量。但是，当前耳机上设置电极进行ECG测量的方案，目前都为单导联方案，获取的信息较少。如图1所示，为本申请实施例提供的颈挂式耳机的结构示意图，在该颈挂式耳机上，电极的设置方式为左耳(left ear，LE)机外壳部分测量部件1(连接LE电极)、右耳(right ear，RE)机外壳部分测量部件2(连接RE电极)分别用于接触用户的左右耳耳廓皮肤。但不受限地，该左右耳外壳可以实施为耳挂等结构。颈部(neck，N)测量部件3(连接N电极)，用作六导联方案时的第三个电极，以及单导联方案时的“右腿驱动电极”。4为处理电路，该处理电路包括模拟前端(analog front end，AFE)、加速度计(accelerometer，ACC)和微控制单元(micro control unit，MCU)，其中，AFE包括上述各电极、运算放大器(amplifier，AMP)和模数转换器(analog-to-digital converter，ADC)等。在一个实施例中，颈挂式耳机可以自身处理测量得到的信号；在另一个实施例中，颈挂式耳机测量到各个电极的信号后，也可以发送给与耳机无线连接的终端，由终端进行处理。则电路4中还可以包括通信模块，例如蓝牙传输模块，该通信模块的通信方式可以是无线或有线连接方式。上述终端可以是手机、智能手表、智能手环、电脑等。
本实施例的颈挂式耳机可以工作在多导联测量模式和单导联测量模式。具体地，可以利用电极1、2、3测量得到的信号经过处理后得到多导联信号，在多导联信号质量较好或者用户处于相对静态时，提取多导联信号的特征；若多导联信号质量较差或者用户处于运动状态，可以切换到单导联测量模式，此时，颈部电极作为右腿驱动电极，且左耳、右耳电极表面电信号的共模分量传输至右腿驱动电极，经过右腿驱动的负反馈，从而迫使人体共模电压接近基准电平，使得所有电极输入的中心位于输入范围的中心，可减少系统的共模噪声，提升单导联信号的信号质量。
图2为本申请实施例提供的一种信号测量装置的结构示意图，该信号测量装置1000包括：模式选择开关11，用于开启多导联测量模式；信号获取模块12，用于获取多导联信 号及用户的状态；特征提取模块13，用于提取所述多导联信号的特征；信号质量获取模块14，用于根据所述多导联信号的特征，获取所述多导联信号的质量；输出模块15，用于若所述多导联信号的质量大于第一阈值，或所述用户处于静态时，输出提取出的所述多导联信号的特征；所述模式选择开关11，还用于若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态时，切换到带右腿驱动的单导联模式；所述信号获取模块12，还用于获取单导联信号；共模信号消除模块16，用于消除所述单导联信号中的共模信号；所述特征提取模块13，还用于提取所述经消除处理的单导联信号的特征；以及所述输出模块15，还用于输出提取出的所述单导联信号的特征。
在一个可能的实现中，所述信号获取模块12包括左耳电极、右耳电极、颈部电极、三个电极分别对应的前置放大器、威尔逊网络电路和处理器，所述共模信号消除模块16包括右腿驱动电极和共模放大器；其中，所述左耳电极连接左耳测量部件，所述右耳电极连接右耳测量部件，以及所述模式选择开关11连接颈部测量部件；所述左耳电极、右耳电极、颈部电极分别连接至对应的前置放大器的正极以及威尔逊网络电路，所述威尔逊网络电路的中心电端分别连接至三个电极的前置放大器的负极，所述三个电极分别对应的前置放大器连接至所述处理器；所述威尔逊网络电路的中心电端还连接至所述共模放大器的负极；以及所述模块选择开关11用于连接至所述颈部电极，以开启多导联测量模式。
在又一个可能的实现中，所述信号获取模块12用于：测量所述左耳电极和右耳电极之间的信号，得到Ⅰ导联信号；测量所述右耳电极和所述颈部电极之间的信号，得到Ⅱ导联信号；测量所述左耳电极和颈部电极之间的信号，得到Ⅲ导联信号；以及根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
在又一个可能的实现中，所述aVR导联信号满足：aVR导联＝RE-0.5*(LE+N)；所述aVL导联信号满足：aVL导联＝LE-0.5*(N+RE)，以及所述avF导联信号满足：avF导联＝N-0.5*(LE+RE)；其中，RE为右耳电极信号，LE为左耳电极信号，N为颈部电极信号。
在又一个可能的实现中，所述特征提取模块13，用于获取所述多导联信号的平均值；以及根据所述多导联信号中每个导联的信号以及所述多导联信号的平均值，获得所述每个导联的信号对应的相关系数作为所述每个导联的信号的特征。
在又一个可能的实现中，所述信号质量获取模块14，用于根据所述每个导联的信号对应的相关系数，获取所述多导联信号对应的相关系数的平均值；所述输出模块15，用于若所述多导联信号对应的相关系数的平均值大于所述第一阈值，或所述加速度信号小于所述第二阈值，则输出提取出的所述多导联信号的特征；以及所述模式选择开关11用于若所述多导联信号对应的相关系数的平均值小于或等于所述第一阈值，且所述加速度信号大于或等于所述第二阈值，则切换到带右腿驱动的单导联模式。
在又一个可能的实现中，所述装置还包括：信号筛选模块18，用于筛选所述多导联信号中信号大于第四阈值的信号；所述特征提取模块13，用于提取所述筛选出的信号的特征。
在又一个可能的实现中，所述模式选择开关11用于若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，切换至所述右腿驱动电极，开启单导联模式；所 述信号获取模块12，用于根据所述左耳电极、所述右耳电极和所述中心电端的信号，获取所述单导联信号；以及所述共模信号消除模块16，用于根据所述中心电端的信号和基准电平信号，经过所述右腿驱动电极的负反馈，获取用户的共模信号，以及消除所述单导联信号中的共模信号。
在又一个可能的实现中，所述信号获取模块12还用于获取加速度信号；所述装置还包括：确定模块17，用于若所述加速度信号小于或等于第二阈值，确定所述用户处于静态；以及所述确定模块，还用于若所述加速度信号大于或等于第三阈值，确定所述用户处于运动状态。
下面结合图2所示的信号测量装置对信号测量的过程进行详细描述：
图3为本申请实施例提供的一种信号测量方法的流程示意图，该方法可以包括：
S101、模式选择开关开启多导联测量模式，信号获取模块获取多导联信号及用户的状态。
本实施例中，信号测量装置包括多个测量电极(例如，如图1所示的颈挂式耳机的LE、RE、N电极)，可以测量多个测量部件(LE、RE、N的测量部件)的信号。该信号测量装置还包括一个右腿驱动电极。包括该右腿驱动电极的右腿驱动电路本质上是一个负反馈，右腿驱动电路作用就是常用于去除输入放大器中的共模信号，提高共模抑制比(common mode rejection ratio，CMRR)；通过反向放大共模信号接到人体起到消除共模的作用。右腿驱动作用主要是在生物电采集中降低共模电压。右腿驱动是降低共模干燥的必要方法。
模式选择单元一端连接其中一个测量部件(例如上述N测量部件)，另一端可连接一个测量电极(例如N电极)，或者连接右腿驱动电极。当模式选择单元的另一端连接上述测量电极(例如N电极)时，信号测量装置开启多导联测量模式；当模式选择单元的另一端连接右腿驱动电极时，信号测量装置开启单导联测量模式。
模式选择单元可以接收终端发送的指令或根据信号测量装置的默认配置，开启多导联测量模式。具体地，该终端发送的指令用于指示信号测量装置开启多导联测量模式；或者信号测量装置默认配置开机时开启多导联测量模式。进一步地，若在开启多导联模式之前，信号测量装置处于单导联模式，则可以根据模式选择单元的切换控制信号，切换至多导联测量模式。
本实施例中，多导联可以是六导联。信号测量装置可以包括三个测量电极，通过威尔逊网络，就可以得到六导联的信号。
S102、特征提取模块提取多导联信号的特征。
获取的多导联信号是用户的较为完整的心电信号。心电信号一般可以用心电图体现。心电图中的每一个心动循环周期由一系列有规律的波形组成，它们分别是P波、QRS复合波和T波，而这些波形的起点、终点、波峰、波谷、以及间期分别记录着心脏活动状态的详细信息，为心脏疾病的诊断提供者重要的分析依据。因此，获取到多导联信号后，可以提取多导联信号的特征。
具体地，提取多导联信号的ECG波形中的P波、PR间期、QRS波群、J点、ST段、T波、U波和QT间期等波形信息，进而获得R-R间期(R-R interval，RRI)或者频域等特征以用于疾病诊断。其中，P波代表了心房的激动，前半部代表右心房激动，后半部代表 左心房的激动。PR间期代表由窦房结产生的兴奋经由心房、房室交界和房室束到达心室并引起心室肌开始兴奋所需要的时间，故也称为房室传导时间。QRS波群代表了心室的除极，激动时限小于0.11秒。当出现心脏左右束枝的传导阻滞、心室扩大或肥厚等情况时，QRS波群出现增宽、变形和时限延长。J点是QRS波结束，ST段开始的交点。代表心室肌细胞全部除极完毕。心室肌全部除极完成，复极尚未开始的一段时间。此时各部位的心室肌都处于除极状态，细胞之间并没有电位差。因此正常情况下ST段应处于等电位线上。当某部位的心肌出现缺血或坏死的表现，心室在除极完毕后仍存在电位差，此时表现为心电图上ST段发生偏移。之后的T波代表了心室的复极。在QRS波主波向上的导联，T波应与QRS主波方向相同。U波与心室的复极有关。QT间期代表了心室从除极到复极的时间。
S103、信号质量获取模块根据多导联信号的特征，获取多导联信号的质量。
获取的多导联信号的质量决定了是否可以将该多导联信号的特征作为测量结果。根据每个导联信号的特征，可以得到多导联信号的整体质量。例如，根据每个导联信号的特征的平均值，可以获取多导联信号的质量。
S104、模式选择开关判断多导联信号的质量是否大于第一阈值，若多导联信号的质量大于第一阈值，则进行到步骤S106；若多导联信号的质量小于或等于第一阈值，则进行到步骤S105。
若多导联信号的质量大于第一阈值，说明多导联信号的质量较好，可以将该多导联信号作为测量结果；如果多导联信号的质量小于或等于第一阈值，说明多导联信号的质量较差，不能将该多导联信号作为测量结果，模式选择开关需进行模式切换。该第一阈值可以根据经验设定。
S105、模式选择开关判断用户是否处于静态，若用户处于静态，则进行到步骤S106；若用户处于运动状态，则转至步骤S107。
若用户处于静态，则测量的多导联信号较为稳定，可以将多导联测量模式下测量得到的多导联信号作为测量结果；但如果用户处于运动状态，会给测量带来共模干扰，且当多导联信号的质量较差时，需要切换到带右腿驱动的单导联测量模式下进行测量。
需要说明的是，步骤S105和S104的操作没有先后顺序，即模式选择开关可以先判断多导联信号的质量是否大于第一阈值，再判断用户是否处于静态；也可以先判断用户是否处于静态，再判断多导联信号的质量是否大于第一阈值；或者同时判断多导联信号的质量是否大于第一阈值，用户是否处于静态。
当多导联信号的质量大于第一阈值或者用户处于静态时，继续执行多导联测量模式下的操作；当多导联信号的质量小于或等于第一阈值，且用户处于运动状态时，模式选择开关切换到带右腿驱动的单导联模式下进行测量。
S106、输出模块输出提取出的多导联信号的特征。
可以通过语音、屏幕显示等方式输出提取出的多导联信号的特征。
S107、模式选择开关判断多导联信号的质量小于或等于第一阈值，且用户处于运动状态，则切换到带右腿驱动的单导联模式。信号获取模块获取单导联信号。
若多导联信号质量小于或等于第一阈值，且用户处于运动状态时，模式选择开关切换到带右腿驱动的单导联模式。信号获取模块获取单导联信号。具体地，信号获取模块使用 除连接到模式选择开关的测量电极之外的其它两个电极进行测量，得到单导联信号。
S108、共模信号消除模块消除单导联信号中的共模信号。
两个电极表面电信号的共模分量传输至右腿驱动电路，经过右腿驱动的负反馈，从而迫使人体共模电压接近基准电平，使得所有电极输入的中心位于输入范围的中心，可减少系统的共模噪声，即可以消除单导联信号中的共模信号，提升系统信号质量。
S109、特征提取模块提取经消除处理的单导联信号的特征。
与提取多导联信号的特征类似，特征提取模块可以提取经消除处理的单导联信号的特征。
进一步地，在提取单导联信号的特征之前，可以对单导联信号进行滤波。
S110、输出提取出的单导联信号的特征。
可以通过语音、屏幕显示等方式输出提取出的单导联信号的特征。
根据本申请实施例提供的一种信号测量方法，通过信号质量与用户运动状态的判断，实现三电极ECG系统多导联ECG测量与带右腿驱动电极单导联ECG测量模式之间的自动切换，在多导联信号质量较高时，输出提取的多导联信号的特征，或者消除单导联信号中的共模信号后，才提取并输出经消除处理的单导联信号的特征，从而可以获取更高质量的心电信号，实现用户心电信号的准确测量。
图4为本申请实施例提供的又一种信号测量方法的流程示意图，该方法可以包括：
S201、模式选择开关连接至颈部电极，以开启多导联测量模式。
本实施例中，该信号测量装置可以是如图1所示的颈挂式耳机。根据用户指令或内部操作指令，模式选择开关连接至颈部电极，以开启多导联测量模式。模式选择开关连接至颈部电极时，则与右腿驱动电极是断开的。
S202、信号获取模块测量左耳电极和右耳电极之间的信号，得到Ⅰ导联信号；测量右耳电极和颈部电极之间的信号，得到Ⅱ导联信号；以及测量左耳电极和颈部电极之间的信号，得到Ⅲ导联信号。
S203、信号获取模块根据Ⅰ导联信号、Ⅱ导联信号和Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
如图5所示，为利用图1所示的颈挂式耳机在多导联测量模式下测量的示意图，左耳LE电极、右耳RE电极和颈部N电极都连接至中心电端，电极LE和电极RE构成Ⅰ导联，电极N和电极RE构成Ⅱ导联，电极N和电极LE构成Ⅲ导联。
如图6所示，示例了信号测量装置处于多导联测量模式时的内部电路示意图，当然信号测量的电路结构不限于此。使用左耳(left ear，LE)、右耳(right ear，RE)、颈部(neck，N)三个电极采集皮肤表面心电信号，三个电极表面电信号经过多路复用器(multiplexer，MUX)电路以及威尔逊(Wilson)网络形成六导联系统，并经过两级可调增益的运算放大器(例如，AD761)进行放大滤波，经放大、滤波、模数转换器(analog-to-digital converter，ADC)转换后的信号传输至MCU中。其中，威尔逊网络是一个电阻网络，将LE、RE、N三个电极经过三个相等的电阻接在一起组成一个平均电位的中心端，称为威尔逊中心电端，中央电势端或威尔森中央电端，该中心电端的电压代表了身体的平均电压。然后，使用加速度计(accelerometer，ACC)测量得到的加速度信号经过ADC处理传输到MCU中。由 MCU对上述LE、RE、N和中心电端的信号进行处理，得到多导联信号。具体在进行测量模式选择和测量时，多路复用器内部开关切换到ECG3，使颈部(N)电极连接到AFE模块的ECG3输入。此时断开与右腿驱动电路(RLD)的连接，右腿驱动电路不工作。3个电极信号输入到运算放大器A的正极，人体共模电压通过3个电极通道输入运算放大器A，运算放大器A输出得到Wilson中心电端Vcm，Vcm输入到3个ECG前置放大器(即ECG1的前置放大器、ECG2的前置放大器、ECG3的前置放大器)的负极。从而可形成三电极输入的六导联系统。
其中，六导联是指Ⅰ导联，Ⅱ导联，Ⅲ导联，aVR导联、aVL导联和avF导联。电极LE和电极RE构成Ⅰ导联，电极N和电极RE构成Ⅱ导联，电极N和电极LE构成Ⅲ导联。aVR导联、aVL导联和avF导联可以根据上述Ⅰ导联，Ⅱ导联和Ⅲ导联推算得到：aVR导联＝RE-0.5*(LE+N)，aVL导联＝LE-0.5*(N+RE)，以及avF导联＝N-0.5*(LE+RE)。
仍然参考图5，左耳LE电极、右耳RE电极和颈部N电极都连接至中心电端，电极LE和电极RE构成Ⅰ导联，电极N和电极RE构成Ⅱ导联，电极N和电极LE构成Ⅲ导联。中心电端输入到3个ECG电极的前置放大器的负极，从而形成六导联，即aVR导联、aVL导联和avF导联可以根据上述Ⅰ导联，Ⅱ导联和Ⅲ导联推算得到：aVR导联＝RE-0.5*(LE+N)，aVL导联＝LE-0.5*(N+RE)，以及avF导联＝N-0.5*(LE+RE)。
S204、特征提取模块获取多导联信号的平均值。
S205、特征提取模块根据多导联信号中每个导联的信号以及多导联信号的平均值，获得每个导联的信号对应的相关系数作为每个导联的信号的特征。
将电极LE、RE和N的信号输入到MCU，MCU根据上述六导联的构成，可以得到六导联信号为A1～A6。进一步地，在获取到各个电极的信号后，以及在传输到MCU之前，可以对信号进行滤波。
特征提取包括提取多导联信号中的Pearson相关系数，Spearman相关系数等相关系数，相关系数是用以反映变量之间相关关系密切程度的统计指标。其中，Pearson相关系数(Pearson correlation coefficient)是用来衡量两个数据集合是否在一条线上面，它用来衡量定距变量间的线性关系。在统计学中,以查尔斯·斯皮尔曼命名的斯皮尔曼等级相关系数，即Spearman相关系数。经常用希腊字母ρ表示。它是衡量两个变量的依赖性的非参数指标。它利用单调方程评价两个统计变量的相关性。如果数据中没有重复值，并且当两个变量完全单调相关时，斯皮尔曼相关系数则为+1或-1。
对于ECG信号，某个导联与多导联平均值相关系数越高，则信号质量越好。可以根据每个导联的信号与六个导联信号的平均值来计算得到六个相关系数，其中，六个导联的平均值A＝(∣A1∣+∣A2∣+∣A3∣+∣A4∣+∣A5∣+∣A6∣)/6，则A1对应的相关系数为γ 1＝cov(A,A1)/σ Aσ A1,A2对应的相关系数为γ 2＝cov(A,A2)/σ Aσ A2，以此类推。
S206、信号质量获取模块根据每个导联的信号对应的相关系数，获取多导联信号对应的相关系数的平均值，作为多导联信号的质量。
在获得每个导联信号的相关系数后，可以得到六个相关系数的平均数Feat1＝(∣γ 1∣+∣γ 2∣+∣γ 3∣+∣γ 4∣+∣γ 5∣+∣γ 6∣)/6，它反应了多导联信号整体的信号质量。
可以理解的是，也可以根据多个导联信号本身确定信号的质量。信号质量可以是一个 具体的信号值。
S207、模式选择开关判断多导联信号对应的相关系数的平均值是否大于第一阈值，若是，则进行到步骤S209；否则，转至步骤S208。
模式选择开关判断多导联信号的质量是否大于第一阈值。具体地，模式选择开关根据上述获得的多导联信号对应的相关系数的平均值，判断该平均值是否大于第一阈值。
S208、确定模块判断加速度信号是否小于或等于第二阈值，若是，则进行到步骤S209；否则，转至步骤S211。
判断用户是处于静态或运动状态，可以通过装置的加速度信号进行判断。则信号获取模块还可以获取加速度信号。具体地，可以通过加速度传感器采集用户的加速度信号。并传输该加速度信号到MCU。该加速度传感器具体可以是重力传感器等。当用户佩戴耳机进入运动状态时，颈挂式耳机利用其重力传感器内部由于加速度造成的晶体变形这个特性，由于这个变形会产生电压，只要计算出产生电压和所施加的加速度之间的关系，就可以将加速度转化成电压输出。
确定模块判断加速度信号小于或等于第二阈值时，用户处于静态；加速度信号大于或等于第三阈值时，用户处于运动状态。确定模块将判断结果输出给模式选择开关。
需要说明的是，S207和S208没有先后顺序，在当多导联信号对应的相关系数的平均值或者加速度信号小于或等于第二阈值时，则执行S209。
S209、若多导联信号对应的相关系数的平均值大于第一阈值，或者加速度信号小于或等于第二阈值，信号筛选模块筛选多导联信号中信号大于第四阈值的信号。
若多导联信号的质量大于第一阈值，是指上述获得的多导联系统的整体的信号质量大于第一阈值，整体的信号质量较好；或加速度信号小于或等于第二阈值，则说明用户当前基本处于静态，采用多导联系统获得的多导联信号质量较好。
在确定可以输出多导联信号时，可以根据需要筛选所需的导联信号。例如，对于需要观察特定导联才能诊断的疾病，如冠心病，则筛选所需的导联信号。又例如，将每个导联的信号与第四阈值进行比较，筛选出信号大于或等于第四阈值的导联信号。
进一步地，可以对筛选出的导联信号进行滤波。
S210、输出筛选出的信号的特征。
由于前面已经提取了多导联信号中每个导联信号的特征，因此，根据筛选出的导联信号，可以输出筛选出的信号的特征。
S211、确定模块判断加速度信号是否大于或等于第三阈值，若是，则进行到步骤S212；否则，转至步骤S208。
若多导联信号对应的相关系数的平均值小于或等于第一阈值，即多导联信号的质量较差；且确定模块判断加速度信号大于或等于第三阈值，即用户处于运动状态，则输出判断结果给模式切换开关。
S212、模式切换开关切换到带右腿驱动的单导联模式。
模式切换开关在确定多导联信号的质量较差，且用户处于运动状态时，切换到带右腿驱动的单导联模式。
S213、信号获取模块根据左耳电极、右耳电极和中心电端的信号，获取单导联信号。
S214、根据中心电端的信号和基准电平信号，经过右腿驱动电极的负反馈，获取用户的共模信号。
S215、消除单导联信号中的共模信号。
具体地，如图7所示，为示例的信号测量装置处于单导联测量模式时的内部电路结构示意图。若多导联信号质量小于或等于第一阈值，且加速度信号大于或等于第二阈值，多路复用器内部开关切换到RLD，使颈部(N)电极连接到AFE模块的RLD，同时断开与AFE模块的ECG3的连接，AFE模块的ECG3通道不工作。2个电极信号(LE、RE)输入到ECG前置放大器的正极，人体共模电压(两个电极表面电信号的共模分量)通过2个电极通道(LE、RE)输入运算放大器A，运算放大器A输出得到Wilson中心电端Vm，Vm输入到2个ECG前置放大器的负极，同时输入到右腿驱动电路运算放大器B的负极，经过右腿驱动电路反馈到人体。运算放大器B的正极输入1.3V基准电平，经过右腿驱动的负反馈，从而迫使人体共模电压接近基准电平，使得所有电极输入的中心位于输入范围的中心，形成带“右腿驱动”的单导联电路。从而可以消除单导联信号中的共模信号，获得质量较好的单导联信号。
S216、提取经消除处理的单导联信号的特征。
在消除单导联信号中的共模信号后，可以提取出经消除处理的单导联信号的特征。提取的过程可参考步骤S204和S205。
S217、输出提取出的单导联信号的特征。
根据本申请实施例提供的一种信号测量方法，通过信号质量与用户运动状态的判断，实现三电极ECG系统多导联ECG测量与带右腿驱动电极单导联ECG测量模式之间的自动切换，在多导联信号质量较高时，输出提取的多导联信号的特征，或者消除单导联信号中的共模信号后，才提取并输出经消除处理的单导联信号的特征，从而可以获取更高质量的心电信号，实现用户心电信号的准确测量。
如图8所示，为用户使用信号测量装置进行测量的场景示意图，结合上面的描述，在实际使用过程中，用户佩戴上述颈挂式耳机，开启耳机测量心电信号时，耳机默认进入多导联测量模式。同时，利用耳机中的加速度传感器测量加速度信号，判断用户处于相对静止状态时，利用左耳、右耳、颈部三个电极测量得到的信号经过处理后得到多导联信号，在多导联信号质量较好或者用户处于相对静态时，提取多导联信号的特征。若多导联信号质量较差或者用户处于运动状态，可以切换到单导联测量模式，此时，颈部电极作为右腿驱动电极，且左耳、右耳电极表面电信号的共模分量传输至右腿驱动电极，经过右腿驱动的负反馈，从而迫使人体共模电压接近基准电平，使得所有电极输入的中心位于输入范围的中心，可减少系统的共模噪声，提升单导联信号的信号质量。
耳机测量得到上述电极的信号后，耳机内部可以处理上述信号得到多导联信号或单导联信号，并提取导联信号的特征。并可以通过耳机播放器输出上述导联信号的特征。耳机测量得到上述电极的信号后，也可以将上述信号传输至与耳机建立无线连接的终端，例如用户手机或其他可穿戴式设备，由手机或其他可穿戴式设备处理上述信号得到多导联信号或单导联信号，并提取导联信号的特征，并在手机或其他可穿戴式设备端输出。从而，可以降低对信号测量装置的计算能力和信号输出能力等的要求。
如图9所示，还提供了一种信号测量装置的结构示意图，该信号测量装置用于执行上述信号测量方法。上述方法中的部分或全部可以通过硬件来实现，也可以通过软件或固件来实现。
可选的，该信号测量装置在具体实现时可以是芯片或者集成电路。
可选的，当上述实施例的信号测量方法中的部分或全部通过软件或固件来实现时，可以通过图9提供的一种信号测量装置2000来实现。如图9所示，该信号测量装置2000可包括：
存储器23和处理器24(装置中的处理器24可以是一个或多个，图9中以一个处理器为例)，还可以包括输入装置21、输出装置22。在本实施例中，输入装置21、输出装置22、存储器23和处理器24可通过总线或其它方式连接，其中，图9中以通过总线连接为例。
其中，处理器24用于执行图3、图4中所执行的方法步骤。
具体地，处理器24用于调用所述程序指令执行如下操作：
开启多导联测量模式，获取多导联信号及用户的状态；提取所述多导联信号的特征，并根据所述多导联信号的特征，获取所述多导联信号的质量；若所述多导联信号的质量大于第一阈值，或所述用户处于静态时，控制所述输出装置输出提取出的所述多导联信号的特征；若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态时，切换到带右腿驱动的单导联模式，获取单导联信号；消除所述单导联信号中的共模信号；提取所述经消除处理的单导联信号的特征，并控制所述输出装置输出提取的单导联信号的特征。
在一个可能的实现中，处理器24还用于执行如下操作：控制所述模式选择开关连接至所述颈部电极，以开启多导联测量模式。
在又一个可能的实现中，处理器24执行所述获取多导联信号的操作，包括：测量所述左耳电极和右耳电极之间的信号，得到Ⅰ导联信号；测量所述右耳电极和所述颈部电极之间的信号，得到Ⅱ导联信号；测量所述左耳电极和颈部电极之间的信号，得到Ⅲ导联信号；以及根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
在又一个可能的实现中，处理器24执行所述根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号的操作，包括：所述aVR导联信号满足：aVR导联＝RE-0.5*(LE+N)；所述aVL导联信号满足：aVL导联＝LE-0.5*(N+RE)，以及所述avF导联信号满足：avF导联＝N-0.5*(LE+RE)；其中，RE为右耳电极信号，LE为左耳电极信号，N为颈部电极信号。
在又一个可能的实现中，处理器24执行所述提取所述多导联信号的特征的操作，包括：获取所述多导联信号的平均值；以及根据所述多导联信号中每个导联的信号以及所述多导联信号的平均值，获得所述每个导联的信号对应的相关系数作为所述每个导联的信号的特征。
在又一个可能的实现中，处理器24还执行如下操作：根据所述每个导联的信号对应的相关系数，获取所述多导联信号对应的相关系数的平均值，作为多导联信号的质量；若所述多导联信号对应的相关系数的平均值大于所述第一阈值，或所述加速度信号小于或等 于第二阈值，则执行所述提取所述多导联信号的特征的操作；以及若所述多导联信号对应的相关系数的平均值小于或等于所述第一阈值，且所述加速度信号大于或等于第三阈值，则执行所述切换到带右腿驱动的单导联模式的操作。
在又一个可能的实现中，处理器24还执行如下操作：筛选所述多导联信号中信号大于第四阈值的信号；以及提取所述筛选出的信号的特征。
在又一个可能的实现中，处理器24执行所述若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，切换到带右腿驱动的单导联模式，获取单导联信号的操作，包括：若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，控制所述模式选择开关切换至所述右腿驱动电极，开启单导联模式；处理器24执行所述获取单导联信号的操作，包括：根据所述左耳电极、所述右耳电极和所述中心电端的信号，获取所述单导联信号；以及处理器24执行所述消除所述单导联信号中的共模信号的操作，包括：根据所述中心电端的信号和基准电平信号，经过所述右腿驱动电极的负反馈，获取用户的共模信号；消除所述单导联信号中的共模信号。
在又一个可能的实现中，处理器24执行所述获取用户的状态的操作，包括：获取加速度信号；若所述加速度信号小于或等于所述第二阈值，确定所述用户处于静态；以及若所述加速度信号大于或等于所述第三阈值，确定所述用户处于运动状态。
可选的，上述信号测量方法的程序可以存储在存储器23中。该存储器23可以是物理上独立的单元，也可以与处理器24集成在一起。该存储器23也可以用于存储数据。
可选的，当上述实施例的信号测量方法中的部分或全部通过软件实现时，该信号测量装置也可以只包括处理器。用于存储程序的存储器位于该信号测量装置之外，处理器通过电路或电线与存储器连接，用于读取并执行存储器中存储的程序。
处理器可以是中央处理器(central processing unit，CPU)，网络处理器(network processor，NP)，或WLAN设备。
处理器还可以进一步包括硬件芯片。上述硬件芯片可以是专用集成电路(application-specific integrated circuit，ASIC)，可编程逻辑器件(programmable logic device，PLD)或其组合。上述PLD可以是复杂可编程逻辑器件(complex programmable logic device，CPLD)，现场可编程逻辑门阵列(field-programmable gate array，FPGA)，通用阵列逻辑(generic array logic，GAL)或其任意组合。
存储器可以包括易失性存储器(volatile memory)，例如随机存取存储器(random-access memory，RAM)；存储器也可以包括非易失性存储器(non-volatile memory)，例如快闪存储器(flash memory)，硬盘(hard disk drive，HDD)或固态硬盘(solid-state drive，SSD)；存储器还可以包括上述种类的存储器的组合。
所属领域的技术人员可以清楚地了解到，为描述的方便和简洁，上述描述的系统、装置和单元的具体工作过程，可以参考前述方法实施例中的对应过程，在此不再赘述。
在本申请所提供的几个实施例中，应该理解到，所揭露的系统、装置和方法，可以通过其它的方式实现。例如，该单元的划分，仅仅为一种逻辑功能划分，实际实现时可以有另外的划分方式，例如，多个单元或组件可以结合或者可以集成到另一个系统，或一些特征可以忽略，或不执行。所显示或讨论的相互之间的耦合、或直接耦合、或通信连接可以 是通过一些接口，装置或单元的间接耦合或通信连接，可以是电性，机械或其它的形式。
作为分离部件说明的单元可以是或者也可以不是物理上分开的，作为单元显示的部件可以是或者也可以不是物理单元，即可以位于一个地方，或者也可以分布到多个网络单元上。可以根据实际的需要选择其中的部分或者全部单元来实现本实施例方案的目的。
在上述实施例中，可以全部或部分地通过软件、硬件、固件或者其任意组合来实现。当使用软件实现时，可以全部或部分地以计算机程序产品的形式实现。该计算机程序产品包括一个或多个计算机指令。在计算机上加载和执行该计算机程序指令时，全部或部分地产生按照本申请实施例的流程或功能。该计算机可以是通用计算机、专用计算机、计算机网络、或者其他可编程装置。该计算机指令可以存储在计算机可读存储介质中，或者通过该计算机可读存储介质进行传输。该计算机指令可以从一个网站站点、计算机、服务器或数据中心通过有线(例如同轴电缆、光纤、数字用户线(digital subscriber line，DSL))或无线(例如红外、无线、微波等)方式向另一个网站站点、计算机、服务器或数据中心进行传输。该计算机可读存储介质可以是计算机能够存取的任何可用介质或者是包含一个或多个可用介质集成的服务器、数据中心等数据存储设备。该可用介质可以是只读存储器(read-only memory，ROM)，或随机存储存储器(random access memory，RAM)，或磁性介质，例如，软盘、硬盘、磁带、磁碟、或光介质，例如，数字通用光盘(digital versatile disc，DVD)、或者半导体介质，例如，固态硬盘(solid state disk，SSD)等。

Claims (18)

  1. 一种信号测量方法，其特征在于，应用于信号测量装置，所述方法包括：
    开启多导联测量模式，获取多导联信号及用户的状态；
    提取所述多导联信号的特征，并根据所述多导联信号的特征，获取所述多导联信号的质量；
    若所述多导联信号的质量大于第一阈值，或所述用户处于静态时，输出提取出的所述多导联信号的特征；
    若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态时，切换到带右腿驱动的单导联模式，获取单导联信号；
    消除所述单导联信号中的共模信号；
    提取并输出所述经消除处理的单导联信号的特征。
  2. 根据权利要求1所述的方法，其特征在于，所述信号测量装置包括左耳电极、右耳电极、颈部电极、三个电极分别对应的前置放大器、威尔逊网络电路、共模产生电路、模式选择开关和处理器，所述左耳电极连接左耳测量部件，所述右耳电极连接右耳测量部件，以及所述模式选择开关连接颈部测量部件；所述共模产生电路包括右腿驱动电极和共模放大器；
    所述左耳电极、右耳电极、颈部电极分别连接至对应的前置放大器的正极以及威尔逊网络电路，所述威尔逊网络电路的中心电端分别连接至三个电极的前置放大器的负极，所述三个电极分别对应的前置放大器连接至所述处理器；
    所述威尔逊网络电路的中心电端还连接至所述共模放大器的负极；
    所述开启多导联测量模式，包括：
    控制所述模式选择开关连接至所述颈部电极，以开启多导联测量模式。
  3. 根据权利要求2所述的方法，其特征在于，所述获取多导联信号，包括：
    测量所述左耳电极和右耳电极之间的信号，得到Ⅰ导联信号；
    测量所述右耳电极和所述颈部电极之间的信号，得到Ⅱ导联信号；
    测量所述左耳电极和颈部电极之间的信号，得到Ⅲ导联信号；
    根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
  4. 根据权利要求3所述的方法，其特征在于，所述根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号，包括：
    所述aVR导联信号满足：aVR导联＝RE-0.5*(LE+N)；
    所述aVL导联信号满足：aVL导联＝LE-0.5*(N+RE)，以及
    所述avF导联信号满足：avF导联＝N-0.5*(LE+RE)；
    其中，RE为右耳电极信号，LE为左耳电极信号，N为颈部电极信号。
  5. 如权利要求3或4所述的方法，其特征在于，所述提取所述多导联信号的特征，包括：
    获取所述多导联信号的平均值；
    根据所述多导联信号中每个导联的信号以及所述多导联信号的平均值，获得所述每个导联的信号对应的相关系数作为所述每个导联的信号的特征。
  6. 如权利要求1～5中任一项所述的方法，其特征在于，所述根据所述多导联信号的特征，获取所述多导联信号的质量，包括：
    根据所述每个导联的信号对应的相关系数，获取所述多导联信号对应的相关系数的平均值，作为所述多导联信号的质量；
    若所述多导联信号对应的相关系数的平均值大于所述第一阈值，或所述加速度信号小于或等于第二阈值，则执行所述输出所述多导联信号的特征的步骤；
    若所述多导联信号对应的相关系数的平均值小于或等于所述第一阈值，且所述加速度信号大于或等于第三阈值，则执行所述切换到带右腿驱动的单导联模式的步骤。
  7. 根据权利要求1～6中任一项所述的方法，其特征在于，所述方法还包括：
    筛选所述多导联信号中信号大于第四阈值的信号；
    提取所述筛选出的信号的特征。
  8. 根据权利要求2～7中任一项所述的方法，其特征在于，若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态，切换到带右腿驱动的单导联模式，获取单导联信号，包括：
    若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态，控制所述模式选择开关切换至所述右腿驱动电极，开启单导联模式；
    所述获取单导联信号，包括：
    根据所述左耳电极、所述右耳电极和所述中心电端的信号，获取所述单导联信号；
    所述消除所述单导联信号中的共模信号，包括：
    根据所述中心电端的信号和基准电平信号，经过所述右腿驱动电极的负反馈，获取用户的共模信号；
    消除所述单导联信号中的共模信号。
  9. 根据权利要求6所述的方法，其特征在于，所述获取用户的状态，包括：
    获取加速度信号；
    若所述加速度信号小于或等于所述第二阈值，确定所述用户处于静态；
    若所述加速度信号大于或等于所述第三阈值，确定所述用户处于运动状态。
  10. 一种信号测量装置，其特征在于，所述装置包括：
    模式选择开关，用于开启多导联测量模式；
    信号获取模块，用于获取多导联信号及用户的状态；
    特征提取模块，用于提取所述多导联信号的特征；
    信号质量获取模块，用于根据所述多导联信号的特征，获取所述多导联信号的质量；
    输出模块，用于若所述多导联信号的质量大于第一阈值，或所述用户处于静态时，输出提取出的所述多导联信号的特征；
    所述模式选择开关，还用于若所述多导联信号的质量小于或等于所述第一阈值，且所述用户处于运动状态时，切换到带右腿驱动的单导联模式；
    所述信号获取模块，还用于获取单导联信号；
    共模信号消除模块，用于消除所述单导联信号中的共模信号；
    所述特征提取模块，还用于提取所述经消除处理的单导联信号的特征；
    所述输出模块，还用于输出提取出的所述单导联信号的特征。
  11. 根据权利要求10所述的装置，其特征在于，所述信号获取模块包括左耳电极、右耳电极、颈部电极、三个电极分别对应的前置放大器、威尔逊网络电路和处理器，所述共模信号消除模块包括右腿驱动电极和共模放大器；其中，所述左耳电极连接左耳测量部件，所述右耳电极连接右耳测量部件，以及所述模式选择开关连接颈部测量部件；所述左耳电极、右耳电极、颈部电极分别连接至对应的前置放大器的正极以及威尔逊网络电路，所述威尔逊网络电路的中心电端分别连接至三个电极的前置放大器的负极，所述三个电极分别对应的前置放大器连接至所述处理器；所述威尔逊网络电路的中心电端还连接至所述共模放大器的负极；
    所述模块选择开关用于连接至所述颈部电极，以开启多导联测量模式。
  12. 根据权利要求10或11所述的装置，其特征在于，所述信号获取模块用于：
    测量所述左耳电极和右耳电极之间的信号，得到Ⅰ导联信号；
    测量所述右耳电极和所述颈部电极之间的信号，得到Ⅱ导联信号；
    测量所述左耳电极和颈部电极之间的信号，得到Ⅲ导联信号；
    根据所述Ⅰ导联信号、所述Ⅱ导联信号和所述Ⅲ导联信号，得到aVR导联信号、aVL导联信号和avF导联信号。
  13. 根据权利要求12所述的装置，其特征在于，所述aVR导联信号满足：aVR导联＝RE-0.5*(LE+N)；
    所述aVL导联信号满足：aVL导联＝LE-0.5*(N+RE)，以及
    所述avF导联信号满足：avF导联＝N-0.5*(LE+RE)；
    其中，RE为右耳电极信号，LE为左耳电极信号，N为颈部电极信号。
  14. 如权利要求10～13任一项所述的装置，其特征在于，所述特征提取模块，用于获 取所述多导联信号的平均值；以及根据所述多导联信号中每个导联的信号以及所述多导联信号的平均值，获得所述每个导联的信号对应的相关系数作为所述每个导联的信号的特征。
  15. 如权利要求10～14中任一项所述的装置，其特征在于，所述信号质量获取模块，用于根据所述每个导联的信号对应的相关系数，获取所述多导联信号对应的相关系数的平均值，作为多导联信号的质量；
    所述输出模块，用于若所述多导联信号对应的相关系数的平均值大于所述第一阈值，或所述加速度信号小于或等于第二阈值，则输出所述多导联信号的特征；
    所述模式选择开关用于若所述多导联信号对应的相关系数的平均值小于或等于所述第一阈值，且所述加速度信号大于或等于第三阈值，则切换到带右腿驱动的单导联模式。
  16. 根据权利要求10～15中任一项所述的装置，其特征在于，所述装置还包括：
    信号筛选模块，用于筛选所述多导联信号中信号大于第四阈值的信号；
    所述特征提取模块，用于提取所述筛选出的信号的特征。
  17. 根据权利要求11～16中任一项所述的装置，其特征在于，所述模式选择开关用于若所述多导联信号小于或等于所述第一阈值，且所述用户处于运动状态，切换至所述右腿驱动电极，开启单导联模式；
    所述信号获取模块，用于根据所述左耳电极、所述右耳电极和所述中心电端的信号，获取所述单导联信号；
    所述共模信号消除模块，用于根据所述中心电端的信号和基准电平信号，经过所述右腿驱动电极的负反馈，获取用户的共模信号，以及消除所述单导联信号中的共模信号。
  18. 根据权利要求15所述的装置，其特征在于，所述信号获取模块还用于获取加速度信号；
    所述装置还包括：
    确定模块，用于若所述加速度信号小于或等于所述第二阈值，确定所述用户处于静态；
    所述确定模块，还用于若所述加速度信号大于或等于所述第三阈值，确定所述用户处于运动状态。
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