High-precision bioelectric sensor

Abstract

The invention relates to the technical field of bioelectricity sensing, in particular to a high-precision bioelectricity sensor which comprises a bioelectricity acquisition module and a control module. The bioelectricity acquisition module is provided with a variable probing electrode, a reference electrode and a signal emission electrode, the variable probing electrode is used for detecting bioelectricity signals, the reference electrode is used for providing reference voltage for the variable probing electrode, and the signal emission electrode is used for outputting impedance detection signals to the body surface skin. The variable probing electrode is provided with an electrode array. The control module judges whether the impedance of the coupling capacitor is matched or not according to the sent impedance detection signal, and if not, the number of element electrodes participating in coupling of the variable probing electrode is adjusted to change the impedance of the variable probing electrode, so that the impedance of the variable probing electrode is matched with the impedance of the reference electrode.

Description

Technical Field

[0001] The present application relates to the field of bioelectric sensing technology, and in particular to a high-precision bioelectric sensor. Background Art

[0002] Wearable physiological monitoring devices are medical devices that integrate biosensors, signal acquisition and processing, data communication and other modules. They can monitor multiple physiological indicators or perform physiological treatments during daily wear.

[0003] In an electrocardiogram monitoring system, ECG signals are generally collected by attaching multiple lead channels to the body surface, setting electrodes at different locations on the human body surface, and calculating the potential difference between two electrodes in the same lead to obtain each waveform in the ECG signal.

[0004] ECG detection devices are divided into two categories: contact and non-contact. Contact devices usually stick wet electrodes on the surface of the human body, which are coated with conductive gel to ensure good contact with the skin. In contrast, non-contact devices use dry electrodes, which are embedded in fabrics and capture ECG signals through the coupling capacitance formed between human skin, fabric and dry electrodes.

[0005] Since non-contact ECG signal detection relies on the coupling capacitance between the sensor and the skin, and the impedance of the coupling capacitance is related to factors such as body surface temperature, humidity, and fabric thickness, it is difficult to match the impedance of the two sensing electrodes in the same lead, resulting in serious baseline offset in the ECG signal.

[0006] In order to complete impedance matching for a non-contact instrument before detecting an electrocardiogram signal, the present application provides a high-precision bioelectric sensor. Summary of the invention

[0007] In order to overcome the problems existing in the related art, the present application provides a high-precision bioelectric sensor, including: a bioelectric acquisition module and a control module;

[0008] The bioelectric acquisition module is provided with a variable detection electrode, a reference electrode and a signal transmitting electrode, wherein the variable detection electrode is used to detect the bioelectric signal, the reference electrode is used to provide a reference voltage to the variable detection electrode, and the signal transmitting electrode is used to output an impedance detection signal to the skin surface of the body;

[0009] The variable probing electrode is provided with an electrode array, and the electrode array is provided with N element electrode assemblies and an element electrode control circuit, and the element electrode control circuit is used to receive the control signal of the control module and control the N element electrode assemblies, where N is an integer greater than or equal to 2;

[0010] The control module is used to control the number of coupled elementary electrode components in the electrode array of the variable probing electrode according to the impedance detection signal.

[0011] In one embodiment, the meta-electrode assembly includes a meta-electrode and a MOS transistor, the source of the MOS transistor is connected to the meta-electrode, the drain of the MOS transistor is connected to the control module, and the gate of the MOS transistor is connected to the meta-electrode control circuit.

[0012] In one embodiment, the control module includes a first amplifying circuit, a second amplifying circuit and a signal transmitting circuit;

[0013] The first amplifying circuit is electrically connected to the variable detecting electrode and is used to collect the voltage of the variable detecting electrode;

[0014] The second amplifier circuit is electrically connected to the reference electrode and is used to collect the voltage of the reference electrode;

[0015] The signal transmitting circuit is electrically connected to the signal transmitting electrode and is used to send the impedance detection signal to the signal transmitting electrode.

[0016] In one embodiment, the control module controls the variable probing electrode based on the following method steps, specifically including:

[0017] S1, controlling the signal transmitting electrode to send the impedance detection signal;

[0018] S2, respectively acquiring a first voltage and a second voltage of the variable probing electrode and the reference electrode;

[0019] S3, calculating a first impedance value and a second impedance value of the variable probing electrode and the reference electrode respectively according to the first voltage and the second voltage;

[0020] S4. Determine whether the first impedance value and the second impedance value match, if so, perform ECG signal detection; if not, adjust the number of the elementary electrode components involved in the coupling.

[0021] In one embodiment, respectively calculating the first impedance value and the second impedance value of the variable probing electrode and the reference electrode according to the first voltage and the second voltage includes:

[0022] The first impedance value is calculated according to a first impedance calculation formula and the first voltage, and the second impedance value is calculated according to a second impedance calculation formula and the second voltage.

[0023] In one implementation, the first impedance calculation formula is:

[0024]

[0025] Among them, Z1 is the impedance of the variable probing electrode, n is the number of connected element electrodes, R1 is the resistance of the element electrode, j is an imaginary unit, f is the frequency of the impedance detection signal, Q1 is the charge of the coupling capacitor of the variable probing electrode, and V1 is the voltage of the variable probing electrode.

[0026] The second impedance calculation formula is:

[0027]

[0028] Among them, Z2 is the impedance of the reference electrode, R2 is the resistance of the reference electrode, j is an imaginary unit, f is the frequency of the impedance detection signal, Q2 is the charge of the coupling capacitor of the reference electrode, and V2 is the voltage of the reference electrode.

[0029] The technical solution provided by this application may have the following beneficial effects:

[0030] In the present application, each electrode in the bioelectric acquisition module is installed on the skin of the body surface, and the signal transmitting electrode is driven to inject the impedance detection signal into the skin of the body surface. After sensing the impedance detection signal, the variable detection electrode and the reference electrode send it to the electrode control module. The control module determines whether the impedance of the coupling capacitor matches according to the impedance detection signal sent by both. If not, the number of element electrodes participating in the coupling of the variable detection electrode is adjusted to change the impedance of the variable detection electrode so that it matches the impedance of the reference electrode.

[0031] It should be understood that the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0032] The above and other objects, features and advantages of the present application will become more apparent through a more detailed description of exemplary embodiments of the present application in conjunction with the accompanying drawings, wherein the same reference numerals generally represent the same components in the exemplary embodiments of the present application.

[0033] Figure 1 This is a schematic diagram of the structure of the high-precision bioelectric sensor shown in the embodiment of the present application;

[0034] Figure 2 for Figure 1 A schematic diagram of a flow chart of control steps executed by a control module of a high-precision bioelectric sensor; and a schematic diagram of a watershed boundary image;

[0035] Description of the accompanying drawings: 1. Bioelectric acquisition module; 10. Variable detection electrode; 11. Reference electrode; 12. Signal transmitting electrode; 101. Meta-electrode assembly; 102. Meta-electrode control circuit; 2. Control module; 201. First amplifying circuit; 202; Second amplifying circuit; 203. Signal transmitting circuit. DETAILED DESCRIPTION

[0036] The preferred embodiments of the present application will be described in more detail below with reference to the accompanying drawings. Although the preferred embodiments of the present application are shown in the accompanying drawings, it should be understood that the present application can be implemented in various forms and should not be limited by the embodiments described herein. On the contrary, these embodiments are provided to make the present application more thorough and complete, and to fully convey the scope of the present application to those skilled in the art.

[0037] The terms used in this application are for the purpose of describing specific embodiments only and are not intended to limit this application. The singular forms of "a", "said" and "the" used in this application and the appended claims are also intended to include plural forms unless the context clearly indicates other meanings. It should also be understood that the term "and / or" used herein refers to and includes any or all possible combinations of one or more associated listed items.

[0038] It should be understood that although the terms "first", "second", "third", etc. may be used in this application to describe various information, this information should not be limited to these terms. These terms are only used to distinguish the same type of information from each other. For example, without departing from the scope of this application, the first information may also be referred to as the second information, and similarly, the second information may also be referred to as the first information. Thus, the features defined as "first" and "second" may explicitly or implicitly include one or more of the features. In the description of this application, the meaning of "multiple" is two or more, unless otherwise clearly and specifically defined.

[0039] The non-contact ECG detection technology is based on the principle of capacitive coupling, which uses the coupling capacitance formed between the skin, fabric and electrodes. When the ECG signal is transmitted to the body surface, the coupling capacitance causes the electrodes to produce a changing potential. Therefore, the non-contact ECG detection technology can be applied to wearable physiological monitoring devices.

[0040] Since non-contact ECG signal detection relies on the coupling capacitance between the sensor and the skin, the impedance of the coupling capacitance is related to factors such as temperature, humidity, electrode installation position, and fabric thickness.

[0041] In order to prevent the impedance mismatch between the detection electrode and the reference electrode, which may cause ECG signal distortion, the present application provides a high-precision bioelectric sensor, such as Figure 1As shown, it includes: a bioelectricity collection module 1 and a control module 2.

[0042] Specifically, the bioelectric acquisition module 1 is provided with a variable detection electrode 10, a reference electrode 11 and a signal transmitting electrode 12. The variable detection electrode 10 is used to detect bioelectric signals, the reference electrode 11 is used to provide a reference voltage to the variable detection electrode 10, and the signal transmitting electrode 12 is used to output an impedance detection signal to the skin surface.

[0043] Further, the variable probing electrode 10 is provided with an electrode array, and the electrode array is provided with N element electrode assemblies 101 and an element electrode control circuit 102, and the element electrode control circuit 102 is used to receive the control signal of the control module 2 and control the N element electrode assemblies 101. It can be understood that N is an integer greater than or equal to 2.

[0044] Furthermore, the control module 2 is used to control the number of element electrode components 101 coupled in the electrode array of the variable probing electrode 10 according to the impedance detection signal.

[0045] When the signal transmitting electrode 12 injects the impedance detection signal into the human skin, the impedance detection signal is transmitted along the human body to the variable detection electrode 10 and the reference electrode 11. The variable detection electrode 10 and the reference electrode 11 sense the impedance detection signal through coupling capacitance, and the control module 2 obtains the potential on the two electrodes, and calculates the impedance between the variable detection electrode 10 and the reference electrode 11 through the potential.

[0046] In order to specifically illustrate the control steps of the control module 2, as shown in FIG. Figure 2 As shown, the control step includes:

[0047] S1, controlling the signal transmitting electrode to send the impedance detection signal;

[0048] S2, respectively acquiring a first voltage and a second voltage of the variable probing electrode and the reference electrode;

[0049] S3, calculating a first impedance value and a second impedance value of the variable probing electrode and the reference electrode respectively according to the first voltage and the second voltage;

[0050] S4. Determine whether the first impedance value and the second impedance value match, if so, perform ECG signal detection; if not, adjust the number of the elementary electrode components involved in the coupling.

[0051] In an embodiment of the present application, each electrode in the bioelectric acquisition module 1 is respectively installed on the skin of the body surface, and the signal emitting electrode 12 is driven to inject the impedance detection signal into the skin of the body surface. After sensing the impedance detection signal, the variable detection electrode 10 and the reference electrode 11 send it to the electrode control module 2. The electrode control module 2 determines whether the impedance of the coupling capacitor matches according to the impedance detection signal sent by both. If not, the number of element electrodes participating in the coupling of the variable detection electrode 10 is adjusted to change the impedance of the variable detection electrode 10 so that it matches the impedance of the reference electrode 11.

[0052] Specifically, the first impedance calculation formula for calculating the impedance value of the variable detection electrode 10 is:

[0053]

[0054] Among them, Z1 is the impedance of the variable probing electrode 10, n is the number of connected element electrodes, R1 is the resistance of the element electrode, j is an imaginary unit, f is the frequency of the impedance detection signal, Q1 is the charge of the coupling capacitor of the variable probing electrode 10, and V1 is the voltage of the variable probing electrode 10.

[0055] Specifically, the second impedance calculation formula for calculating the impedance value of the reference electrode 11 is:

[0056]

[0057] Among them, Z2 is the impedance of the reference electrode 11, R2 is the resistance of the reference electrode 11, j is an imaginary unit, f is the frequency of the impedance detection signal, Q2 is the charge of the coupling capacitor of the reference electrode 11, and V2 is the voltage of the reference electrode 11.

[0058] In the embodiment of the present application, when the impedance does not match, the number of element electrodes of the variable probing electrode 10 connected to the circuit is adjusted, that is, the plate area of ​​the coupling capacitor is changed, and then the charge amount of the coupling capacitor Q1 is changed to adjust the impedance of the variable probing electrode 10.

[0059] It can be understood that the charge amount is obtained by calculating the current and the charging time.

[0060] Furthermore, the control module 2 includes a first amplifying circuit 201, a second amplifying circuit 202 and a signal transmitting circuit 203; the first amplifying circuit 201 is electrically connected to the variable detecting electrode 10 for collecting the voltage of the variable detecting electrode 10; the second amplifying circuit 202 is electrically connected to the reference electrode 11 for collecting the voltage of the reference electrode 11; the signal transmitting circuit 203 is electrically connected to the signal transmitting electrode 12 for sending the impedance detection signal to the signal transmitting electrode 12.

[0061] Furthermore, the meta-electrode assembly 101 includes a meta-electrode and a MOS transistor, the source of the MOS transistor is connected to the meta-electrode, the drain of the MOS transistor is connected to the control module 2 , and the gate of the MOS transistor is connected to the meta-electrode control circuit 102 .

[0062] When the control module 2 needs to adjust the coupling capacitor Q1, a control signal is sent to the element electrode control circuit 102, and the element electrode control circuit 102 turns on or off the element electrode through the gate of the MOS transistor.

[0063] Regarding the device in the above embodiment, the specific way in which each module performs the operation has been described in detail in the embodiment of the method, and will not be elaborated here.

[0064] The scheme of the present application has been described in detail above with reference to the accompanying drawings. In the above embodiments, the description of each embodiment has its own emphasis. For parts that are not described in detail in a certain embodiment, please refer to the relevant description of other embodiments. Those skilled in the art should also be aware that the actions and modules involved in the description are not necessarily required for the present application.

[0065] In addition, it can be understood that the steps in the method of the embodiment of the present application can be adjusted in order, combined and deleted according to actual needs, and the modules in the device of the embodiment of the present application can be combined, divided and deleted according to actual needs.

[0066] In addition, the method according to the present application may also be implemented as a computer program or a computer program product, which includes computer program code instructions for executing some or all of the steps in the above method of the present application.

[0067] Alternatively, the present application can also be implemented as a non-temporary machine-readable storage medium (or computer-readable storage medium, or machine-readable storage medium) on which executable code (or computer program, or computer instruction code) is stored. When the executable code (or computer program, or computer instruction code) is executed by a processor of an electronic device (or electronic device, server, etc.), the processor executes part or all of the steps of the above-mentioned method according to the present application.

[0068] Those skilled in the art will further appreciate that the various illustrative logical blocks, modules, circuits, and algorithm steps described in connection with the application herein may be implemented as electronic hardware, computer software, or a combination of both.

[0069] The flow chart and block diagram in the accompanying drawings show the possible architecture, function and operation of the system and method according to multiple embodiments of the present application. In this regard, each square box in the flow chart or block diagram can represent a part of a module, a program segment or a code, and the part of the module, the program segment or the code contains one or more executable instructions for realizing the specified logical function. It should also be noted that in some alternative implementations, the functions marked in the square box can also occur in a sequence different from that marked in the accompanying drawings. For example, two continuous square boxes can actually be executed substantially in parallel, and they can sometimes be executed in the opposite order, depending on the functions involved. It should also be noted that each square box in the block diagram and / or the flow chart, and the combination of the square boxes in the block diagram and / or the flow chart can be implemented with a dedicated hardware-based system that performs the specified function or operation, or can be implemented with a combination of dedicated hardware and computer instructions.

[0070] The embodiments of the present application have been described above, and the above description is exemplary, not exhaustive, and is not limited to the disclosed embodiments. Many modifications and changes will be apparent to those of ordinary skill in the art without departing from the scope and spirit of the described embodiments. The selection of terms used herein is intended to best explain the principles of the embodiments, practical applications, or improvements to the technology in the market, or to enable other persons of ordinary skill in the art to understand the embodiments disclosed herein.

Claims

1. A high-precision bioelectric sensor, characterized in that: include: Bioelectricity collection module (1) and control module (2); The bioelectric acquisition module (1) is provided with a variable detection electrode (10), a reference electrode (11) and a signal transmitting electrode (12); the variable detection electrode (10) is used to detect bioelectric signals; the reference electrode (11) is used to provide a reference voltage to the variable detection electrode (10); and the signal transmitting electrode (12) is used to output an impedance detection signal to the skin surface of the body; The variable probing electrode (10) is provided with an electrode array, the electrode array is provided with N elementary electrode components (101) and an elementary electrode control circuit (102), the elementary electrode control circuit (102) is used to receive a control signal from the control module (2) and control the N elementary electrode components (101), N being an integer greater than or equal to 2; The control module (2) is used to control the number of elementary electrode components (101) coupled in the electrode array of the variable probing electrode (10) according to the impedance detection signal.

2. A high-precision bioelectric sensor according to claim 1, characterized in that: The meta-electrode assembly (101) comprises a meta-electrode and a MOS transistor, the source of the MOS transistor is connected to the meta-electrode, the drain of the MOS transistor is connected to the control module (2), and the gate of the MOS transistor is connected to the meta-electrode control circuit (102).

3. A high-precision bioelectric sensor according to claim 1, characterized in that: The control module (2) comprises a first amplifying circuit (201), a second amplifying circuit (202) and a signal transmitting circuit (203); The first amplifying circuit (201) is electrically connected to the variable detection electrode (10) and is used to collect the voltage of the variable detection electrode (10); The second amplifier circuit (202) is electrically connected to the reference electrode (11) and is used to collect the voltage of the reference electrode (11); The signal transmitting circuit (203) is electrically connected to the signal transmitting electrode (12) and is used to transmit the impedance detection signal to the signal transmitting electrode (12).

4. A high-precision bioelectric sensor according to claim 1, characterized in that: The control module (2) controls the variable detection electrode (10) based on the following method steps, specifically comprising: S1, controlling the signal transmitting electrode to send the impedance detection signal; S2, respectively acquiring a first voltage and a second voltage of the variable probing electrode and the reference electrode; S3, calculating a first impedance value and a second impedance value of the variable probing electrode and the reference electrode respectively according to the first voltage and the second voltage; S4. Determine whether the first impedance value and the second impedance value match, if so, perform ECG signal detection; if not, adjust the number of the elementary electrode components involved in the coupling.

5. A high-precision bioelectric sensor according to claim 4, characterized in that: The calculating the first impedance value and the second impedance value of the variable probing electrode and the reference electrode respectively according to the first voltage and the second voltage specifically includes: The first impedance value is calculated according to a first impedance calculation formula and the first voltage, and the second impedance value is calculated according to a second impedance calculation formula and the second voltage.

6. A high-precision bioelectric sensor according to claim 5, characterized in that: The first impedance calculation formula is: Wherein, Z1 is the impedance of the variable detection electrode, n is the number of connected element electrodes, R1 is the resistance of the element electrode, j is an imaginary unit, f is the frequency of the impedance detection signal, Q1 is the charge of the coupling capacitor of the variable detection electrode, and V1 is the voltage of the variable detection electrode; The second impedance calculation formula is: Among them, Z2 is the impedance of the reference electrode, R2 is the resistance of the reference electrode, j is an imaginary unit, f is the frequency of the impedance detection signal, Q2 is the charge of the coupling capacitor of the reference electrode, and V2 is the voltage of the reference electrode.

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