WO2024103214A1 - 信号采集系统 - Google Patents

信号采集系统 Download PDF

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Publication number
WO2024103214A1
WO2024103214A1 PCT/CN2022/131703 CN2022131703W WO2024103214A1 WO 2024103214 A1 WO2024103214 A1 WO 2024103214A1 CN 2022131703 W CN2022131703 W CN 2022131703W WO 2024103214 A1 WO2024103214 A1 WO 2024103214A1
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Prior art keywords
electrode
signal
electrodes
acquisition system
physiological
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PCT/CN2022/131703
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English (en)
French (fr)
Inventor
周鑫
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Shenzhen Shokz Co Ltd
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Shenzhen Shokz Co Ltd
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Priority to PCT/CN2022/131703 priority Critical patent/WO2024103214A1/zh
Priority to EP22965407.4A priority patent/EP4487777A4/en
Priority to CN202280092974.XA priority patent/CN118829397A/zh
Publication of WO2024103214A1 publication Critical patent/WO2024103214A1/zh
Priority to US18/908,863 priority patent/US20250025108A1/en
Anticipated expiration legal-status Critical
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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
    • A61B5/68—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
    • A61B5/6804—Garments; Clothes
    • 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
    • A61B5/68—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
    • 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
    • A61B5/6843—Monitoring or controlling sensor contact pressure
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/04—Constructional details of apparatus
    • A61B2560/0462—Apparatus with built-in sensors
    • A61B2560/0468—Built-in electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0219—Inertial sensors, e.g. accelerometers, gyroscopes, tilt switches
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/06—Arrangements of multiple sensors of different types
    • A61B2562/066—Arrangements of multiple sensors of different types in a matrix array

Definitions

  • This specification relates to the field of signal acquisition, and in particular to a signal acquisition system.
  • Signal acquisition systems which are widely used in the fields of physiological testing, disease diagnosis, experimental research, etc., can acquire data related to the user's physical condition by collecting physiological signals.
  • the signal acquisition system can detect and use the information of the electrocardiogram signal to reflect the working state of the human heart.
  • interference signals generated by some movement or shaking of the human body during the signal acquisition process often cause the collected physiological signals to contain motion artifacts, resulting in poor quality of the physiological signals and difficulty in accurately reflecting the user's physical condition. Therefore, it is hoped that a signal acquisition system can be proposed that can reduce the interference of motion artifacts and improve the quality of the collected physiological signals.
  • One of the embodiments of the present specification provides a signal acquisition system, including: a wearable body; a plurality of electrodes fixed to the wearable body and in contact with the user's skin, the plurality of electrodes including a first electrode group and a second electrode group, the first electrode group being used to collect physiological signals, and the second electrode group being used to collect detection signals; and a processing circuit for eliminating motion artifacts in the physiological signals based on the detection signals.
  • the first electrode group includes two first electrodes arranged at intervals
  • the second electrode group includes two second electrodes arranged respectively close to the two first electrodes
  • the physiological signal is a first physiological signal
  • the detection signal is a second physiological signal
  • the processor is used to eliminate motion artifacts in the first physiological signal based on the second physiological signal.
  • the conductivity of the materials of the two second electrodes is different.
  • the two second electrodes are raised relative to the user's skin at different heights in a direction perpendicular to the user's skin surface.
  • the hardness of the materials of the two second electrodes is different, or the corrugation degrees of the materials of the two second electrodes are different.
  • the areas of the two second electrodes are different.
  • the first electrode group includes two first electrodes arranged at intervals, and the second electrode group includes a second electrode arranged close to one of the two first electrodes, wherein the second electrode and the first electrode close thereto are used to collect detection signals.
  • each second electrode is less conductive than the material of its corresponding first electrode.
  • a protrusion of each second electrode relative to the wearable body is smaller than a height of a protrusion of the corresponding first electrode relative to the wearable body in a direction perpendicular to the user's skin surface.
  • the second material of each second electrode is harder than the first material of the corresponding first electrode, or the second material of each second electrode is more wrinkled than the first material of the corresponding first electrode.
  • the area of each second electrode in contact with the skin is smaller than the area of the corresponding first electrode in contact with the skin.
  • the first electrode group includes two first electrodes arranged at intervals
  • the second electrode group includes two second electrodes arranged respectively close to the two first electrodes
  • the detection signal is a detection signal reflecting the contact impedance between the two first electrodes and the user's skin.
  • an excitation source electrically connected to the two second electrodes is further included, and the excitation source is used to provide an excitation signal.
  • the frequency of the physiological signal is in the range of 20 Hz-400 Hz, and the frequency of the excitation signal is not less than 250 Hz.
  • the difference between the frequency of the excitation signal and any integer multiple of 50 Hz is not less than 1 Hz; or, the difference between the frequency of the excitation signal and any integer multiple of 60 Hz is not less than 1 Hz.
  • the frequency of the excitation signal is higher than the frequency range of the physiological signal.
  • the detection signal and the physiological signal are collected separately in different time periods.
  • a minimum distance between an edge of each second electrode and an edge of a corresponding first electrode is less than 10 cm.
  • each second electrode is respectively connected to a first electrode by an inelastic connection, and the ratio of the difference in distance between the second electrode and the corresponding first electrode on a surface parallel to the skin surface to the movable distance of the corresponding first electrode on a surface parallel to the skin surface is not greater than 50%.
  • the processing circuit is configured to:
  • the motion artifacts in the physiological signals are eliminated according to the detection signals.
  • an inertial sensor is further included.
  • the inertial sensor is disposed on a side of the first electrode group facing away from the user's skin and is used to measure motion artifacts of the first electrode group.
  • One of the embodiments of the present specification also provides a signal acquisition system, including: a wearable body; a plurality of electrodes fixed to the wearable body and in contact with the user's skin, the plurality of electrodes including two electrodes arranged at intervals to collect physiological signals; an excitation source electrically connected to the two electrodes, the excitation source being used to provide an excitation signal to generate a detection signal reflecting the contact impedance between the two electrodes and the user's skin; and a processing circuit for eliminating motion artifacts in the physiological signal based on the detection signal.
  • the frequency of the physiological signal is in the range of 20 Hz-400 Hz, and the frequency of the excitation signal is not less than 250 Hz.
  • the difference between the frequency of the excitation signal and any integer multiple of 50 Hz is not less than 1 Hz; or, the difference between the frequency of the excitation signal and any integer multiple of 60 Hz is not less than 1 Hz.
  • the frequency of the excitation signal is higher than the frequency range of the physiological signal.
  • the detection signal and the physiological signal are collected separately in different time periods.
  • FIG1 is a block diagram of an exemplary signal acquisition system according to some embodiments of the present specification.
  • FIG2 is a schematic diagram of an exemplary signal acquisition system according to some embodiments of the present specification.
  • FIG3 is a schematic diagram of an exemplary signal acquisition system according to some embodiments of the present specification.
  • FIG4 is a schematic diagram of the structure of an exemplary signal acquisition system according to some embodiments of this specification.
  • FIG5 is a schematic diagram of the structure of an exemplary signal acquisition system according to still other embodiments of this specification.
  • FIG6 is a block diagram of an exemplary signal acquisition system according to some embodiments of the present specification.
  • FIG7A is a schematic diagram of the fluctuation relationship between contact impedance and electromyographic signal according to some embodiments of this specification.
  • FIG. 7B is a schematic diagram of the fluctuation relationship between contact impedance and electromyographic signal shown in some embodiments of this specification.
  • FIG. 8 is a block diagram of an exemplary signal acquisition system according to some embodiments of the present specification.
  • system means for distinguishing different components, elements, parts, portions or assemblies at different levels.
  • device means for distinguishing different components, elements, parts, portions or assemblies at different levels.
  • unit means for distinguishing different components, elements, parts, portions or assemblies at different levels.
  • the words can be replaced by other expressions.
  • words “first”, “second” and similar words used in the specification and claims of this application do not indicate any order, quantity or importance, but are only used to distinguish different components. Similarly, words such as “one” or “an” do not indicate a quantitative limitation, but rather indicate the presence of at least one. Unless otherwise indicated, words such as “front”, “rear”, “lower” and/or “upper” are used for ease of description only and are not limited to one position or one spatial orientation. Generally speaking, the terms “comprises” and “comprising” only indicate the inclusion of clearly identified steps and elements, and these steps and elements do not constitute an exclusive list, and the method or device may also include other steps or elements.
  • the signal acquisition system may include a wearable body and a plurality of electrodes.
  • the electrode is fixed on the wearable body, and when the wearable body is worn on the user, the plurality of electrodes are in contact with the user's skin to collect the user's physiological signals through the electrodes.
  • the plurality of electrodes may include a first electrode group and a second electrode group, the first electrode group includes two first electrodes arranged at intervals to collect the first physiological signal, and the second electrode group includes two second electrodes arranged close to the two first electrodes to collect the second physiological signal.
  • the two groups of electrodes can collect differentiated first physiological signals and second physiological signals.
  • the first physiological signal may contain a real physiological signal and a motion artifact
  • the second physiological signal may contain a motion artifact and a small amount of real physiological signal
  • the second physiological signal only contains a motion artifact, wherein the motion artifact refers to the interference signal generated by the user's movement (for example, shaking of the head and/or limbs, etc.) during the signal acquisition process.
  • the second electrode is arranged close to the first electrode, the second electrode has motion consistency with the first electrode, so the physiological signals collected by the second electrode group and the first electrode group have a strong correlation.
  • the signal acquisition system may also include a processing circuit, which eliminates the motion artifact in the first physiological signal according to the second physiological signal to obtain the real physiological signal in the first physiological signal.
  • the signal acquisition system described in the embodiments of this specification can eliminate the motion artifact in the collected physiological signal as much as possible, so that the final obtained physiological signal has less interference and higher quality.
  • FIG1 is a block diagram of an exemplary signal acquisition system 100 according to some embodiments of the present specification.
  • the signal acquisition system 100 includes a wearable body 110, a first electrode group 12, a second electrode group 13, and a processing circuit 140.
  • the first electrode group 12 may include two first electrodes 120
  • the second electrode group 13 may include two second electrodes 130.
  • the wearable body 110 is used to be worn on the user.
  • the wearable body 110 can be a top (such as a T-shirt, a vest, a vest, a coat, etc.), which is worn on the upper body of the user.
  • the wearable body 110 can be a trousers (such as trousers, shorts, etc.), which is worn on the lower body of the user.
  • the wearable body 110 can also be a leg ring or a belt, which is worn on the legs or waist of the user respectively.
  • the wearable body 110 can also include a smart bracelet, smart shoes and socks, smart glasses, smart helmets, smart watches, smart backpacks, smart accessories, etc. or any combination thereof.
  • the electrode may refer to a circuit element used to contact other objects to input or output voltage (current).
  • the electrode e.g., the first electrode 120 in the first electrode group 12, the second electrode 130 in the second electrode group 13
  • the electrode may be in contact with the skin to collect physiological signals of the user.
  • Physiological signals are signals that can reflect the user's physical state.
  • physiological signals may include one or more signals such as breathing signals, electrocardiogram signals (ECG), electromyography signals, blood pressure signals, blood oxygen signals, and temperature signals.
  • ECG electrocardiogram signals
  • ECG electrocardiogram signals
  • electromyography signals blood pressure signals
  • blood oxygen signals blood oxygen signals
  • temperature signals During the collection of physiological signals, the electrodes may be fixed on the wearable body 110 and maintain contact with the user's skin.
  • the electrodes may be arranged on the wearable body 110 relative to various parts of the human body, such as the calf, thigh, waist, back, chest, shoulder, neck, etc.
  • multiple electrodes for collecting ECG signals can be set on the wearable body 110 at different distances from the user's heart (for example, the waist, back, chest, hands, etc. of the human body).
  • the two first electrodes 120 of the first electrode group 12 can be spaced apart in the waist area of the human body, and the two second electrodes 130 in the second electrode group 13 are respectively arranged close to the two first electrodes 120.
  • the wearable body 110 in order to improve the similarity of motion artifacts in the ECG signals collected by the two first electrodes (or second electrodes), the wearable body 110 can symmetrically fit the two first electrodes (or second electrodes) on both sides of the midsagittal plane of the human body.
  • One of the two first electrodes 120 collects a first potential, and the other first electrode 120 collects a second potential, and there is a first potential difference between the first potential and the second potential (the first potential difference can be used to generate a parameter reflecting the first ECG signal).
  • One of the two second electrodes 130 collects a third potential, and the other second electrode 130 collects a fourth potential. There is a second potential difference between the third potential and the fourth potential (the second potential difference can be used to reflect parameters of the second electrocardiogram signal).
  • multiple electrodes for collecting electromyographic signals can be set at positions with large muscle groups on the wearable body 110 (for example, the back, waist, legs, etc. of the human body).
  • the two first electrodes 120 of the first electrode group 12 can be set at intervals on a muscle, and the two second electrodes 130 in the second electrode group 13 are respectively set close to the two first electrodes 120.
  • the two first electrodes 120 and the two second electrodes 130 can be set in sequence along the length direction of the muscle fibers at this position. Different positions in the length direction of the muscle fibers have different potentials.
  • One of the two first electrodes 120 can collect the first potential, and the other first electrode 120 can collect the second potential.
  • first potential difference between the first potential and the second potential (the first potential difference can be used to generate a parameter reflecting the first electromyographic signal).
  • first potential difference can be used to generate a parameter reflecting the first electromyographic signal.
  • One of the two second electrodes 130 can collect the third potential, and the other second electrode 130 can collect the fourth potential.
  • second potential difference between the third potential and the fourth potential (the third potential difference can be used to generate a parameter reflecting the second electromyographic signal).
  • FIG2 is a schematic diagram of an exemplary signal acquisition system 100 according to some embodiments of the present specification.
  • the signal acquisition system 100 includes a wearable body 110, which is a top.
  • Two first electrodes 120 are arranged at intervals, and one of the two second electrodes 130 is arranged close to one of the two first electrodes 120.
  • the two first electrodes 120 and the two second electrodes 130 can be arranged at a position of the top corresponding to the chest of the human body.
  • FIG3 is a schematic diagram of an exemplary signal acquisition system 100 according to some embodiments of the present specification.
  • the wearable body 110 is a strap that is put on the lower leg of a human body.
  • a first electrode 120 and a second electrode 130 disposed close thereto may be disposed on one side of the strap along the length direction of the muscle fiber; another first electrode 120 and a second electrode 130 disposed close thereto may be disposed on the other side of the strap along the length direction of the muscle fiber.
  • the processing circuit 140 can be used to process signals.
  • the processing circuit 140 can be set independently of the wearable body 110, and multiple electrodes can be connected to the processing circuit 140 for communication.
  • the processing circuit 140 can be fixed on the wearable body 110.
  • the first electrode group 12 (two first electrodes 120) and the second electrode group 13 (two second electrodes 130) can be electrically connected to the processing circuit 140, and the processing circuit 140 receives the first potential and the second potential from the two first electrodes 120 and the third potential and the fourth potential from the two second electrodes 130.
  • the processing circuit 140 can differentially process the first potential and the second potential to obtain a first potential difference for characterizing a physiological signal (e.g., a first physiological signal).
  • the processing circuit 140 can differentially process the third potential and the fourth potential to obtain a second potential difference for characterizing a detection signal (e.g., a second physiological signal).
  • the processing circuit 140 can use the second physiological signal to perform differential processing on the first physiological signal to eliminate motion artifacts in the first physiological signal.
  • the ratio of the real physiological signal and the motion artifact in the first physiological signal can be different from the ratio of the real physiological signal and the motion artifact in the second physiological signal by differential design between multiple electrodes (for example, the first electrode 120 and the second electrode 130, and/or the two second electrodes 130), so as to eliminate the motion artifact in the first physiological signal according to the differentiated first physiological signal and the second physiological signal.
  • the electrode differential design please refer to Figures 4, 5 and other related descriptions in this specification.
  • the signal acquisition system 100 may further include an inertial sensor 150.
  • the inertial sensor 150 is used to measure the motion artifact of the first electrode group 12.
  • the inertial sensor 150 may be disposed on the first electrode group 12.
  • an inertial sensor 150 is disposed at any one of the two first electrodes 120 (for example, the side of the first electrode 120 facing away from the user's skin). At this time, it can be considered that the inertial sensor 150 and the first electrode 120 where it is located have a consistent motion state, so the motion signal detected by the inertial sensor 150 can represent the motion state of the first electrode 120 where it is located, and the detected motion signal can be used to characterize the motion artifact of the first electrode group 12.
  • an inertial sensor 150 may be respectively disposed at the two first electrodes 120 (for example, the side of each first electrode 120 facing away from the user's skin). At this time, the two inertial sensors 150 can respectively detect motion signals used to represent the motion state of the first electrode 120 where it is located. In some embodiments, the two motion signals detected by the two inertial sensors 150 can be processed (for example, averaged, weighted averaged, etc.) to obtain the motion artifact of the first electrode group 12.
  • the inertial sensor 150 may be electrically connected to the processing circuit 140.
  • the signal acquisition system 100 may include a first electrode group 12, an inertial sensor 150 disposed on a side of the first electrode group away from the user's skin, and a processing circuit 140.
  • the first electrode group 12 includes two first electrodes 120 arranged at intervals to collect physiological signals (i.e., first physiological signals); the inertial sensor 150 is used to measure the motion signal of the first electrode group 12 as the motion artifact of the first electrode group 12; the processing circuit 140 is used to eliminate the motion artifact in the physiological signal collected by the first electrode group 12 according to the motion signal measured by the inertial sensor 150.
  • the processing circuit 140 can eliminate the motion artifact in the motion signal by pre-processing the motion signal and the physiological signal (for example, normalizing the motion signal and the physiological signal) and then performing differential processing. For another example, by preprocessing the motion signal and the physiological signal, performing principal component analysis on both the motion signal and the physiological signal, then removing the principal component of the motion signal from the physiological signal, and reconstructing it, the motion artifact in the motion signal can be eliminated.
  • the information acquisition system 100 may include a first electrode group 12, a second electrode group 13, an inertial sensor 150 disposed on the side of the first electrode group away from the user's skin, and a processing circuit 140.
  • the processing circuit 140 is used to determine the confidence of the second physiological signal for eliminating the motion artifact in the first physiological signal based on the motion signal measured by the inertial sensor 150. For example, a threshold value may be preset in the processing circuit 140.
  • the processing circuit 140 may perform differential processing on the first physiological signal according to the second physiological signal to eliminate the motion artifact in the first physiological signal; if the difference between the motion signal and the second physiological signal exceeds the preset threshold value, it is considered that the confidence of the second physiological signal is low, and the processing circuit 140 may send an instruction to reacquire the second physiological signal to the second electrode group 13.
  • the processing circuit 140 may perform differential processing on the first physiological signal according to the motion signal measured by the inertial sensor 150 (as described above, pre-processing is performed first and then differential processing is performed) to eliminate the motion artifact in the first physiological signal.
  • the signal acquisition system 100 may include a plurality of first electrode groups 12 and a plurality of second electrode groups 13.
  • the plurality of first electrode groups 12 and the plurality of second electrode groups 13 are respectively fixed on the wearable body 110 corresponding to different parts of the human body to collect physiological signals of different parts of the user's body.
  • the technical solution of using the inertial sensor 150 can be applied to other embodiments of this specification, for example, it can be applied to the signal acquisition system 100 shown in Figures 4 and 5, the signal acquisition system 300 shown in Figure 6, and the signal acquisition system 400 shown in Figure 8.
  • differentiated first physiological signals and second physiological signals can be obtained by differential design between multiple electrodes (for example, differentiation between the first electrode 120 and the second electrode 130 or differential design between the two second electrodes 130).
  • the differentiated design of electrodes will be exemplarily described below in conjunction with Figures 4 and 5.
  • Figure 4 is a structural schematic diagram of an exemplary signal acquisition system 100 according to some embodiments of this specification.
  • Figure 5 is a structural schematic diagram of an exemplary signal acquisition system 100 according to some other embodiments of this specification. As shown in Figures 4 and 5, multiple electrodes can be fixed on the side of the wearable body 110 close to the user's skin and can contact the skin.
  • the two first electrodes 120 can be spaced apart, and the two second electrodes 130 can be respectively arranged close to the first electrodes 120.
  • the two first electrodes 120 and the two second electrodes 130 can be arranged side by side, and the two second electrodes 130 can be located on opposite sides of the two first electrodes 120.
  • the two second electrodes 130 can be located between the two first electrodes 120.
  • one of the second electrodes 130 may be located between the two first electrodes 120, and the other second electrode 130 may be located on the side of the first electrode 120 close to it and away from the other first electrode 120.
  • the two first electrodes 120 and/or the two second electrodes 130 are not limited to being arranged side by side as shown in Figures 4 and 5, but may also be arranged in other ways.
  • the two first electrodes 120 may be separately arranged in any separation manner on a surface parallel to the skin surface, and the second electrode 130 arranged close to each first electrode 120 may be arranged at any position around the first electrode 120 at a certain distance, and this specification does not limit this.
  • the distance between the second electrode 130 and the corresponding first electrode 120 refers to the minimum distance between the edge of the second electrode 130 and the edge of the corresponding first electrode 120.
  • the distance between the second electrode 130 and the corresponding first electrode 120 can refer to dimension a, that is, the minimum distance between the edges of the second electrode 130 and the first electrode 120 close to each other.
  • the certain distance can be less than 10 cm.
  • the certain distance can be less than 8 cm.
  • the certain distance can be less than 6 cm.
  • the "corresponding" mentioned here refers to two first electrodes 120 and second electrodes 130 that are arranged close to each other. That is, if a first electrode 120 and a second electrode 130 are arranged close to each other, the first electrode 120 can be called the first electrode corresponding to the second electrode 130, and the second electrode 130 can also be called the second electrode corresponding to the first electrode 120.
  • the second electrode 130 and the corresponding first electrode 120 can be physically connected.
  • the physical connection described in this specification refers to a physical connection achieved through a structure, material or a composite structural material.
  • the physical connection mentioned here is an insulating connection.
  • the second electrode 130 and the corresponding first electrode 120 can be connected through an insulating structure (for example, a silicone layer).
  • any position of the second electrode 130 (for example, a side, a side edge or a local area on the surface, etc.) can be physically connected to any position of the first electrode 120 (for example, a side, a side edge or a local area on the surface, etc.).
  • the second electrode 130 and the corresponding first electrode 120 in order to enhance the movement consistency of the second electrode 130 and the corresponding first electrode 120, can be non-elasticly connected (or rigidly connected).
  • the ratio of the distance difference between each second electrode 130 and the corresponding first electrode 120 on the surface parallel to the skin surface to the movable distance of the corresponding first electrode 120 on the surface parallel to the skin surface may be no greater than 50%.
  • the first electrode group 12 and the second electrode group 13 may move on the skin surface.
  • the ratio of the distance difference between each second electrode 130 and the corresponding first electrode 120 on the surface parallel to the skin surface to the movable distance of the corresponding first electrode 120 on the surface parallel to the skin surface may be no greater than 45%.
  • the ratio of the distance difference between each second electrode 130 and the corresponding first electrode 120 on the surface parallel to the skin surface to the movable distance of the corresponding first electrode 120 on the surface parallel to the skin surface may be no greater than 40%.
  • the first electrode 120 and the second electrode 130 may be designed differently to enhance the difference between the first physiological signal and the second physiological signal.
  • each second electrode 130 is less conductive than the material of the corresponding (e.g., physically connected) first electrode 120. In this way, the proportion of the real physiological signal in the first physiological signal collected by the first electrode group 12 is greater than the proportion of the real physiological signal in the second physiological signal collected by the second electrode group 13.
  • the real physiological signal in the second physiological signal collected by the second electrode group 13 can be small enough to be ignored, so the second physiological signal can be considered to contain only motion artifacts.
  • the impedance of the first electrode 120 is several thousand ohms, and the impedance of the material of the first electrode 120 and the impedance of the material of the second electrode 130 differ by more than 1M ohm, and the component of the motion artifact signal in the second physiological signal collected by the second electrode group 13 becomes significantly more; when the impedance of the material of the first electrode 120 and the impedance of the material of the second electrode 130 differ by more than 100M ohms, the second physiological signal collected is mainly motion artifacts.
  • the electrode can be an electrode composed of a single material, such as a metal fabric electrode, a conductive silicon electrode, a hydrogel electrode, a metal electrode, etc.
  • the material of each first electrode 120 can be a metal fabric
  • the material of the corresponding second electrode 130 can be conductive silicon
  • the metal fabric electrode has a smaller resistivity and a stronger conductivity.
  • the difference in electrode materials not only affects the impedance of the electrode itself, but also affects the contact impedance between the electrode and the skin.
  • the material of each first electrode 120 may be a hydrogel
  • the material of the corresponding second electrode 130 may be conductive silicon. Compared with conductive silicon, hydrogel is more skin-friendly and keeps moist. Therefore, the contact impedance of the first electrode 120 relative to the corresponding second electrode 130 is smaller and the conductivity is stronger.
  • the difference in electrode materials will also affect the potential strength of the stratum corneum. For example, the absolute value of the half-cell potential of the silver chloride material is smaller than that of the silver material, and its stratum corneum potential is smaller.
  • the differentiation of the first electrode 120 and the second electrode 130 can be achieved by different thicknesses of the same material.
  • the thickness of the metal fabric electrode is within a certain range, the greater the thickness, the smaller its impedance and the contact impedance between the skin, and the better the conductivity.
  • the material of each first electrode 120 and the material of the corresponding second electrode 130 can both be metal fabrics, but the thickness of the material of the first electrode 120 in the direction perpendicular to the skin (see the A direction shown in Figures 4 and 5) is greater than the thickness of the material of the corresponding second electrode 130 in the A direction.
  • the material of the first electrode 120 and the corresponding material of the second electrode 130 may both be conductive silicon, but the thickness of the material of the first electrode 120 is greater than the thickness of the material of the corresponding second electrode 130.
  • the material of the first electrode 120 and/or the material of the corresponding second electrode 130 may be a combination of different materials (e.g., stacked, combined, etc.).
  • the material of the first electrode 120 and the material of the corresponding second electrode 130 are both composed of metal fabric and conductive silicon material, the thickness of the metal fabric in the material of the first electrode 120 is less than the thickness of the metal fabric in the material of the corresponding second electrode 130, and the thickness of the conductive silicon material in the material of the first electrode 120 is greater than the thickness of the conductive silicon material in the material of the corresponding second electrode 130.
  • the electrode can be fixed to the wearable body 110 by gluing, snapping, Velcro, sewing, pressing, etc., and the electrode may have a protrusion relative to the wearable body 110 in the direction toward the skin surface.
  • the height of each second electrode 130 relative to the wearable body 110 in the direction perpendicular to the user's skin surface, can be less than the height of the corresponding first electrode 120 relative to the wearable body 110.
  • the "protrusion" of the electrode in this specification refers to the part of the electrode that exceeds the surface 111 of the wearable body 110 close to the skin; the height of the protrusion refers to the height of the part of the electrode that exceeds the surface 111 of the wearable body 110 close to the skin in the direction perpendicular to the user's skin surface.
  • the height of each first electrode 120 relative to the wearable body 110 in the direction perpendicular to the skin surface i.e., direction A
  • the height of the corresponding second electrode 130 relative to the wearable body 110 in the direction perpendicular to the skin surface i.e., direction A
  • the height b of each second electrode 130 relative to the protrusion of the wearable body 110 along the direction perpendicular to the skin surface can be less than the height c of the corresponding first electrode 120 relative to the protrusion of the wearable body 110 along the direction perpendicular to the skin surface (i.e., direction A).
  • the first electrical signal collected by the first electrode group 12 is different from the second electrical signal collected by the second electrode group 13.
  • the difference between the height b of the protrusion of the second electrode 130 and the height c of the protrusion of the corresponding first electrode 120 is greater than a certain height threshold (e.g., 5%)
  • the first electrical signal collected by the first electrode group 12 and the second electrical signal collected by the second electrode group 13 are significantly different, so the second physiological signal can be considered to contain only motion artifacts.
  • the second physiological signal can be used to perform differential processing on the first physiological signal to eliminate motion artifacts in the first physiological signal, reduce the interference of motion artifacts in the first physiological signal, and obtain a high-quality physiological signal.
  • the height of the protrusion of each first electrode 120 can be in the range of 1mm-10cm, and the corresponding height of the protrusion of the second electrode 130 can be in the range of 0mm-5mm.
  • the material of each second electrode 130 may be different from the material of the corresponding first electrode 120.
  • the material of each second electrode 130 may be harder than the material of the corresponding first electrode 120, so that the corresponding first electrode 120 fits better to the user's skin than the second electrode 130, so that the proportion of the real physiological signal in the second physiological signal is less than that of the first physiological signal (i.e., the proportion of the motion artifact in the second physiological signal is greater than that of the first physiological signal).
  • the material of each second electrode 130 may be more wrinkled than the material of the corresponding first electrode 120, so that the corresponding first electrode 120 fits better to the user's skin than the second electrode 130, so that the proportion of the real physiological signal in the second physiological signal is less than that of the first physiological signal (i.e., the proportion of the motion artifact in the second physiological signal is greater than that of the first physiological signal). It should be understood that the hardness or wrinkle degree of the material is a comparison measured under the same measurement method or the same measurement standard.
  • differentiated first physiological signals and second physiological signals can be generated by the difference in contact impedance between the first electrode group 12 and the second electrode group 13 and the skin.
  • differentiated contact impedance can be generated between the first electrode group 12 and the second electrode group 13 by the difference in the area of each first electrode 120 and the corresponding second electrode 130 contacting the skin.
  • the first electrode 120 and the skin contact surface for example, the B surface shown in FIG. 4
  • the corresponding second electrode 130 and the skin contact surface for example, the C surface shown in FIG.
  • each second electrode 130 can have a second area, and the second area of each second electrode 130 can be smaller than the first area of the corresponding first electrode 120, so that the contact impedance between the first electrode 120 and the skin is smaller than the contact impedance between the corresponding second electrode 130 and the skin.
  • the proportion of real physiological signals in the first physiological signal collected by the first electrode group 12 is greater than that of the second physiological signal collected by the second electrode group 13, and at the same time, the proportion of motion artifacts in the second physiological signal is greater than that of the first physiological signal.
  • the B surface of the first electrode 120 or the C surface of the second electrode 130 can be a rectangle or a rounded rectangle.
  • the area of the first electrode 120 contacting the skin (for example, the B surface shown in FIG. 4) can be in the range of 1 cm 2 -100 cm 2 ; the area of the second electrode 130 contacting the skin (for example, the C surface shown in FIG. 4) can be in the range of 0.5 cm 2 -50 cm 2.
  • the shape of the B surface of the first electrode 120 or the C surface of the second electrode 130 can also be a circle, a triangle, a hexagon or other regular or irregular shapes.
  • the shape of the B surface or the C surface can depend on the shape of the part to be collected for physiological signals.
  • a structure with a specific pattern or a fold structure can be arranged on the C surface of each second electrode 130 to reduce the fit of the second electrode 130 to the skin, and at the same time reduce the area of the second electrode 130 contacting the skin, so as to achieve the purpose of being distinguished from the first electrode 120.
  • the signal acquisition system 100 including four electrodes shown in Figures 1-3 is only an example and is not intended to limit the number of electrodes in the signal acquisition system 100.
  • the number of electrodes in the signal acquisition system 100 can be any number that can obtain differentiated motion signals and physiological signals, and is not limited here.
  • the first electrode group 12 may include two first electrodes 120
  • the second electrode group 13 may include only one second electrode 130 (that is, the signal acquisition system 100 includes 3 electrodes).
  • the two first electrodes 120 are used to obtain the first physiological signal
  • the second electrode 130 can be arranged close to one of the first electrodes 120 and form an electrode pair with the first electrode 120 for obtaining the second physiological signal.
  • the second electrode group 13 may include only one second electrode 130
  • the parameters such as the material, conductivity, protrusion relative to the wearable body, hardness, wrinkle degree, and skin contact area of the second electrode 130 and the corresponding first electrode 120 in the second electrode group may be the same as the corresponding parameters of each second electrode 130 and the corresponding first electrode 120 when the second electrode group 13 may include two second electrodes 130, which will not be repeated here.
  • the signal acquisition system 100 may also include a reference electrode for obtaining a reference signal.
  • the two first electrodes 120 are used to obtain a first physiological signal; the two second electrodes 130 can form an electrode pair with the two first electrodes 120 respectively to obtain a second physiological signal and a third physiological signal; the two second electrodes 130 can obtain a fourth physiological signal.
  • the signal acquisition system 100 including four electrodes can obtain four sets of differentiated electrical signals.
  • the first electrode group described in this specification includes two first electrodes 120 for example only, and the first electrode group may include more than two first electrodes 120.
  • the second electrode group may include the same number of second electrodes 130 as the first electrodes 120.
  • the first electrode group includes three first electrodes 120 for collecting physiological signals; the second electrode group includes three second electrodes 130 for collecting detection signals.
  • the first electrode group may include more than two first electrodes 120, and the second electrode group may include at least one second electrode 130.
  • the first electrode group may include three first electrodes 120 for collecting physiological signals; the second electrode group may include one second electrode 130 for being arranged close to one of the first electrodes 120 to collect detection signals.
  • the two second electrodes 130 in the second electrode group 13 may be the same.
  • each second electrode 130 may have the same conductivity, protrusion height, hardness, wrinkle degree, contact area with the skin, etc.
  • the two second electrodes 130 of the second electrode group 13 may be designed differently. When the two second electrodes 130 are different (for example, one or any combination of conductivity, protrusion height, hardness, wrinkle degree, contact area with the skin, etc.
  • the proportion of motion artifacts in the second physiological signal collected by the second electrode group 13 is greater than that in the second physiological signal collected by the same two second electrodes 130. Therefore, the differentiated first physiological signal and the second physiological signal can be obtained by the differentiated design of the two second electrodes 130 in the second electrode group 13, so as to reduce the interference of motion artifacts when the second physiological signal is used to eliminate the motion artifacts in the first physiological signal.
  • the differentiation between the two second electrodes 130 may be similar to the differentiated design between the first electrode 120 and the corresponding second electrode 130 described above.
  • the conductivity of the materials of the two second electrodes 130 may be different.
  • the two second electrodes 130 may be conductive silicon electrodes of different thicknesses.
  • the materials of the two second electrodes 130 may be conductive silicon electrodes and metal fabric electrodes, respectively.
  • the heights of the protrusions of the two second electrodes 130 relative to the wearable body 110 along the A direction may be different, so that the fit of the two second electrodes 130 relative to the user's skin is different.
  • the hardness of the materials of the two second electrodes 130 may be different, so that the fit of the two second electrodes 130 relative to the user's skin is different.
  • the degree of wrinkling of the materials of the two second electrodes 130 may be different, so that the fit of the two second electrodes 130 relative to the user's skin is different.
  • the areas of contact between the two second electrodes 130 and the skin may be different, so that the contact impedance between the two second electrodes 130 and the skin is different.
  • the signal acquisition system 100 may further include an inertial sensor 150.
  • the inertial sensor 150 is disposed on the side of the first electrode 120 away from the user's skin so that the first electrode 120 and the inertial sensor 150 have a consistent motion state.
  • FIG. 4 and FIG. 5 are only two embodiments of the signal acquisition system 100 and are not used to limit the structure of the signal acquisition system 100.
  • the signal acquisition system 100 may include a first electrode group 12, an inertial sensor 150 disposed on the side of the first electrode group 12 away from the user's skin, and a processing circuit 140 (i.e., excluding the second electrode group 13).
  • a processing circuit 140 i.e., excluding the second electrode group 13
  • the information acquisition system 100 may include a first electrode group 12, a second electrode group 13, an inertial sensor 150 disposed on the side of the first electrode group away from the user's skin, and a processing circuit 140.
  • the inertial sensor 150 please refer to the relevant description of FIG. 1 .
  • the signal acquisition system 100 may include a first electrode group 12, a second electrode group 13, and a processing circuit 140 (i.e., excluding the inertial sensor 150).
  • FIG6 is a block diagram of an exemplary signal acquisition system 300 according to some embodiments of the present specification.
  • the signal acquisition system 300 may include a wearable body 310, a first electrode group 32, a second electrode group 33, and a processing circuit 340.
  • the first electrode group 12 may include two first electrodes 320.
  • the second electrode group 13 may include two second electrodes 330.
  • the functions and structural distributions of the wearable body 310 and the first electrode 320 shown in FIG6 may be similar to the wearable body 110 and the first electrode 120 described in FIG1-5, respectively, and are not repeated here.
  • the difference between the signal acquisition system 300 of FIG6 and the signal acquisition system 100 described in FIG1-5 lies in the function and structural distribution of the second electrode 330.
  • the second electrode 330 is used to collect a detection signal reflecting the contact impedance between the two first electrodes 320 and the user's skin, and accordingly, the processing circuit 340 is used to eliminate the motion artifact in the physiological signal according to the detection signal (for example, the detection signal and the physiological signal can be connected to the circuit, processed in an analog circuit, or processed in a digital circuit, or processed in an algorithm).
  • the second electrode 330 is used to collect a detection signal reflecting the contact impedance between the two second electrodes 330 and the user's skin.
  • each second electrode 330 can be set to be less than 10 cm from the edge of the corresponding first electrode 320.
  • each second electrode 330 can also be set to be connected to a first electrode 320 through a non-elastic connection, and the ratio of the distance difference between the movable distance of the second electrode 330 and the corresponding first electrode 320 on the surface parallel to the skin surface to the movable distance of the corresponding first electrode 320 on the surface parallel to the skin surface is not greater than 50%.
  • each second electrode 330 can be the same as the corresponding first electrode 320.
  • the material of each second electrode 330 and the material of the corresponding first electrode 320 can have the same conductivity.
  • the protrusion of each second electrode 330 relative to the wearable body 310 may be the same as the height of the protrusion of the corresponding first electrode 320 in the direction perpendicular to the user's skin.
  • the hardness and/or wrinkle degree of the material of each second electrode 330 may be the same as the hardness and/or wrinkle degree of the corresponding first electrode 320.
  • the contact area between each second electrode 330 and the skin may be the same as the contact area between the corresponding first electrode 320 and the skin. In this way, the motion consistency between the first electrode 320 and the second electrode 330 is as consistent as possible with the contact impedance of the skin, and the detection signal of the contact impedance between the two second electrodes 330 and the user's skin collected by the two second electrodes 330 can be used to reflect the detection signal of the contact impedance between the two first electrodes 320 and the user's skin.
  • the processing circuit 340 can differentially process the signals collected by the two first electrodes 320 to obtain a physiological signal, differentially process the signals collected by the two second electrodes 330 to obtain a detection signal, and eliminate the motion artifacts in the physiological signal according to the detection signal.
  • the signal acquisition system 300 further includes an excitation source 370 electrically connected to the two second electrodes 330.
  • the excitation source 370 can be used to provide an excitation signal to generate a detection signal reflecting the contact impedance between the first electrode group 32 and the human body.
  • the excitation source 370 can be an AC excitation source, a DC excitation source, or a combination of the two.
  • the excitation signal can be understood as forming a closed loop after flowing through the human body through the second electrode 330.
  • the detection signal can correspond to the voltage division of the contact impedance between the second electrode group 33 and the human body in the closed loop.
  • FIG. 7A is a schematic diagram of the fluctuation relationship between the contact impedance and the electromyographic signal according to some embodiments of the present specification
  • FIG. 7B is a schematic diagram of the fluctuation relationship between the contact impedance and the electromyographic signal shown in some embodiments of the present specification.
  • the value of the contact impedance will produce relevant fluctuations with movement (for example, the value of the contact impedance will increase with the increase of the electromyographic signal, and will also decrease with the decrease of the electromyographic signal).
  • motion artifacts can be obtained according to the contact impedance, and the obtained motion artifacts (for example, motion artifacts characterized by the detection signal reflecting the contact impedance between the first electrode group 32 and the user's skin collected by the second electrode group 33) can be used to eliminate the motion artifacts in the physiological signals collected by the first electrode group 32.
  • the contact impedance can be subjected to frequency analysis to obtain the main frequency of the motion artifact, and the contact impedance can also be subjected to amplitude analysis (for example, fluctuation value/nearby average value, etc.) to obtain the intensity information of the motion artifact.
  • the excitation source 370 may be a circuit element that provides electrical energy. In some embodiments, the excitation source 370 may provide an excitation signal of a first frequency to generate a detection signal reflecting the contact impedance between the second electrode 330 and the human body. In some embodiments, the excitation source 370 may be a current source or a voltage source. It should also be noted that the setting of the intensity of the excitation source 370 also needs to consider the safe voltage or safe current of the human body to ensure the safety of the human body, and the intensity of the excitation source 370 should not be too high. In some embodiments, the current intensity of the excitation source 370 may be less than 1mA. Further, in some embodiments, the current intensity of the excitation source 370 may be less than 100 ⁇ A. Further, in some embodiments, the current intensity of the excitation source 370 may be 10 ⁇ A.
  • the number of excitation sources 370 may be one, and it may be connected to the plurality of second electrodes 330 through a plurality of branches to provide excitation signals to the plurality of second electrodes 330, wherein each branch may be provided with a second electrode 330. In some embodiments, there may be a plurality of excitation sources 370, and each excitation source 370 may be connected to one or more second electrodes 330, respectively, to provide an excitation signal to each second electrode 330.
  • the excitation source 370 can simultaneously generate multiple excitation signals with different frequencies, and can provide multiple second electrodes 330 with excitation signals with the same frequency or different frequencies, thereby generating detection signals with different frequencies.
  • the excitation source 370 can provide multiple second electrodes 330 with excitation signals of different frequencies to collect different detection signals.
  • the detection signals of different frequencies corresponding to the multiple second electrodes 330 can be used to reflect the body composition information of the human body, such as body fat percentage, bone density, body fluid content, and other body composition information.
  • the excitation source 370 can provide a second excitation signal of a second frequency different from the first frequency to generate a second detection signal.
  • the second detection signal can reflect the impedance information on the closed loop formed between the second electrode 330 and the human body at the second frequency, including the contact impedance between the second electrode 330 and the human body and the impedance of the human tissue on the closed loop.
  • body composition information of a human body can be determined using a first detection signal generated by a first excitation signal (e.g., an excitation signal having a first frequency) and a second detection signal generated by a second excitation signal.
  • the excitation signal may be a voltage signal or a current signal.
  • the excitation signal may be an AC signal having a first frequency, so that the generated detection signal also has the first frequency.
  • the first frequency may be set in a frequency range that is less susceptible to external interference (e.g., power frequency interference) and less interferes with physiological signals.
  • the frequency of the excitation signal can be set according to the frequency range of the physiological signal. In some embodiments, the frequency of the excitation signal can be higher than the frequency range of the physiological signal to avoid most of the frequency bands where the physiological signal is located and reduce the mutual interference between the physiological signal and the excitation signal. In some embodiments, the excitation frequency may be not less than 850Hz. For example, the excitation frequency may be not less than 400Hz.
  • the excitation signal for example, the excitation signal with a frequency of not less than 400Hz
  • the excitation signal can tolerate a small part of the physiological signal (such as a physiological signal with a frequency of 400Hz to 850Hz).
  • the frequency of the physiological signal for example, the electromyographic signal
  • the frequency of the excitation signal provided by the excitation source 370 can be greater than 250Hz.
  • the frequency of the excitation source can also avoid the frequency range where the power frequency noise is located.
  • the difference between the frequency of the excitation signal provided by the excitation source 370 and any integer multiple of 50 Hz or 60 Hz may be not less than 1 Hz, or the difference between the frequency of the excitation signal provided by the excitation source 370 and any integer multiple of 50 Hz or 60 Hz may be not less than 2%.
  • the frequency of the excitation signal provided by the excitation source 370 may be above 400 Hz, such as 460 Hz, 640 Hz, 830 Hz, etc.
  • the setting of the frequency of the excitation signal provided by the excitation source 370 also needs to be considered in combination with the sampling frequency of the processing circuit 340.
  • the sampling frequency may be at least 2 times or more of the frequency of the excitation signal provided by the excitation source 370.
  • the sampling frequency may be 4 times or more of the frequency of the excitation signal provided by the excitation source 370.
  • the frequency of the excitation signal provided by the excitation source 370 can be set within the range of 250 Hz to 2000 Hz.
  • the signal acquisition system 300 can collect physiological signals and detection signals respectively in different time periods.
  • the signal acquisition system 300 can collect physiological signals in a first time period.
  • the signal acquisition system 300 can collect detection signals in a second time period.
  • the signal acquisition system 300 may include a switch circuit, which can be used to control the conduction state of the first electrode group and the processing circuit 340, and can also be used to control the conduction state of the second electrode group and the excitation source 370, so that only the first electrode group and the processing circuit 340 are kept in an electrically conductive state at the same time, or only the second electrode group and the excitation source 370 are kept in an electrically conductive state.
  • the signal acquisition system 300 can collect physiological signals and detection signals at the same time, and transmit them to different processing circuits through different transmission channels to avoid mutual interference between signals.
  • FIG8 is a block diagram of an exemplary signal acquisition system 400 according to some embodiments of the present specification.
  • the signal acquisition system 400 may include a wearable body 410, two electrodes 420, a processing circuit 440, and an AC excitation source 470.
  • the wearable body 410, the processing circuit 440, and the AC excitation source 470 shown in FIG8 are similar to the wearable body 310 and the processing circuit 340 shown in FIG6 , and are not described in detail here.
  • the signal acquisition system 400 of FIG8 includes only one set of electrodes (two electrodes 420), and the two electrodes 420 can collect both physiological signals and detection signals reflecting the contact impedance between the two electrodes 420 and the skin;
  • the excitation source in the signal acquisition system 400 is an AC excitation source 470, while the excitation source in the signal acquisition system 300 can be an AC excitation source, a DC excitation source, or a combination of the two.
  • the two electrodes 420 for collecting physiological signals and detection signals can be fixed to the wearable body 410 and contact the user's skin.
  • the AC excitation source 470 is electrically connected to the two electrodes 420.
  • the AC excitation source 470 is used to provide an excitation signal to generate a detection signal reflecting the contact impedance between the two electrodes 420 and the human body.
  • the excitation signal can be understood as a closed loop formed after flowing through the human body through the electrode 420.
  • the detection signal can correspond to the voltage division of the contact impedance between the electrode 420 and the human body in the closed loop.
  • the value of the contact impedance will produce relevant fluctuations with movement (for example, the value of the contact impedance will increase with the increase of the electromyographic signal, and will also decrease with the decrease of the electromyographic signal). Therefore, the motion artifact can be obtained according to the contact impedance, that is, the obtained motion artifact (for example, the motion artifact characterized by the detection signal reflecting the contact impedance between the two electrodes 420 and the user's skin collected by the two electrodes 420) can be used to eliminate the motion artifact in the physiological signal collected by the two electrodes 420.
  • the obtained motion artifact for example, the motion artifact characterized by the detection signal reflecting the contact impedance between the two electrodes 420 and the user's skin collected by the two electrodes 420
  • the frequency of the physiological signal collected by the signal acquisition system 400 shown in Figure 8, the frequency of the excitation signal, etc. can be similar to that of the signal acquisition system 300 shown in Figure 6, and will not be repeated here. Since the physiological signal and the detection signal are collected by the same set of electrodes, the signal acquisition system 400 can collect the physiological signal and the detection signal respectively in different time periods. Exemplarily, the signal acquisition system 400 can collect the physiological signal in a first time period. The signal acquisition system 400 can collect the detection signal in a second time period.
  • the signal acquisition system 400 may include a switching circuit, which can be used to control the conduction state of the two electrodes 420 and the processing circuit 440, and can also be used to control the conduction state of the two electrodes 420 and the excitation source 370, so that the two electrodes 420 and the processing circuit 440 maintain an electrically conductive state at the same time, or the two electrodes 420 and the AC excitation source 470 maintain an electrically conductive state.
  • a switching circuit which can be used to control the conduction state of the two electrodes 420 and the processing circuit 440, and can also be used to control the conduction state of the two electrodes 420 and the excitation source 370, so that the two electrodes 420 and the processing circuit 440 maintain an electrically conductive state at the same time, or the two electrodes 420 and the AC excitation source 470 maintain an electrically conductive state.
  • the above description of the signal acquisition system is only an exemplary description and does not limit this specification to the scope of the embodiments.
  • Different embodiments may produce different beneficial effects.
  • the beneficial effects that may be produced may be any one or a combination of the above, or any other possible beneficial effects.
  • the present specification has the following technical effects: (1) Through the differentiated design of the first electrode group and the second electrode group, the physiological signals collected by the first electrode group and the second electrode group can be differentiated; (2) Through the differentiated design of the two second electrodes in the second electrode group, differentiated physiological signals can be achieved; (3) Differentiated physiological signals can reduce the interference of motion artifacts, thereby extracting higher quality physiological signals; (4) Since there is a correlation between contact impedance and movement, the interference of motion artifacts in physiological signals is eliminated according to the contact impedance.
  • the present application uses specific words to describe the embodiments of the present application.
  • “one embodiment”, “an embodiment”, and/or “some embodiments” refer to a certain feature, structure or characteristic related to at least one embodiment of the present application. Therefore, it should be emphasized and noted that “one embodiment” or “an embodiment” or “an alternative embodiment” mentioned twice or more in different positions in this specification does not necessarily refer to the same embodiment.
  • some features, structures or characteristics in one or more embodiments of the present application can be appropriately combined.
  • numbers describing the number of components and attributes are used. It should be understood that such numbers used in the description of the embodiments are modified by the modifiers "about”, “approximately” or “substantially” in some examples. Unless otherwise specified, “about”, “approximately” or “substantially” indicate that the numbers are allowed to vary by ⁇ 20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximate values, which may change according to the required features of individual embodiments. In some embodiments, the numerical parameters should take into account the specified significant digits and adopt the general method of retaining digits. Although the numerical domains and parameters used to confirm the breadth of their range in some embodiments of the present application are approximate values, in specific embodiments, the setting of such numerical values is as accurate as possible within the feasible range.

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Abstract

本说明书实施例提供一种信号采集系统，包括穿戴本体；固定于穿戴本体并与用户皮肤接触的多个电极，多个电极包括第一电极组和第二电极组，第一电极组包括间隔布置以采集第一生理信号的两个第一电极，第二电极组包括分别靠近两个第一电极布置以采集第二生理信号的两个第二电极；以及处理电路，用于根据第二生理信号消除第一生理信号中的运动伪迹。

Description

信号采集系统 技术领域
本说明书涉及信号采集领域，特别涉及信号采集系统。
背景技术
广泛应用于生理检测、疾病诊断、实验研究等领域中的信号采集系统可以通过采集生理信号获取与用户身体状况相关的数据。例如，信号采集系统可以检测并利用心电信号的信息反映人体心脏的工作状态。然而，在信号采集系统采集生理信号时，常常会因为人体在信号采集过程中发生的一些移动或晃动等产生的干扰信号，导致采集到的生理信号包含运动伪迹，造成生理信号质量较差，难以准确地反映用户身体状态。因此，希望可以提出一种信号采集系统，能够减少运动伪迹的干扰，提高采集到的生理信号的质量。
发明内容
本说明书实施例之一提供一种信号采集系统，包括：穿戴本体；固定于穿戴本体并与用户皮肤接触的多个电极，多个电极包括第一电极组和第二电极组，第一电极组用于采集生理信号，第二电极组用于采集检测信号；以及处理电路，用于根据检测信号消除生理信号中的运动伪迹。
在一些实施例中，第一电极组包括间隔布置的两个第一电极，第二电极组包括分别靠近两个第一电极布置的两个第二电极，生理信号为第一生理信号，检测信号为第二生理信号，处理器用于根据第二生理信号消除第一生理信号中的运动伪迹。
在一些实施例中，两个第二电极的材料的导电性不同。
在一些实施例中，两个第二电极相对用户皮肤的凸起沿与用户皮肤表面垂直方向上的高度不同。
在一些实施例中，两个第二电极的材料的硬度不同，或两个第二电极的材料的褶皱程度不同。
在一些实施例中，两个第二电极的面积不同。
在一些实施例中，第一电极组包括间隔布置的两个第一电极，第二电极组包括靠近两个第一电极中其中一个第一电极布置的一个第二电极，其中，第二电极和与之靠近的第一电极用于采集检测信号。
在一些实施例中，每个第二电极的材料比与之对应的第一电极的材料的导电性弱。
在一些实施例中，每个第二电极相对穿戴本体的凸起比与之对应的第一电极相对穿戴本体的凸起沿与用户皮肤表面垂直方向上的高度小。
在一些实施例中，每个第二电极的第二材料比与之对应的第一电极的第一材料的硬度大，或者每个第二电极的第二材料比与之对应的第一电极的第一材料的褶皱程度大。
在一些实施例中，每个第二电极与皮肤接触的面积比与之对应的第一电极与皮肤接触的面积小。
在一些实施例中，第一电极组包括间隔布置的两个第一电极，第二电极组包括分别靠近两个第一电极布置的两个第二电极，检测信号为反映两个第一电极与用户皮肤 之间接触阻抗的检测信号。
在一些实施例中，还包括与两个第二电极电连接的激励源，激励源用于提供激励信号。
在一些实施例中，生理信号的频率在20Hz-400Hz范围内，且激励信号的频率不小于250Hz。
在一些实施例中，激励信号的频率与50Hz的任一整数倍频的差值不小于1Hz；或者，激励信号的频率与60Hz的任一整数倍频的差值不小于1Hz。
在一些实施例中，激励信号的频率高于生理信号的频率范围。
在一些实施例中，检测信号和生理信号是在不同的时间段内分别采集的。
在一些实施例中，每个第二电极的边缘与对应第一电极的边缘之间的最小距离小于10cm。
在一些实施例中，每个第二电极分别与一个第一电极之间通过非弹性连接，且第二电极与对应第一电极在与皮肤表面平行的表面上的可移动距离的距离差与对应第一电极在与皮肤表面平行的表面上的可移动距离的比值不大于50％。
在一些实施例中，处理电路用于：
差分处理两个第一电极采集的信号得到生理信号；
差分处理两个第二电极采集的信号得到检测信号；以及
根据检测信号消除生理信号中的运动伪迹。
在一些实施例中，还包括惯性传感器，惯性传感器设置在第一电极组背离用户皮肤的一侧，并用于测量第一电极组的运动伪迹。
本说明书实施例之一还提供一种信号采集系统，包括：穿戴本体；固定于穿戴本体并与用户皮肤接触的多个电极，多个电极包括间隔布置以采集生理信号的两个电极；与两个电极电连接的激励源，激励源用于提供激励信号，以产生反映两个电极与用户皮肤之间接触阻抗的检测信号；以及处理电路，用于根据检测信号消除生理信号中的运动伪迹。
在一些实施例中，生理信号的频率在20Hz-400Hz范围内，且激励信号的频率不小于250Hz。
在一些实施例中，激励信号的频率与50Hz的任一整数倍频的差值不小于1Hz；或者，激励信号的频率与60Hz的任一整数倍频的差值不小于1Hz。
在一些实施例中，激励信号的频率高于生理信号的频率范围。
在一些实施例中，检测信号和生理信号是在不同的时间段内分别采集的。
附图说明
图1是根据本说明书的一些实施例所示的示例性信号采集系统的框图；
图2是根据本说明书的一些实施例所示的示例性信号采集系统的示意图；
图3是根据本说明书的一些实施例所示的示例性信号采集系统的示意图；
图4是根据本说明书的一些实施例所示的示例性信号采集系统的结构示意图；
图5是根据本说明书的又一些实施例所示的示例性信号采集系统的结构示意图；
图6是根据本说明书的一些实施例所示的示例性信号采集系统的框图；
图7A是根据本说明书的一些实施例所示的接触阻抗和肌电信号的波动关系示意图；
图7B是本说明书的一些实施例所示的接触阻抗和肌电信号的波动关系示意图；以及
图8是根据本说明书的一些实施例所示的示例性信号采集系统的框图。
具体实施方式
为了更清楚地说明本申请实施例的技术方案，下面将对实施例描述中所需要使用的附图作简单的介绍。显而易见地，下面描述中的附图仅仅是本申请的一些示例或实施例，对于本领域的普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图将本申请应用于其它类似情景。除非从语言环境中显而易见或另做说明，图中相同标号代表相同结构或操作。
应当理解，本文使用的“系统”、“装置”、“单元”和/或“模块”是用于区分不同级别的不同组件、元件、部件、部分或装配的一种方法。然而，如果其他词语可实现相同的目的，则可通过其他表达来替换词语。
如本申请和权利要求书中所示，除非上下文明确提示例外情形，“一”、“一个”、“一种”和/或“该”等词并非特指单数，也可包括复数。一般说来，术语“包括”与“包含”仅提示包括已明确标识的步骤和元素，而这些步骤和元素不构成一个排它性的罗列，方法或者设备也可能包含其它的步骤或元素。
本申请说明书以及权利要求书中使用的“第一”“第二”以及类似的词语并不表示任何顺序、数量或者重要性，而只是用来区分不同的组成部分。同样，“一个”或者“一”等类似词语也不表示数量限制，而是表示存在至少一个。除非另行指出，“前部”、“后部”、“下部”和/或“上部”等类似词语只是为了便于说明，而并非限于一个位置或者一种空间定向。一般说来，术语“包括”与“包含”仅提示包括已明确标识的步骤和元素，而这些步骤和元素不构成一个排它性的罗列，方法或者设备也可能包含其它的步骤或元素。
本说明书实施例描述了一种信号采集系统。在一些实施例中，信号采集系统可以包括穿戴本体和多个电极。其中，电极固定于穿戴本体上，当穿戴本体穿戴在用户身上时，多个电极与用户皮肤相接触，以通过电极采集用户的生理信号。在一些实施例中，多个电极可以包括第一电极组和第二电极组，第一电极组包括间隔布置以采集第一生理信号的两个第一电极，第二电极组包括分别靠近两个第一电极布置以采集第二生理信号的两个第二电极。在一些实施例中，通过对上述两组电极(例如第一电极组和第二电极组)的设计，可以使两组电极采集到差异化的第一生理信号和第二生理信号。例如，第一生理信号中可以包含真实生理信号及运动伪迹，第二生理信号中可以包含运动伪迹以及少量真实生理信号，或者第二生理信号仅包含运动伪迹，其中，运动伪迹是指在信号采集过程中，用户的运动(例如，头部和/或肢体的晃动等)所产生的干扰信号。由于第二电极靠近第一电极设置，第二电极与第一电极具有运动一致性，故第二电极组与第一电极组采集到的生理信号具有强相关性。在一些实施例中，可以认为第一生理信号中的运动伪迹与第二生理信号中的运动伪迹大致相同，第二生理信号中的少量真实生理信号可以忽略不计。在一些实施例中，信号采集系统还可以包括处理电路，处理电路根据第二生理信号消除第一生理信号中的运动伪迹，以得到第一生理信号中的真实生理信号。本说明书实施例描述的信号采集系统，可以尽可能地消除采集到的生理信号中的运动伪迹，使最终获得的生理信号干扰较少，质量较高。
图1是根据本说明书的一些实施例所示的示例性信号采集系统100的框图。如图1所示，信号采集系统100包括穿戴本体110、第一电极组12、第二电极组13以及处理电路140。第一电极组12可以包括两个第一电极120，第二电极组13可以包括两个第二电极130。
穿戴本体110用于穿戴于用户身上。在一些实施例中，穿戴本体110可以为上 衣(例如T恤、马甲、背心、外套等)，穿戴于用户的上半身。在一些实施例中，穿戴本体110可以为裤装(例如长裤、短裤等)，穿戴于用户的下半身。在一些实施例中，穿戴本体110也可以为腿环或腰带，分别对应穿戴于用户的腿部或腰部。在一些实施例中，穿戴本体110还可以包括智能手环、智能鞋袜、智能眼镜、智能头盔、智能手表、智能背包、智能配件等或其任意组合。
电极(例如，第一电极组12中的第一电极120，第二电极组13中的第二电极130)可以指用于与其他物体接触以输入或导出电压(电流)的电路元件。在一些实施例中，电极(例如，第一电极组12中的第一电极120，第二电极组13中的第二电极130)可以与皮肤接触，用于采集用户的生理信号。生理信号为可以反应用户身体状态的信号，在一些实施例中，生理信号可以包括呼吸信号、心电信号(ECG)、肌电信号、血压信号、血氧信号、温度信号等一种或多种信号。在生理信号的采集过程中，电极可以固定在穿戴本体110上且保持与用户皮肤的接触。在一些实施例中，电极可以设置在穿戴本体110上相对人体各个部位，例如，小腿、大腿、腰、后背、胸部、肩部、颈部等。
以采集心电信号为例，用于采集心电信号的多个电极可以设置在穿戴本体110上距离用户心脏不同距离的位置(例如，人体的腰、后背、胸部、手部等)。例如，第一电极组12的两个第一电极120可以在人体的腰部区域间隔分布，第二电极组13中的两个第二电极130分别靠近两个第一电极120设置。在一些实施例中，为了提高两个第一电极(或第二电极)所采集的心电信号中运动伪迹的相似性，穿戴本体110可以将两个第一电极(或第二电极)对称贴合在人体的正中矢状面的两侧。两个第一电极120中的一个第一电极120采集第一电势，另一个第一电极120采集第二电势，第一电势和第二电势之间具有第一电势差(第一电势差可以用来产生反映第一心电信号的参数)。两个第二电极130中的一个第二电极130采集第三电势，另一个第二电极130采集第四电势，第三电势和第四电势之间具有第二电势差(第二电势差可以用来反映第二心电信号的参数)。
又以采集肌电信号为例，用于采集肌电信号的多个电极可以设置在穿戴本体110上具有大肌群的位置(例如，人体的背部、腰部、腿部等)。例如，第一电极组12的两个第一电极120可以在一块肌肉上间隔设置，第二电极组13中的两个第二电极130分别靠近两个第一电极120设置。在一些实施例中，两个第一电极120及两个第二电极130可以沿该部位肌肉纤维的长度方向依次设置。肌肉纤维长度方向上的不同位置具有不同的电势，两个第一电极120中的一个第一电极120可以采集第一电势，另一个第一电极120可以采集第二电势，第一电势和第二电势之间具有第一电势差(第一电势差可以用来产生反映第一肌电信号的参数)。两个第二电极130中的一个第二电极130可以采集第三电势，另一个第二电极130可以采集第四电势，第三电势和第四电势之间具有第二电势差(第三电势差可以用来产生反映第二肌电信号的参数)。
以下结合图2及图3示例性说明第一电极120及第二电极130的设置位置。
图2是根据本说明书的一些实施例所示的示例性信号采集系统100的示意图。如图2所示，信号采集系统100包括穿戴本体110，所述穿戴本体110为上衣。两个第一电极120间隔设置，两个第二电极130中的一个第二电极130分别靠近两个第一电极120中的一个第一电极120设置。如图2所示，两个第一电极120和两个第二电极130可以设置于上衣对应于人体胸部的位置。
图3是根据本说明书的一些实施例所示的示例性信号采集系统100的示意图。如图3所示，穿戴本体110为绑带，套在人体的小腿上。在一些实施例中，一个第一电极120及与其靠近设置的第二电极130可以设置于绑带上沿肌肉纤维长度方向上的一 侧；另一个第一电极120及与其靠近设置的第二电极130可以设置于绑带上沿肌肉纤维长度方向上的另外一侧。
处理电路140可以用于处理信号。在一些实施例中，处理电路140可以独立于穿戴本体110设置，多个电极可以与处理电路140通讯连接。在又一些实施例中，处理电路140可以固定于穿戴本体110上。在一些实施例中，第一电极组12(两个第一电极120)和第二电极组13(两个第二电极130)可以均与处理电路140电连接，处理电路140接收来自两个第一电极120的第一电势和第二电势以及来自两个第二电极130的第三电势和第四电势。处理电路140可以差分处理第一电势和第二电势得到第一电势差，用于表征生理信号(例如，第一生理信号)。处理电路140可以差分处理第三电势和第四电势得到第二电势差，用于表征检测信号(例如，第二生理信号)。在一些实施例中，处理电路140可以利用第二生理信号对第一生理信号进行差分处理，以消除第一生理信号中的运动伪迹。在一些实施例中，可以通过对多个电极(例如，第一电极120与第二电极130，和/或两个第二电极130)之间的差异化设计，使第一生理信号中的真实生理信号和运动伪迹的占比与第二生理信号中的真实生理信号和运动伪迹的占比不同，以根据差异化的第一生理信号和第二生理信号，消除第一生理信号中的运动伪迹。关于电极差异化设计的更多说明可以参见图4、图5及本说明书其它部分的相关描述。
在一些实施例中，信号采集系统100还可以包括惯性传感器150。惯性传感器150用于测量第一电极组12的运动伪迹。在一些实施例中，惯性传感器150可以设置在第一电极组12上。例如，两个第一电极120中的任意一个处(例如，所述该第一电极120背离用户皮肤的一侧)设置有惯性传感器150，此时，可以认为惯性传感器150及其所在的第一电极120具有一致的运动状态，故惯性传感器150检测到的运动信号可以表示其所在的第一电极120的运动状态，检测到的运动信号可以用于表征第一电极组12的运动伪迹。再例如，两个第一电极120处(例如，每个第一电极120背离用户皮肤的一侧)可以分别设置有惯性传感器150。此时，两个惯性传感器150可以分别检测到用于表示其所在的第一电极120的运动状态的运动信号。在一些实施例中，可以将两个惯性传感器150检测到的两个运动信号做处理(例如，平均、加权平均等)，以获得第一电极组12的运动伪迹。
在一些实施例中，惯性传感器150可以与处理电路140电连接。在一些实施例中，信号采集系统100可以包括第一电极组12、设置在所述第一电极组背离用户皮肤的一侧的惯性传感器150以及处理电路140。第一电极组12包括间隔布置以采集生理信号(即第一生理信号)的两个第一电极120；惯性传感器150用于测量所述第一电极组12的运动信号，作为所述第一电极组12的运动伪迹；处理电路140用于根据惯性传感器150测得的运动信号消除所述第一电极组12采集的生理信号中的运动伪迹。由于惯性传感器150测量运动信号的原理与第一电极组12采集生理信号中包含运动伪迹的测量原理不同，因此处理电路140可以通过预处理运动信号与生理信号(例如，将运动信号和生理信号进行归一化处理)后再做差分处理，以消除运动信号中的运动伪迹。再例如，通过预处理运动信号和生理信号，将运动信号和生理信号都做主成分分析，然后在生理信号中去掉运动信号的主成分，再重构，以消除运动信号中的运动伪迹。在一些实施例中，信息采集系统100可以包括第一电极组12、第二电极组13、设置在所述第一电极组背离用户皮肤的一侧的惯性传感器150以及处理电路140。处理电路140用于根据惯性传感器150测得的运动信号确定第二生理信号用于消除第一生理信号中的运动伪迹的置信度。例如，处理电路140中可以预设阈值，若惯性传感器150测得的运动信号与第二电极组13采集的第二生理信号的差异小于预设阈值，则认为第二生理信号的置信度较高，处理电路140可以根据第二生理信号对第一生理信号进行差分处理，以 消除第一生理信号中的运动伪迹；若运动信号与第二生理信号的差异超过预设阈值，则认为所述第二生理信号的置信度较低，所述处理电路140可以发送重新获取第二生理信号的指令给第二电极组13。再例如，处理电路140可以根据惯性传感器150测得的运动信号对第一生理信号进行差分处理(如上所述，先进行预处理再进行差分处理)，以消除第一生理信号中的运动伪迹。
需要说明的是，信号采集系统100可以包括多个第一电极组12和多个第二电极组13。多个第一电极组12和多个第二电极组13分别固定在穿戴本体110上对应人体的不同部位，以采集用户的不同身体部位的生理信号。还需要说明的是，关于采用惯性传感器150的技术方案可以应用于本说明书的其它实施例中，例如，可以应用于图4、图5所示的信号采集系统100、图6所示的信号采集系统300及图8所示的信号采集系统400中。
为获得更准确、质量更高的生理信号，可以通过对多个电极之间的差异化设计(例如，第一电极120与第二电极130之间的差异化或两个第二电极130之间的差异化设计)，以获得差异化的第一生理信号和第二生理信号。以下将结合图4-图5对电极的差异化设计进行示例性说明。图4是根据本说明书的一些实施例所示的示例性信号采集系统100的结构示意图。图5是根据本说明书的又一些实施例所示的示例性信号采集系统100的结构示意图。如图4及图5所示，多个电极可以固定在穿戴本体110靠近用户皮肤的侧面上，且能够与皮肤接触。在穿戴本体110上，两个第一电极120可以间隔开设置，两个第二电极130可以分别靠近第一电极120设置。在一些实施例中，两个第一电极120与两个第二电极130可以并排设置，两个第二电极130可以位于两个第一电极120的相对的两侧。在一些实施例中，两个第二电极130可以位于两个第一电极120之间。在另一些实施例中，其中一个第二电极130可以位于两个第一电极120之间，另外一个第二电极130可以位于与之靠近的第一电极120的远离另外一个第一电极120的一侧。需要知道的是，两个第一电极120和/或两个第二电极130不限于如图4及图5所示的并排设置，也可以是呈其他方式设置。例如，两个第一电极120可以在于皮肤表面平行的表面上以任一分隔的方式分开设置，与每个第一电极120靠近设置的第二电极130可以以一定距离设置在所述第一电极120周围的任意位置，本说明书对此不作限制。
在一些实施例中，第二电极130与对应第一电极120之间的距离指第二电极130的边缘与对应第一电极120的边缘之间的最小距离。如图4及图5所示，第二电极130与对应第一电极120之间的距离可以指尺寸a，即第二电极130和与之靠近的第一电极120的相互靠近的边缘之间的最小距离。为保证第二电极组13与第一电极组12的运动具有一致性，在一些实施例中，所述一定距离可以小于10cm。例如，所述一定距离可以小于8cm。再例如，所述一定距离可以小于6cm。这里所述的“对应”指两个靠近设置的第一电极120和第二电极130。即如果一个第一电极120和一个第二电极130靠近设置，则可以称该第一电极120为与该第二电极130对应的第一电极，也可以称该第二电极130为与该第一电极120对应的第二电极。
在一些实施例中，为保证第二电极组13与第一电极组12的运动尽可能一致，第二电极130与对应第一电极120之间可以物理连接。本说明书所述的物理连接是指通过结构、材料或复合的结构材料，实现物理意义上的连接。为避免第一电极120与第二电极130之间产生电信号影响，这里所说的物理连接，是一种绝缘性连接。在一些实施例中，第二电极130与对应第一电极120之间可以通过绝缘结构(例如，硅胶层)实现连接。第二电极130的任意位置(例如侧面、侧边或面上局部区域等)可以与第一电极120的任意位置(例如侧面、侧边或面上局部区域等)通过物理连接。在一些实施例中，为了加强第二电极130与对应第一电极120的运动一致性，第二电极130与对应第一电 极120之间可以非弹性连接(或刚性连接)。在一些实施例中，每个第二电极130与对应第一电极120在与皮肤表面平行的表面上的可移动距离的距离差与对应第一电极120在与皮肤表面平行的表面上的可移动距离的比值可以不大于50％。例如，在用户佩戴所述信号采集系统100时，第一电极组12和第二电极组13可能在皮肤表面移动，移动时，每个第二电极130与对应第一电极120在与皮肤表面平行的表面上的可移动距离的距离差与对应第一电极120在与皮肤表面平行的表面上的可移动距离的比值可以不大于45％。再例如，每个第二电极130与对应第一电极120在与皮肤表面平行的表面上的可移动距离的距离差与对应第一电极120在与皮肤表面平行的表面上的可移动距离的比值可以不大于40％。
为了降低运动伪迹的干扰，提高最终所得的生理信号的质量，可以通过对第一电极120及第二电极130的差异化设计，以提升第一生理信号与第二生理信号之间的差异性。
在一些实施例中，每个第二电极130的材料比与之对应(例如，物理连接)的第一电极120的材料的导电性弱。如此，第一电极组12采集的第一生理信号中的真实生理信号占比相对于第二电极组13采集的第二生理信号中真实生理信号的占比更多。在一些实施例中，当第二电极130的材料的导电性比与之相对应的第一电极120的材料的导电性弱到一定程度(例如，第二电极130的材料的阻抗和与之相对应的第一电极120的材料的阻抗相差一定程度)时，第二电极组13采集到的第二生理信号中的真实生理信号可以小到可以忽略，因此第二生理信号可以被认为只包含运动伪迹。例如，在电极保护的尺寸下，50Hz处为例，第一电极120的阻抗在几千欧姆，第一电极120的材料的阻抗和第二电极130的材料的阻抗相差达到1M欧姆以上时，第二电极组13采集到的第二生理信号中运动伪迹信号的成分明显变多；当第一电极120的材料的阻抗和第二电极130的材料的阻抗相差达到100M欧姆以上，第二生理信号中采集的主要是运动伪迹。同时，因为第一电极组12与第二电极组13的运动具有一致性，因此可以根据第二生理信号消除第一生理信号中的运动伪迹，以降低第一生理信号中运动伪迹的干扰，得到高质量的生理信号。在一些实施例中，电极可以是由单一材料组成的电极，例如金属织物电极、导电硅电极、水凝胶电极、金属电极等。例如，每个第一电极120的材料可以为金属织物，与之对应的第二电极130的材料可以为导电硅，金属织物电极电阻率更小，导电性更强。在一些实施例中，电极材料的不同不仅仅会影响电极本身的阻抗，同时会影响电极与皮肤间的接触阻抗。例如，每个第一电极120的材料可以为水凝胶，与之对应的第二电极130的材料可以为导电硅，水凝胶相比于导电硅更加亲和皮肤且保持湿润，因此，第一电极120相对于与之对应的第二电极130的接触阻抗更小，导电性更强。在一些实施例中，电极材料的不同还会影响角质层的电势强度。例如氯化银材料相比于银材料的半电池电势绝对值更小，其角质层电势更小，相同其他条件下，MA的影响小。在一些实施例中，第一电极120及第二电极130的差异化可以通过相同的材料的不同厚度实现。例如，由于金属织物电极厚度在一定范围内时，厚度越大，其阻抗以及与皮肤之间的接触阻抗也越小，导电性越好。在一些实施例中，每个第一电极120的材料和与之对应的第二电极130的材料可以均为金属织物，但第一电极120的材料的垂直于皮肤方向(参见图4及图5所示A方向)上的厚度大于与之对应的第二电极130的材料A方向上的厚度。再例如，由于导电硅电极厚度越大，其阻值越小，导电性越好，故在一些实施例中，第一电极120的材料和与之对应的第二电极130的材料可以均为导电硅，但第一电极120的材料的厚度大于与之对应的第二电极130的材料的厚度。在一些实施例中，第一电极120的材料和/或与之对应的第二电极130的材料可以是不同材料的组合(例如层叠、结合等)。例如，第一电极120的材料及与之对应的第二电 极130的材料均由金属织物与导电硅材料构成，第一电极120的材料中的金属织物的厚度小于与之对应的第二电极130的材料中的金属织物的厚度，第一电极120的材料中的导电硅材料的厚度大于与之对应的第二电极130的材料中的导电硅材料的厚度。
在一些实施例中，电极可以通过胶粘、卡扣、魔术贴、缝合、压合等方式固定在穿戴本体110上，电极相对于穿戴本体110朝向皮肤表面的方向可能存在凸起。在一些实施例中，在沿与用户皮肤表面垂直的方向上，每个第二电极130相对于穿戴本体110的高度可以小于与之对应的第一电极120相对于穿戴本体110的高度。本说明书中的电极的“凸起”指在电极超过穿戴本体110靠近皮肤的表面111的部分；凸起的高度指在沿与用户皮肤表面垂直的方向上，电极超过穿戴本体110靠近皮肤的表面111的部分的高度。如图4所示，每个第一电极120相对穿戴本体110的凸起沿与皮肤表面垂直的方向(即方向A)的高度为c；与之对应的第二电极130相对穿戴本体110的凸起沿与皮肤表面垂直方向(即方向A)的高度为b。为了使第二电极130与皮肤之间的压力小于相对应的第一电极120与皮肤之间的压力，使第二电极130与皮肤的贴合程度相对于第一电极120更差，进而使第二电极组13采集的第二生理信号中真实生理信号的比例小，如图4所示，每个第二电极130相对穿戴本体110的凸起沿与皮肤表面垂直方向(即方向A)的高度b可以小于与之对应的第一电极120相对穿戴本体110的凸起沿与皮肤表面垂直的方向(即方向A)的高度c。如此，第一电极组12采集的第一电信号与第二电极组13采集的第二电信号存在差异化。在一些实施例中，当第二电极130的凸起的高度b和与之对应的第一电极120的凸起的高度c之间的差值与对应第一电极120的高度c的比值大于一定高度阈值(例如，5％)时，第一电极组12采集的第一电信号与第二电极组13采集的第二电信号存在明显差异，因此第二生理信号可以被认为只包含运动伪迹。同时，因为第一电极组12与第二电极组13的运动具有一致性，因此可以利用第二生理信号对第一生理信号进行差分处理，以消除第一生理信号中的运动伪迹，以降低第一生理信号中运动伪迹的干扰，得到高质量的生理信号。在一些实施例中，为了产生差异化的第一生理信号和第二生理信号，每个第一电极120的凸起的高度可以在1mm-10cm范围内，与之对应的第二电极130的凸起的高度可以在0mm-5mm范围内。
在一些实施例中，为了产生差异化的第一生理信号和第二生理信号，每个第二电极130的材料可以和与之对应的第一电极120的材料不同。例如，每个第二电极130的材料可以比与之对应的第一电极120的材料的硬度大，以使对应的第一电极120比第二电极130相对于用户皮肤的贴合性更好，因此第二生理信号中真实生理信号的占比相对于第一生理信号更少(即第二生理信号中运动伪迹的占比相对于第一生理信号更大)。在一些实施例中，每个第二电极130的材料可以比与之对应的第一电极120的材料的褶皱程度大，以使对应的第一电极120比第二电极130相对于用户皮肤的贴合性更好，因此第二生理信号中真实生理信号的占比相对于第一生理信号更少(即第二生理信号中运动伪迹的占比相对于第一生理信号更大)。应当理解的是材料的硬度或褶皱程度是在同一测量方法或同一测量标准下测量的比较。
在一些实施例中，可以通过第一电极组12和第二电极组13与皮肤之间的接触阻抗的差异，产生差异化的第一生理信号和第二生理信号。在一些实施例中，可以通过每个第一电极120和与之对应的第二电极130与皮肤接触面的面积的差别，使第一电极组12和第二电极组13之间产生差异化的接触阻抗。例如，第一电极120与皮肤接触面(例如，如图4所示B面)可以具有第一面积，与之对应的第二电极130与皮肤接触面(例如，如图4所示C面)可以具有第二面积，每个第二电极130的第二面积可以比与之对应的第一电极120的第一面积小，以使第一电极120与皮肤之间的接触阻抗小于 与之对应的第二电极130与皮肤之间的接触阻抗。如此，第一电极组12采集的第一生理信号中的真实生理信号占比相对于第二电极组13采集的第二生理信号的更多，同时，第二生理信号中的运动伪迹占比相对于第一生理信号更多。在一些实施例中，第一电极120的B面或第二电极130的C面可以为矩形或圆角矩形。在一些实施例中，为了使第一电极组12和第二电极组13与皮肤之间的接触阻抗不同，进而产生差异化的第一生理信号和第二生理信号，第一电极120与皮肤接触面(例如，如图4所示B面)的面积可以在1cm 2-100cm 2范围内；第二电极130与皮肤接触面(例如，如图4所示C面)的面积可以在0.5cm 2-50cm 2范围内。在一些实施例中，第一电极120的B面或第二电极130的C面的形状也可以为圆形、三角形、六边形等其他规则或不规则的形状，在实际应用中，B面或C面的形状可以取决于生理信号待采集部位的形状。在一些实施例中，可以在每个第二电极130的C面上布置特定图案的结构或褶皱结构，以此降低第二电极130与皮肤的贴合性，同时减少第二电极130与皮肤贴合的面积，达到区别于第一电极120的目的。
应当理解的是，图1-3所示的包含四个电极的信号采集系统100仅为示例，并不旨在限定信号采集系统100中电极的数量。信号采集系统100中电极的数量可以是任意能够获取差异化运动信号和生理信号的数量，在此不做限定。例如，第一电极组12可以包括两个第一电极120，第二电极组13可以只包括一个第二电极130(即信号采集系统100包括3个电极)。两个第一电极120用于获取第一生理信号，第二电极130可以靠近其中一个第一电极120布置，并与该第一电极120组成一个电极对，用于获取第二生理信号。应当理解的是，当第二电极组13可以只包括一个第二电极130时，第二电极组中的第二电极130和与之对应的第一电极120的材料、导电性、相对于穿戴本体的凸起、硬度、褶皱程度、与皮肤接触面积等参数可以与第二电极组13可以包括两个第二电极130时每个第二电极130和与之对应的第一电极120的对应参数相同，在此不赘述。再例如，在上述3个电极的基础上，信号采集系统100还可以包括一个参考电极，用于获取参考信号。再例如，如图1-3所示的包含四个电极的信号采集系统100中，两个第一电极120用于获取第一生理信号；两个第二电极130可以分别于两个第一电极120构成电极对，获取第二生理信号和第三生理信号；两个第二电极130可以获取第四生理信号。如此，包含四个电极的信号采集系统100可以获取四组差异化的电信号。应当理解的是，本说明书中描述的第一电极组包括两个第一电极120仅为示例，第一电极组可以包括两个以上数量的第一电极120，相对应地，在一些实施例中，第二电极组可以包括与所述第一电极120数量相同的第二电极130。例如，第一电极组包括三个第一电极120，用于采集生理信号；第二电极组包括三个第二电极130，用于采集检测信号。在一些实施例中，第一电极组可以包括两个以上数量的第一电极120，第二电极组可以包括至少一个第二电极130。例如，第一电极组可以包括三个第一电极120，用于采集生理信号；第二电极组可以包括一个第二电极130，用于与其中一个第一电极120靠近布置，以采集检测信号。
在一些实施例中，为了方便信号采集系统100中多个电极的生产制作，第二电极组13中的两个第二电极130可以相同。例如，如图4所示，每个第二电极130可以具有相同的导电性、凸起高度、硬度、褶皱程度、与皮肤的接触面积等。在一些实施例中，为了降低运动伪迹的干扰，提高生理信号的质量，可以对第二电极组13的两个第二电极130实施差异化设计。当两个第二电极130不同(例如，导电性、凸起高度、硬度、褶皱程度、与皮肤的接触面积等中的一个或任意组合不同)时，第二电极组13采集到的第二生理信号中运动伪迹的占比相对于相同的两个第二电极130采集的第二生理信号中的更多。因此可以通过第二电极组13中的两个第二电极130的差异化设计， 获得差异化的第一生理信号和第二生理信号，以利用第二生理信号消除第一生理信号中的运动伪迹时，以降低运动伪迹的干扰。
在一些实施例中，两个第二电极130之间的差异化可以与上述第一电极120和与之对应的第二电极130之间的差异化设计类似。在一些实施例中，两个第二电极130的材料的导电性可以不同。例如，两个第二电极130可以为厚度不同的导电硅电极。再例如，两个第二电极130的材料可以分别为导电硅电极和金属织物电极。在一些实施例中，两个第二电极130相对穿戴本体110的凸起沿与A方向上的高度(参见图5所示的高度d和e)可以不同，以使两个第二电极130相对于用户皮肤的贴合性不同。在一些实施例中，两个第二电极130的材料的硬度可以不同，以使两个第二电极130相对于用户皮肤的贴合性不同。在一些实施例中，两个第二电极130的材料的褶皱程度可以不同，以使两个第二电极130相对于用户皮肤的贴合性不同。在一些实施例中，两个第二电极130与皮肤接触的面积(参见图5所示的E面及D面)可以不同，以使两个第二电极130与皮肤之间的接触阻抗不同。
在一些实施例中，如图4和图5所示，信号采集系统100还可以包括惯性传感器150。惯性传感器150设置在第一电极120背离用户皮肤的一侧，以使第一电极120与惯性传感器150具有一致的运动状态。应当理解的是，图4和图5仅为信号采集系统100的两个实施例，并不用于限定信号采集系统100的结构。例如，信号采集系统100可以包括第一电极组12、设置在所述第一电极组12背离用户皮肤的一侧的惯性传感器150以及处理电路140(即不包括第二电极组13)。再例如，如图4或图5所示，信息采集系统100可以包括第一电极组12、第二电极组13、设置在所述第一电极组背离用户皮肤的一侧的惯性传感器150以及处理电路140。关于惯性传感器150的描述可以参见图1的相关描述。再例如，信号采集系统100可以包括第一电极组12、第二电极组13以及处理电路140(即不包括惯性传感器150)。
图6是根据本说明书的一些实施例所示的示例性信号采集系统300的框图。如图6所示，信号采集系统300可以包括穿戴本体310、第一电极组32、第二电极组33以及处理电路340。第一电极组12可以包括两个第一电极320。第二电极组13可以包括两个第二电极330。图6示出的穿戴本体310和第一电极320的功能与结构分布可以分别与图1-5所述的穿戴本体110和第一电极120类似，在此不再赘述。图6的信号采集系统300与图1-5所述的信号采集系统100相比的不同在于第二电极330的功能与结构分布。例如，第二电极330用于采集反映所述两个第一电极320与用户皮肤之间接触阻抗的检测信号，相应地，所述处理电路340用于根据所述检测信号消除所述生理信号中的运动伪迹(例如，可以将检测信号和生理信号接入电路，在模拟电路中处理，也可以在数字电路中处理，或在算法中处理)。在一些实施例中，第二电极330用于采集反映所述两个第二电极330与用户皮肤之间接触阻抗的检测信号。为了保证第一电极320与第二电极330之间的运动一致性，在一些实施例中，可以通过将每个第二电极330的边缘设置成与对应第一电极320的边缘之间的最小距离小于10cm。在一些实施例中，还可以将每个第二电极330设置成分别与一个第一电极320之间通过非弹性连接，且所述第二电极330与对应第一电极320在与皮肤表面平行的表面上的可移动距离的距离差与对应第一电极320在与皮肤表面平行的表面上的可移动距离的比值不大于50％。再例如，为了使两个第一电极320与两个第二电极330与皮肤之间的接触阻抗尽量一致，以使第二电极330的接触阻抗可以间接反映第一电极320的接触阻抗，每个第二电极330可以和与之对应的第一电极320相同。例如，每个第二电极330的材料和与之对应的第一电极320的材料的导电性可以相同。再例如，每个第二电极330相对于穿戴本体310的凸起可以和与之对应的第一电极320的凸起沿与用户皮肤垂直方向上的高度 相同。再例如，每个第二电极330的材料的硬度和/或褶皱程度可以和与之对应的第一电极320的硬度和/或褶皱程度相同。再例如，每个第二电极330与皮肤的接触面积可以和与之对应的第一电极320与皮肤的接触面积相同。如此，第一电极320与第二电极330之间的运动一致性且与皮肤的接触阻抗尽量一致，两个第二电极330采集的两个第二电极330与用户皮肤之间接触阻抗的检测信号可以用于反映两个第一电极320与用户皮肤之间接触阻抗的检测信号。在一些实施例中，处理电路340可以差分处理两个第一电极320采集的信号得到生理信号，差分处理所述两个第二电极330采集的信号得到检测信号，并根据所述检测信号消除所述生理信号中的运动伪迹。
在一些实施例中，信号采集系统300还包括与两个第二电极330电连接的激励源370。激励源370可以用于提供激励信号，以产生反映第一电极组32与人体之间接触阻抗的检测信号。在一些实施例中，激励源370可以是交流激励源，也可以是直流激励源，也可以是两者的组合。仅作为示例，激励信号可以理解为通过第二电极330流经人体后形成闭环回路，此时，检测信号可以对应第二电极组33与人体之间的接触阻抗在该闭环回路中的分压。图7A是根据本说明书的一些实施例所示的接触阻抗和肌电信号的波动关系示意图；图7B是本说明书的一些实施例所示的接触阻抗和肌电信号的波动关系示意图。如图7A和图7B所示，无论接触阻抗值是大还是小，在相同的采样点，接触阻抗的值均会随着运动而产生相关波动(例如，接触阻抗的值会随着肌电信号的增大而增大，也会随着肌电信号的减小而减小)。因此，可以根据接触阻抗获得运动伪迹，并可利用获得的运动伪迹(例如，通过第二电极组33采集的反映第一电极组32与用户皮肤之间接触阻抗的检测信号来表征的运动伪迹)消除第一电极组32采集的生理信号中的运动伪迹。例如，可以对接触阻抗进行频率分析，得到运动伪迹的主频率，还可以对接触阻抗进行幅值分析(例如，波动值/附近的平均值等)，以获取运动伪迹的强度信息。
激励源370可以为提供电能的电路元件。在一些实施例中，激励源370可以提供第一频率的激励信号，以产生反映第二电极330与人体之间接触阻抗的检测信号。在一些实施例中，激励源370可以为电流源或电压源。同时需要说明的是，激励源370的强度的设置还需要考虑人体的安全电压或安全电流，以保证人体安全，激励源370的强度不宜过高。在一些实施例中，激励源370的电流强度可以小于1mA。进一步的，在一些实施例中，激励源370的电流强度可以小于100μA。再进一步的，在一些实施例中，激励源370的电流强度可以10μA。
在一些实施例中，激励源370的数量可以为一个，可以通过多个分路与多个第二电极330连接，为多个第二电极330提供激励信号，其中，每个分路可以设置有一个第二电极330。在一些实施例中，激励源370可以为多个，每个激励源370可以分别与一个或多个第二电极330连接，为每个第二电极330提供激励信号。
在一些实施例中，激励源370可以同时产生多个具有不同频率的激励信号，并且可以给多个第二电极330提供具有相同频率或不同频率的激励信号，由此产生不同频率的检测信号。例如，激励源370可以为多个第二电极330提供不同频率的激励信号以采集不同的检测信号。多个第二电极330之间可以具有较大的距离(例如大于或等于5cm)，以使激励信号流经的闭环回路可以经由不同的人体组织，如此设置，多个第二电极330对应的不同频率的检测信号可以用于反映人体的体成分信息，如体脂率、骨密度、体液含量等等体成分信息。具体地，激励源370可以提供与第一频率不同的第二频率的第二激励信号，以产生第二检测信号。第二检测信号可以反映在第二频率下第二电极330与人体之间形成的闭环回路上的阻抗信息，包括第二电极330与人体的接触阻抗以及闭环回路上人体组织的阻抗。在一些实施例中，利用通过第一激励信号(如，具有 第一频率的激励信号)产生的第一检测信号，以及通过第二激励信号产生的第二检测信号，可以确定人体的体成分信息。
在一些实施例中，激励信号可以为电压信号或电流信号。在一些实施例中，激励信号可以为具有第一频率的交流信号，以使产生的检测信号也具有第一频率。第一频率可以设置在受外界干扰(例如，工频干扰)较小且对生理信号干扰较小的频率范围。
在一些实施例中，激励信号的频率可以根据生理信号的频率范围进行设定。在一些实施例中，激励信号的频率可以高于所述生理信号的频率范围，以避开生理信号所在的大部分频段，减小生理信号与激励信号之间的相互干扰。在一些实施例中，激励频率可以不小于850Hz。例如，激励频率可以不小于400Hz。若激励信号的强度较大或者与待测量部位的电极对应的接触阻抗能分到足够多的电压，则生理信号对激励信号的干扰较低，激励信号(例如，频率可以不小于400Hz的激励信号)可以容忍少部分的生理信号(如，频率在400Hz～850Hz内的生理信号)。在一些实施例中，由于生理信号(例如，肌电信号)的频率主要集中在20Hz～400Hz，并且，低频段中具有强度较大的运动伪迹，为了避免受到肌电信号和运动伪迹的影响，激励源370提供的激励信号的频率可以大于250Hz。在一些实施例中，由于信号采集系统300中还存在工频(如，50Hz或60Hz的交流供电及其谐波)噪声的干扰，激励源的频率还可以避开工频噪声所在的频率范围。在一些实施例中，激励源370提供的激励信号的频率与50Hz或60Hz的任一整数倍频的差值可以不小于1Hz，或者，激励源370提供的激励信号的频率与50Hz或60Hz的任一整数倍频的差值可以不小于2％。在一些实施例中，激励源370提供的激励信号的频率可以为400Hz以上，例如460Hz、640Hz、830Hz等。在一些实施例中，激励源370提供的激励信号的频率的设置还需要结合处理电路340的采样频率进行考虑。具体来说，为了采集到检测信号，该采样频率可以是激励源370提供的激励信号的频率的至少2倍及以上。为了减少误差，在一些实施例中，采样频率可以是激励源370提供的激励信号的频率的4倍及以上。需要说明的是，由于待采样的通道数目可能较多，大部分处理电路340难以支持多通道的极高采样频率，所以处理电路340的采样频率和激励源370提供的激励信号的频率也不宜过高。基于此，在一些实施例中，激励源370提供的激励信号的频率可以在设置在250Hz～2000Hz范围内。
在一些实施例中，信号采集系统300可以在不同的时间段内分别采集生理信号和检测信号。示例性的，信号采集系统300可以在第一时间段内采集生理信号。信号采集系统300可以在第二时间段内采集检测信号。例如，信号采集系统300可以包括开关电路，开关电路可以用于控制第一电极组与处理电路340的导通状态，还可以用于控制第二电极组与激励源370的导通状态，以使在同一时刻仅有第一电极组与处理电路340保持电导通状态，或是仅有第二电极组与激励源370保持电导通状态。如此，通过分时采集以及处理检测信号和生理信号，可以在避免信号互相干扰的同时，减轻设备的处理压力，节约计算资源。在一些实施例中，信号采集系统300可以同时采集生理信号和检测信号，并通过不同的传输通道传输给不同的处理电路，以避免信号互相干扰。
图8是根据本说明书的一些实施例所示的示例性信号采集系统400的框图。如图8所示，信号采集系统400可以包括穿戴本体410、两个电极420、处理电路440及交流激励源470。图8示出的穿戴本体410、处理电路440及交流激励源470与图6所示的穿戴本体310、以及处理电路340类似，在此不再赘述。图8的信号采集系统400与图6的信号采集系统300的不同在于，信号采集系统400仅包括一组电极(两个电极420)，两个电极420可以既采集生理信号，又采集反映两个电极420与皮肤之间接触阻抗的检测信号；信号采集系统400中的激励源为交流激励源470，而信号采集系统300中的激励源可以为交流激励源，也可以为直流激励源，也可以为两者的组合。在一些实 施例中，用于采集生理信号和检测信号的两个电极420可以固定于所述穿戴本体410并与用户皮肤接触。
在一些实施例中，交流激励源470与两个电极420电连接。交流激励源470用于提供激励信号，以产生反映两个电极420与人体之间接触阻抗的检测信号。仅作为示例，激励信号可以理解为通过电极420流经人体后形成闭环回路，此时，检测信号可以对应电极420与人体之间的接触阻抗在该闭环回路中的分压。在一些实施例中，如图7A和图7B所示，接触阻抗的值会随着运动而产生相关波动(例如，接触阻抗的值会随着肌电信号的增大而增大，也会随着肌电信号的减小而减小)。因此，可以根据接触阻抗获得运动伪迹，即可利用获得的运动伪迹(例如，通过两个电极420采集的反映两个电极420与用户皮肤之间接触阻抗的检测信号来表征的运动伪迹)消除两个电极420采集的生理信号中的运动伪迹。应当理解的是，图8所示的信号采集系统400采集的生理信号的频率、激励信号的频率等可以与图6所示的信号采集系统300的类似，在此不赘述。由于生理信号和检测信号由同一组电极采集，信号采集系统400可以在不同的时间段内分别采集生理信号和检测信号。示例性的，信号采集系统400可以在第一时间段内采集生理信号。信号采集系统400可以在第二时间段内采集检测信号。例如，信号采集系统400可以包括开关电路，开关电路可以用于控制两个电极420与处理电路440的导通状态，还可以用于控制两个电极420与激励源370的导通状态，以使在同一时刻两个电极420与处理电路440保持电导通状态，或是两个电极420与交流激励源470保持电导通状态。如此，通过分时采集以及处理检测信号和生理信号，可以在避免信号互相干扰的同时，减轻设备的处理压力，节约计算资源。
需要注意的是，以上对于信号采集系统的描述，仅为示例性描述，并不能把本说明书限制在所举实施例范围之内。其中不同实施例可能产生的有益效果不同，在不同的实施例里，可能产生的有益效果可以是以上任意一种或几种的组合，也可以是其他任何可能获得的有益效果。
本说明书具有以下技术效果：(1)通过第一电极组和与第二电极组的差异化设计，可以实现第一电极组和第二电极组采集的生理信号的差异化；(2)通过第二电极组中两个第二电极的差异化设计，可以实现差异化的生理信号；(3)差异化的生理信号可以降低运动伪迹的干扰，从而提取质量较高的生理信号；(4)由于接触阻抗和运动之间存在关联性，根据接触阻抗消除生理信号中运动伪迹的干扰。
上文已对基本概念做了描述，显然，对于本领域技术人员来说，上述详细披露仅仅作为示例，而并不构成对本申请的限定。虽然此处并没有明确说明，本领域技术人员可能会对本申请进行各种修改、改进和修正。该类修改、改进和修正在本申请中被建议，所以该类修改、改进、修正仍属于本申请示范实施例的精神和范围。
同时，本申请使用了特定词语来描述本申请的实施例。如“一个实施例”、“一实施例”、和/或“一些实施例”意指与本申请至少一个实施例相关的某一特征、结构或特点。因此，应强调并注意的是，本说明书中在不同位置两次或多次提及的“一实施例”或“一个实施例”或“一个替代性实施例”并不一定是指同一实施例。此外，本申请的一个或多个实施例中的某些特征、结构或特点可以进行适当的组合。
此外，除非权利要求中明确说明，本申请处理元素和序列的顺序、数字字母的使用、或其他名称的使用，并非用于限定本申请流程和方法的顺序。尽管上述披露中通过各种示例讨论了一些目前认为有用的发明实施例，但应当理解的是，该类细节仅起到说明的目的，附加的权利要求并不仅限于披露的实施例，相反，权利要求旨在覆盖所有符合本申请实施例实质和范围的修正和等价组合。例如，虽然以上所描述的系统组件可以通过硬件设备实现，但是也可以只通过软件的解决方案得以实现，如在现有的服务器 或移动设备上安装所描述的系统。
同理，应当注意的是，为了简化本申请披露的表述，从而帮助对一个或多个发明实施例的理解，前文对本申请实施例的描述中，有时会将多种特征归并至一个实施例、附图或对其的描述中。但是，这种披露方法并不意味着本申请对象所需要的特征比权利要求中提及的特征多。实际上，实施例的特征要少于上述披露的单个实施例的全部特征。
一些实施例中使用了描述成分、属性数量的数字，应当理解的是，此类用于实施例描述的数字，在一些示例中使用了修饰词“大约”、“近似”或“大体上”来修饰。除非另外说明，“大约”、“近似”或“大体上”表明数字允许有±20％的变化。相应地，在一些实施例中，说明书和权利要求中使用的数值参数均为近似值，该近似值根据个别实施例所需特点可以发生改变。在一些实施例中，数值参数应考虑规定的有效数位并采用一般位数保留的方法。尽管本申请一些实施例中用于确认其范围广度的数值域和参数为近似值，在具体实施例中，此类数值的设定在可行范围内尽可能精确。
针对本申请引用的每个专利、专利申请、专利申请公开物和其他材料，如文章、书籍、说明书、出版物、文档等，特此将其全部内容并入本申请作为参考。与本申请内容不一致或产生冲突的申请历史文件除外，对本申请权利要求最广范围有限制的文件(当前或之后附加于本申请中的)也除外。需要说明的是，如果本申请附属材料中的描述、定义、和/或术语的使用与本申请内容有不一致或冲突的地方，以本申请的描述、定义和/或术语的使用为准。
最后，应当理解的是，本申请中实施例仅用以说明本申请实施例的原则。其他的变形也可能属于本申请的范围。因此，作为示例而非限制，本申请实施例的替代配置可视为与本申请的教导一致。相应地，本申请的实施例不仅限于本申请明确介绍和描述的实施例。

Claims (26)

  1. 一种信号采集系统，包括：
    穿戴本体；
    固定于所述穿戴本体并与用户皮肤接触的多个电极，所述多个电极包括第一电极组和第二电极组，所述第一电极组用于采集生理信号，所述第二电极组用于采集检测信号；以及
    处理电路，用于根据所述检测信号消除所述生理信号中的运动伪迹。
  2. 根据权利要求1所述的信号采集系统，其特征在于，所述第一电极组包括间隔布置的两个第一电极，所述第二电极组包括分别靠近所述两个第一电极布置的两个第二电极，所述生理信号为第一生理信号，所述检测信号为第二生理信号，所述处理电路用于根据所述第二生理信号消除所述第一生理信号中的运动伪迹。
  3. 根据权利要求2所述的信号采集系统，其特征在于，所述两个第二电极的材料的导电性不同。
  4. 根据权利要求2或权利要求3所述的信号采集系统，其特征在于，所述两个第二电极相对用户皮肤的凸起沿与用户皮肤表面垂直方向上的高度不同。
  5. 根据权利要求2-4中任意一项所述的信号采集系统，其特征在于，所述两个第二电极的材料的硬度不同，或所述两个第二电极的材料的褶皱程度不同。
  6. 根据权利要求2-5中任意一项所述的信号采集系统，其特征在于，所述两个第二电极的面积不同。
  7. 根据权利要求1所述的信号采集系统，其特征在于，所述第一电极组包括间隔布置的两个第一电极，所述第二电极组包括靠近所述两个第一电极中其中一个第一电极布置的一个第二电极，其中，所述第二电极和与之靠近的所述第一电极用于采集所述检测信号。
  8. 根据权利要求2-7中任意一项所述的信号采集系统，其特征在于，所述每个第二电极的材料比与之对应的第一电极的材料的导电性弱。
  9. 根据权利要求2-8中任意一项所述的信号采集系统，其特征在于，所述每个第二电极相对穿戴本体的凸起比与之对应的第一电极相对穿戴本体的凸起沿与用户皮肤表面垂直方向上的高度小。
  10. 根据权利要求2-9中任意一项所述的信号采集系统，其特征在于，所述每个第二电极的第二材料比与之对应的第一电极的第一材料的硬度大，或者所述每个第二电极的第二材料比与之对应的第一电极的第一材料的褶皱程度大。
  11. 根据权利要求2-10中任意一项所述的信号采集系统，其特征在于，所述每个第二电极与皮肤接触的面积比与之对应的第一电极与皮肤接触的面积小。
  12. 根据权利要求1所述的信号采集系统，其特征在于，所述第一电极组包括间隔布置的两个第一电极，所述第二电极组包括分别靠近所述两个第一电极布置的两个第二电极，所述检测信号为反映所述两个第一电极与用户皮肤之间接触阻抗的检测信号。
  13. 根据权利要求12所述的信号采集系统，其特征在于，还包括与所述两个第二电极电连接的激励源，所述激励源用于提供激励信号。
  14. 根据权利要求13所述的信号采集系统，其特征在于，所述生理信号的频率在20Hz-400Hz范围内，且所述激励信号的频率不小于250Hz。
  15. 根据权利要求14所述的信号采集系统，其特征在于，所述激励信号的频率与50Hz的任一整数倍频的差值不小于1Hz；或者，所述激励信号的频率与60Hz的任一整数倍频的差值不小于1Hz。
  16. 根据权利要求12-15中任意一项所述的信号采集系统，其特征在于，所述激励信号的频率高于所述生理信号的频率范围。
  17. 根据权利要求12所述的信号采集系统，其特征在于，所述检测信号和所述生理信号是在不同的时间段内分别采集的。
  18. 根据权利要求2-17中任意一项所述的信号采集系统，其特征在于，每个第二电极的边缘与对应第一电极的边缘之间的最小距离小于10cm。
  19. 根据权利要求2-18中任意一项所述的信号采集系统，其特征在于，每个第二电极分别与一个第一电极之间通过非弹性连接，且所述第二电极与对应第一电极在与皮肤表面平行的表面上的可移动距离的距离差与对应第一电极在与皮肤表面平行的表面上的可移动距离的比值不大于50％。
  20. 根据权利要求1-19中任意一项所述的信号采集系统，其特征在于，所述处理电路用于：
    差分处理所述两个第一电极采集的信号得到生理信号；
    差分处理所述两个第二电极采集的信号得到检测信号；以及
    根据所述检测信号消除所述生理信号中的运动伪迹。
  21. 根据权利要求1-20中任意一项所述的信号采集系统，其特征在于，还包括惯性传感器，所述惯性传感器设置在所述第一电极组背离用户皮肤的一侧，并用于测量所述第一电极组的运动伪迹。
  22. 一种信号采集系统，包括：
    穿戴本体；
    固定于所述穿戴本体并与用户皮肤接触的多个电极，所述多个电极包括间隔布置以采集生理信号的两个电极；
    与所述两个电极电连接的激励源，所述激励源用于提供激励信号，以产生反映所述两个电极与用户皮肤之间接触阻抗的检测信号；以及
    处理电路，用于根据所述检测信号消除所述生理信号中的运动伪迹。
  23. 根据权利要求22所述的信号采集系统，其特征在于，所述生理信号的频率在20Hz-400Hz范围内，且所述激励信号的频率不小于250Hz。
  24. 根据权利要求22所述的信号采集系统，其特征在于，所述激励信号的频率与50 Hz的任一整数倍频的差值不小于1Hz；或者，所述激励信号的频率与60Hz的任一整数倍频的差值不小于1Hz。
  25. 根据权利要求22-24中任意一项所述的信号采集系统，其特征在于，所述激励信号的频率高于所述生理信号的频率范围。
  26. 根据权利要求22所述的信号采集系统，其特征在于，所述检测信号和所述生理信号是在不同的时间段内分别采集的。
PCT/CN2022/131703 2022-11-14 2022-11-14 信号采集系统 Ceased WO2024103214A1 (zh)

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