CN106691432B - Induction type electrocardio measuring method and device - Google Patents
Induction type electrocardio measuring method and device Download PDFInfo
- Publication number
- CN106691432B CN106691432B CN201610910648.1A CN201610910648A CN106691432B CN 106691432 B CN106691432 B CN 106691432B CN 201610910648 A CN201610910648 A CN 201610910648A CN 106691432 B CN106691432 B CN 106691432B
- Authority
- CN
- China
- Prior art keywords
- digital
- electrocardiosignal
- analog
- electrocardiosignals
- filtering
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
-
- 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
-
- 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
- A61B5/6844—Monitoring or controlling distance between sensor and tissue
-
- 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
Abstract
The invention discloses an induction type electrocardio measuring method and device, wherein the method comprises the following steps: the potential field sensor outputs an initial electrocardiosignal; performing front-end filtering amplification; analog-to-digital conversion is carried out; digital signal processing is carried out; performing digital-to-analog conversion; dividing voltage through an external resistor network; the back-end analog electrocardiosignals are obtained through back-end filtering and amplification; obtaining a rear-end digital electrocardiosignal after analog-to-digital conversion; and the main controller processes the rear-end digital electrocardiosignal to obtain an electrocardio parameter. An induction type electrocardio measuring method and device are used, and an Ag/AgCl electrode is not required to be adhered; the initial electrocardiosignal output by the potential field sensor in the induction type electrocardiosignal probe is subjected to front end filtering amplification, digital signal processing and external resistance network to divide pressure, and then effective signals are extracted through a circuit of a later stage. The external resistor network simulates the impedance of limbs of a human body, can improve the input impedance of electrocardio, has higher common mode rejection ratio and has stronger anti-interference capability.
Description
Technical Field
The invention relates to the field of medical equipment, in particular to electrocardiographic measurement equipment based on body surface space potential.
Background
The electrocardiograph is an important index for representing health conditions, and most of the existing electrocardiograph is a measuring device based on a lead method, and when the electrocardiograph is used, a plurality of electrodes are required to be respectively arranged at specific positions on a human body, and the measuring device is required to be connected with an electrocardiograph to trace an electrocardiogram. The traditional electrocardiograph measurement method is that an Ag/AgCl electrode is stuck on the body of a patient, the electrode and a detection instrument are connected by a lead wire, and the display and the printing are carried out after the amplification and the filtering, so that the method is used as the basis of diagnosing the illness state of the patient by a doctor. However, some patients are not suitable for sticking electrodes, such as neonates, burn patients, etc., and may be troublesome to the monitoring subject and the doctor.
Patent document publication No. CN201220073456.7 discloses an electrocardiograph based on body surface space potential, which is provided with one or two polar plates of coupling capacitance for sensing the magnitude of weak electric field around the body surface of the measured human body and the change thereof, a charge amplifier for converting the charge quantity accumulated on the polar plates into voltage quantity and amplifying, and a signal conditioning circuit for amplifying and filtering the voltage signal output by the charge amplifier. However, there is a problem that the signal processing process is complicated and is easily interfered by clutter.
Disclosure of Invention
In order to overcome the defects of the prior art, the invention aims to provide an induction type electrocardiograph measurement method and device, which can solve the problems that the conventional electrocardiograph measurement method needs to paste Ag/AgCl electrodes on the body of a patient, the signal processing process of the conventional electrocardiograph measurement device based on the body surface space potential is complex, the polar plates are easily influenced by humidity, dust and the like, and the analog-digital conversion accuracy is poor.
The invention adopts the following technical scheme:
an induction type electrocardiograph measurement method, comprising the following steps:
the potential field sensor outputs an initial electrocardiosignal;
the initial electrocardiosignal is subjected to front-end filtering amplification;
performing analog-to-digital conversion on the initial electrocardiosignals after filtering and amplifying to obtain front-end digital electrocardiosignals;
performing digital signal processing on the front-end digital electrocardiosignals;
performing digital-to-analog conversion on the front-end digital electrocardiosignals subjected to digital signal processing to obtain front-end analog electrocardiosignals;
the front-end simulation electrocardiosignals are subjected to voltage division through an external resistance network to obtain limb electrocardiosignals;
performing back-end filtering amplification on the limb electrocardiosignals to obtain back-end simulation electrocardiosignals;
performing analog-to-digital conversion on the back-end analog electrocardiosignal to obtain a back-end digital electrocardiosignal;
and the main controller processes the rear-end digital electrocardiosignal to obtain an electrocardio parameter.
Preferably, the induction type electrocardiograph measurement method further comprises: and carrying out differential amplification on the initial electrocardiosignal to obtain a feedback signal, wherein the feedback signal is used as an electrocardio reference potential.
Preferably, the performing back-end filtering amplification on the limb electrocardiosignal specifically includes: and filtering, amplifying, differentiating, re-filtering and re-amplifying the limb electrocardiosignals.
Preferably, the performing digital signal processing on the front-end digital electrocardiograph signal specifically includes: and carrying out digital filtering and digital difference on the front-end digital electrocardiosignal.
Preferably, the potential field sensor outputs an initial electrocardiosignal, and in particular, the potential field sensor selected by the first analog switch outputs the initial electrocardiosignal;
before the front-end simulation electrocardiosignal is subjected to voltage division through an external resistance network, the method further comprises the following steps: an external resistor network port is selected by a second analog switch.
An induction electrocardiograph device, comprising:
the potential field sensor is used for outputting an initial electrocardiosignal;
the front-end filtering and amplifying unit is used for performing front-end filtering and amplifying on the initial electrocardiosignal;
the front-end analog-to-digital conversion unit is used for converting the initial electrocardiosignal after front-end filtering amplification into a front-end digital electrocardiosignal;
the digital signal processing unit is used for carrying out digital signal processing on the front-end digital electrocardiosignals;
the front-end digital-to-analog conversion unit is used for converting the front-end digital electrocardiosignals processed by the digital signals into front-end analog electrocardiosignals;
the external resistor network is used for dividing the front-end simulation electrocardiosignal to obtain a limb electrocardiosignal;
the back-end filtering and amplifying unit is used for carrying out back-end filtering and amplifying on the limb electrocardiosignals to obtain back-end analog electrocardiosignals;
the back-end analog-to-digital conversion unit is used for converting the back-end analog electrocardiosignal into a back-end digital electrocardiosignal;
and the main controller is used for processing the rear-end digital electrocardiosignal to obtain electrocardio parameters.
Preferably, the induction type electrocardiograph measurement device further comprises a feedback unit, wherein the feedback unit differentially amplifies the initial electrocardiograph signal subjected to front-end filtering amplification to serve as a feedback signal serving as an electrocardiograph reference potential.
The back-end filtering and amplifying unit preferably comprises a filtering component, an amplifying component, a differential component, a re-filtering component and a re-amplifying component, and the filtering component, the amplifying component, the differential component, the re-filtering component and the re-amplifying component are electrically connected in sequence.
Preferably, the digital signal processing unit includes a digital filtering part and a digital differentiating part, and the digital filtering part and the digital differentiating part are electrically connected.
Preferably, the induction electrocardiograph measurement device further includes:
and the first analog switch is used for switching the potential field sensor and is electrically connected with the potential field sensor and the front-end filtering and amplifying unit.
The second analog switch is used for selecting an external resistance network port corresponding to the front-end analog electrocardiosignal and is electrically connected with the front-end digital-to-analog conversion unit and the external resistance network.
Compared with the prior art, the invention has the beneficial effects that: by using the induction type electrocardio measuring method and device, the electrocardio detection can be conveniently carried out by directly contacting the skin or contacting the skin through clothes without pasting an Ag/AgCl electrode; the initial electrocardiosignal output by the potential field sensor in the induction type electrocardiosignal probe is subjected to front end filtering amplification, digital signal processing and external resistance network to divide pressure, and then effective signals are extracted through a circuit of a later stage. The external resistor network simulates the impedance of limbs of a human body, can improve the input impedance of electrocardio, has higher common mode rejection ratio and has stronger anti-interference capability.
Drawings
Fig. 1 is a flow chart of an induction type electrocardiograph measurement method according to an embodiment of the present invention;
fig. 2 is a flow chart of an induction type electrocardiograph measurement method according to a second embodiment of the present invention;
FIG. 3 is a schematic flow diagram of the back-end filter amplification of FIGS. 1 and 2;
FIG. 4 is a schematic flow diagram of the digital signal processing of FIGS. 1 and 2;
FIG. 5 is a schematic structural diagram of an induction electrocardiograph device according to a third embodiment of the present invention;
FIG. 6 is a schematic structural diagram of an induction electrocardiograph device according to a fourth embodiment of the present invention;
Detailed Description
The foregoing description is only an overview of the present invention, and is intended to be implemented in accordance with the teachings of the present invention, as well as the preferred embodiments thereof, together with the following detailed description of the invention, given by way of illustration only, together with the accompanying drawings.
Embodiment one:
the induction type electrocardiograph measuring method shown in fig. 1 comprises the following steps:
s101, outputting an initial electrocardiosignal by the electric potential field sensor.
The electric potential field sensor can realize that electrocardiographic measurement is very simple, does not need to be wound by a plurality of wires, does not need to lie on a special sickbed, does not need to paint conductive liquid on skin, and only needs to measure alternating current signals in space by using the electric potential field sensor through a medium (such as clothes, cotton cloth, gauze and the like).
S102, performing front-end filtering amplification on an initial electrocardiosignal; the front-end filter amplification converts weak potential field signals into voltage signals.
S103, carrying out analog-to-digital conversion on the initial electrocardiosignals after filtering and amplifying to obtain front-end digital electrocardiosignals;
s104, performing digital signal processing on the front-end digital electrocardiosignals;
the voltage signal obtained in S102 has high noise, and after the front end analog-digital conversion and the digital signal processing (typically, a single chip microcomputer or DSP) process, the voltage signal (or the physiological electrical signal of the human body) has a certain cone shape.
S105, performing digital-to-analog conversion on the front-end digital electrocardiosignals subjected to digital signal processing to obtain front-end analog electrocardiosignals;
s106, dividing the front-end simulation electrocardiosignal through an external resistance network to obtain a limb electrocardiosignal;
the design of the external resistance network simulates the impedance principle of the limbs of the human body, so that weak electrocardiosignals corresponding to the heart activities of the human body are output by digital-to-analog conversion at the front end, and the electrocardiosignals pass through the external resistance network (compared with the limb impedance of the human body), namely differential voltage differences are generated, the differential voltage differences of the human body electrical signals are generated, and the subsequent extraction of useful signals is facilitated
S107, performing back-end filtering amplification on the limb electrocardiosignals to obtain back-end simulation electrocardiosignals;
s108, performing analog-to-digital conversion on the rear-end analog electrocardiosignal to obtain a rear-end digital electrocardiosignal;
and S109, the main controller processes the digital electrocardiosignals at the rear end to obtain electrocardiosignals.
The digital electrocardiosignals at the rear end are transmitted to the main controller for processing. And outputting electrocardio waveform signals, heart rate values and other electrocardio parameters after being processed by a filtering algorithm, a gain control algorithm, an electrocardio signal QRS wave extraction algorithm, a heart rate calculation algorithm and the like of the main controller.
Embodiment two:
the induction electrocardiographic measurement method shown in fig. 2, S201 to S209 correspond to S101 to S109 in the first embodiment in order, and the second embodiment differs from the first embodiment in that the method further includes the following steps:
s2011, the first analog switch selects a potential field sensor, namely the potential field sensor in S201 outputs an initial electrocardiosignal, and specifically the potential field sensor with the first analog switch on outputs the initial electrocardiosignal;
s2061, selecting an external resistor network port through a second analog switch, namely before the front-end analog electrocardiosignal is divided by the external resistor network in S206, further comprises: an external resistor network port is selected by a second analog switch.
The first analog switch and the second analog switch can realize the selection of the electrocardiosignal of the corresponding potential field sensor to be processed by the induction type electrocardio measuring device.
S2022, the initial electrocardiosignal is filtered and amplified at the front end and then is amplified by differential amplification to obtain a feedback signal, and the feedback signal is used as an electrocardio reference potential, so that interference of factors such as static electricity and the like can be eliminated.
As shown in fig. 3, the back-end filtering amplification specifically includes: the limb electrocardiosignals are filtered S2071, amplified S2072, differential S2073, re-filtered S2074 and re-amplified S2075.
As shown in fig. 4, the digital signal processing includes digital filtering S2041, digital differencing S2042.
Embodiment III:
an induction type electrocardiograph measuring device as shown in fig. 5, comprising:
a potential field sensor 101 for outputting an initial electrocardiographic signal;
the front-end filtering and amplifying unit 102 is used for performing front-end filtering and amplifying on the initial electrocardiosignal;
the front-end analog-to-digital conversion unit 103 is configured to convert the front-end filtered and amplified initial electrocardiographic signal into a front-end digital electrocardiographic signal;
a digital signal processing unit 104, configured to perform digital signal processing on the front-end digital electrocardiograph signal;
a front-end digital-to-analog conversion unit 105, configured to convert the front-end digital electrocardiograph signal after digital signal processing into a front-end analog electrocardiograph signal;
an external resistor network 106, configured to divide the front-end analog electrocardiograph signal to obtain a limb electrocardiograph signal;
the back-end filtering and amplifying unit 107 is configured to perform back-end filtering and amplifying on the limb electrocardiosignal to obtain a back-end analog electrocardiosignal;
the back-end analog-to-digital conversion unit 108 is configured to convert the back-end analog electrocardiograph signal into a back-end digital electrocardiograph signal;
and the main controller 109 is used for processing the back-end digital electrocardiosignal to obtain electrocardio parameters.
The potential field sensor 101 may be provided on the electrocardiographic probe, or may be mounted at a corresponding position on a hospital bed or chair. The potential field sensor 101 can realize that electrocardiographic measurement is simple, a plurality of wires are not required to be wound, a patient is not required to lie on a special sickbed, a conductive liquid is not required to be smeared on skin, and only alternating current signals in a space are required to be measured by the potential field sensor 101 through a medium (such as clothes, cotton cloth, gauze and the like). The frequency range of the detection signal is different from 0.05Hz to 200MHz, the frequency range control can be adjusted through programming, the output signal of the sensor is a square wave signal, and the bandwidth is from 0.5 Hz to 40Hz.
In one implementation, a high-precision analog device (including a front-end filter amplification unit 102) integrated inside a programmable system on a chip (PSOC) converts a weak electric potential field signal into a voltage signal, and when the voltage signal is very noisy, after being processed by a front-end analog-to-digital conversion unit 103 and a digital signal processing unit 104 (typically a single chip microcomputer or a DSP), the voltage signal (or a physiological electric signal of a human body) has a certain cone shape, and the front-end digital-to-analog conversion unit 105 converts the digital signal into an analog signal. The design of the external resistor network 106 simulates the impedance principle of the limbs of the human body, so that the electrocardiosignal is weaker than the front-end digital-to-analog conversion unit 105 which outputs the weak electrocardiosignal corresponding to the heart activity of the human body, and the electrocardiosignal passes through the external resistor network 106 (better than the limb impedance of the human body), namely, a differential voltage difference is generated, the differential voltage of the human body electrical signal is generated, and the useful signal can be extracted more effectively by a simulation hardware circuit at the later stage.
Embodiment four:
the induction type electrocardiograph apparatus as shown in fig. 6, 201 to 209 correspond in sequence to 101 to 109 in the third embodiment, in which 202 includes a filter and an amplifier.
The back-end filter amplification unit 207 includes a filter part 2071, an amplification part 2072, a differential part 2073, a re-filter part 2074, and a re-amplification part 2075, and the filter part 2071, the amplification part 2072, the differential part 2073, the re-filter part 2074, and the re-amplification part 2075 are electrically connected in this order. The back-end filtering and amplifying unit 207 may be formed by discrete components, and the analog hardware circuit performs a series of conditioning circuits such as filtering, amplifying, differentiating, re-filtering, re-amplifying on the signal input by the external resistor network 206, and then samples the signal by the back-end analog-to-digital converting unit 208, so as to complete the process of extracting the analog signal. The electrocardiosignal is processed by a filtering algorithm, a gain control algorithm, an electrocardiosignal QRS wave extraction algorithm, a heart rate calculation algorithm and the like of the main controller 209, and then parameters such as an electrocardiosignal signal, a heart rate value and the like are output. The induction electrocardiograph device further comprises an interaction unit 210, which comprises a display, a printer, a keyboard and other output and input devices, and the interaction unit is typically a monitor upper computer.
The digital signal processing unit 204 includes a digital filtering section and a digital differentiating section, which are electrically connected.
The induction type electrocardiograph device further includes a feedback unit 2022, and the feedback unit 2022 differentially amplifies the initial electrocardiograph signal after the front-end filtering amplification as a feedback signal serving as an electrocardiograph reference potential.
The induction electrocardiograph device further comprises a first analog switch 2011 for switching the electric potential field sensor 201, and the first analog switch 2011 is electrically connected to the electric potential field sensor 201 and the front-end filtering amplifying unit 202.
The second analog switch 2061 is used for selecting a port of the external resistor network 206 corresponding to the front-end analog electrocardiograph signal, and the second analog switch 2061 is electrically connected to the front-end digital-to-analog conversion unit 205 and the external resistor network 206.
The first analog switch 2011 and the second analog switch 2061 may implement selecting the corresponding electrical potential field sensor 201 of the induction type electrocardiograph device to process. Preferably, the induction type electrocardiograph comprises 3, 4, 5, 7 or 10 potential field sensors 201 for testing potential signals at different positions to realize multi-lead electrocardiograph parameters. When 3 potential field sensors 201 are included, the potential field sensors 201 are respectively mounted on the Left Arm (LA), the Right Arm (RA) and the Left Leg (LL), and the potential differences between the points LA and RA, LL and RA, and LL and LA are respectively referred to as standard I, II, III leads. The feedback signal output by the feedback unit 2022 serves as an electrocardiographic reference potential, which is equivalent to a conventional right leg driving circuit. The preferred feedback unit 2022 outputs a feedback signal to the conductive cloth on which a person sits to eliminate interference from factors such as static electricity. The digital signal processing unit 204 may adjust the gain of the amplifier in the feedback unit 2022. Alternatively, a potential field sensor 201 is also mounted on the right leg, that is to say the induction electrocardiograph comprises 4 potential field sensors 201.
Various other corresponding changes and modifications will occur to those skilled in the art from the foregoing description and the accompanying drawings, and all such changes and modifications are intended to be included within the scope of the present invention as defined in the appended claims.
Claims (10)
1. An induction type electrocardiograph measurement method is characterized by comprising the following steps:
the potential field sensor outputs an initial electrocardiosignal;
the initial electrocardiosignal is subjected to front-end filtering amplification;
performing analog-to-digital conversion on the initial electrocardiosignals after filtering and amplifying to obtain front-end digital electrocardiosignals;
performing digital signal processing on the front-end digital electrocardiosignals;
performing digital-to-analog conversion on the front-end digital electrocardiosignals subjected to digital signal processing to obtain front-end analog electrocardiosignals;
the front-end simulation electrocardiosignals are subjected to voltage division through an external resistance network to obtain limb electrocardiosignals;
performing back-end filtering amplification on the limb electrocardiosignals to obtain back-end simulation electrocardiosignals;
performing analog-to-digital conversion on the back-end analog electrocardiosignal to obtain a back-end digital electrocardiosignal;
and the main controller processes the rear-end digital electrocardiosignal to obtain an electrocardio parameter.
2. The method of inductive electrocardiographic measurement according to claim 1, further comprising:
and carrying out differential amplification on the initial electrocardiosignal to obtain a feedback signal, wherein the feedback signal is used as an electrocardio reference potential.
3. The method of inductive electrocardiographic measurement according to claim 1, wherein:
the performing back-end filtering amplification on the limb electrocardiosignals specifically comprises the following steps: and filtering, amplifying, differentiating, re-filtering and re-amplifying the limb electrocardiosignals.
4. The method of inductive electrocardiographic measurement according to claim 1, wherein:
the digital signal processing of the front-end digital electrocardiosignal specifically comprises the following steps: and carrying out digital filtering and digital difference on the front-end digital electrocardiosignal.
5. The method of inductive electrocardiographic measurement according to claim 1, wherein:
the potential field sensor outputs an initial electrocardiosignal, and particularly the potential field sensor selected by the first analog switch outputs the initial electrocardiosignal;
before the front-end simulation electrocardiosignal is subjected to voltage division through an external resistance network, the method further comprises the following steps: an external resistor network port is selected by a second analog switch.
6. An induction electrocardiograph device, comprising:
the potential field sensor is used for outputting an initial electrocardiosignal;
the front-end filtering and amplifying unit is used for performing front-end filtering and amplifying on the initial electrocardiosignal;
the front-end analog-to-digital conversion unit is used for converting the initial electrocardiosignal after front-end filtering amplification into a front-end digital electrocardiosignal;
the digital signal processing unit is used for carrying out digital signal processing on the front-end digital electrocardiosignals;
the front-end digital-to-analog conversion unit is used for converting the front-end digital electrocardiosignals processed by the digital signals into front-end analog electrocardiosignals;
the external resistor network is used for dividing the front-end simulation electrocardiosignal to obtain a limb electrocardiosignal;
the back-end filtering and amplifying unit is used for carrying out back-end filtering and amplifying on the limb electrocardiosignals to obtain back-end analog electrocardiosignals;
the back-end analog-to-digital conversion unit is used for converting the back-end analog electrocardiosignal into a back-end digital electrocardiosignal;
the main controller is used for processing the rear-end digital electrocardiosignals to obtain electrocardiosignals;
the electric potential field sensor is arranged on an electrocardiograph probe or is arranged on a sickbed or a chair.
7. The induction electrocardiograph device according to claim 6, wherein:
the device also comprises a feedback unit, wherein the feedback unit differentially amplifies the initial electrocardiosignal filtered and amplified at the front end and is used as a feedback signal used as an electrocardio reference potential.
8. The induction electrocardiograph device according to claim 6, wherein:
the back-end filtering and amplifying unit comprises a filtering component, an amplifying component, a differential component, a re-filtering component and a re-amplifying component, and the filtering component, the amplifying component, the differential component, the re-filtering component and the re-amplifying component are electrically connected in sequence.
9. The induction electrocardiograph device according to claim 6, wherein:
the digital signal processing unit comprises a digital filtering component and a digital differential component, and the digital filtering component and the digital differential component are electrically connected.
10. The inductive electrocardiograph device according to claim 6, further comprising:
the first analog switch is used for switching the potential field sensor and is electrically connected with the potential field sensor and the front-end filtering and amplifying unit;
the second analog switch is used for selecting an external resistance network port corresponding to the front-end analog electrocardiosignal and is electrically connected with the front-end digital-to-analog conversion unit and the external resistance network.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610910648.1A CN106691432B (en) | 2016-10-19 | 2016-10-19 | Induction type electrocardio measuring method and device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610910648.1A CN106691432B (en) | 2016-10-19 | 2016-10-19 | Induction type electrocardio measuring method and device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN106691432A CN106691432A (en) | 2017-05-24 |
| CN106691432B true CN106691432B (en) | 2023-04-21 |
Family
ID=58940266
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201610910648.1A Active CN106691432B (en) | 2016-10-19 | 2016-10-19 | Induction type electrocardio measuring method and device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN106691432B (en) |
Family Cites Families (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1124823C (en) * | 1995-07-28 | 2003-10-22 | 北京新兴生物医学工程研究发展中心 | Standard cardioelectric lead meauring method without wilson network |
| DK199901006A (en) * | 1999-07-09 | 2001-01-10 | Telital R & D Denmark As | Digital to analog conversion device |
| US6611705B2 (en) * | 2000-07-18 | 2003-08-26 | Motorola, Inc. | Wireless electrocardiograph system and method |
| JP2002224069A (en) * | 2001-02-07 | 2002-08-13 | Japan Science & Technology Corp | Body surface multi-lead electrocardiogram device and analytical method using this device |
| CN101524272B (en) * | 2008-03-04 | 2011-08-31 | 李平 | Digital pick-up device for body surface cardiac electric signals |
| US9351654B2 (en) * | 2010-06-08 | 2016-05-31 | Alivecor, Inc. | Two electrode apparatus and methods for twelve lead ECG |
| CN102599901A (en) * | 2012-02-10 | 2012-07-25 | 无锡先凯智能科技有限公司 | Physiological weak current signal acquiring and processing system and device |
| CN103239222A (en) * | 2013-04-17 | 2013-08-14 | 深圳市科曼医疗设备有限公司 | Electrocardio signal acquisition device and method |
| CN104490387B (en) * | 2014-09-17 | 2016-09-21 | 中国科学院上海微系统与信息技术研究所 | Wireless portable and the Wearable ECG detector of motion artifacts can be suppressed |
| CN107205678B (en) * | 2014-09-23 | 2019-11-29 | Rr图形逻辑有限公司 | Contactless electrocardiogram system |
| CN104382583B (en) * | 2014-11-12 | 2016-11-02 | 深圳市理邦精密仪器股份有限公司 | A kind of 18 harvester leading electrocardiosignal and methods thereof |
| CN204581270U (en) * | 2015-04-20 | 2015-08-26 | 深圳市杰纳瑞医疗仪器股份有限公司 | A kind of vicarious cardiographic detector |
| CN206534637U (en) * | 2016-10-19 | 2017-10-03 | 深圳市杰纳瑞医疗仪器股份有限公司 | Induction type pressure electrocardio measuring device |
-
2016
- 2016-10-19 CN CN201610910648.1A patent/CN106691432B/en active Active
Also Published As
| Publication number | Publication date |
|---|---|
| CN106691432A (en) | 2017-05-24 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| KR101736978B1 (en) | Apparatus and method for measuring biological signal | |
| CN101194836B (en) | Method and device for eliminating interference in bio-electrical impedance measurement | |
| CN109171702A (en) | A kind of measuring device and measurement method of contactless electrocardiosignal | |
| Su et al. | Wireless ECG detection system with low-power analog front-end circuit and bio-processing ZigBee firmware | |
| CN110840454B (en) | Electroencephalogram signal acquisition device and method | |
| WO2018167523A1 (en) | System and method for emg signal acquisition | |
| CN101822540A (en) | Myoelectricity amplifier and method for sampling myoelectricity signals | |
| CN110338790A (en) | A kind of flexible fingerstall for collection surface myoelectricity and a variety of physiological parameters | |
| WO2018162365A1 (en) | Physiological measurement device with common mode interference suppression | |
| CN105232034A (en) | Electrode and circuit multiplex structure for detecting electrocardiograph signals and human impedance | |
| CN112401898B (en) | High-precision electroencephalogram signal acquisition method and device | |
| JP4063349B2 (en) | Cardiac monitoring system and method | |
| CN106691432B (en) | Induction type electrocardio measuring method and device | |
| CN110384496B (en) | Wearable multi-parameter measuring instrument | |
| CN204581270U (en) | A kind of vicarious cardiographic detector | |
| CN107212863A (en) | Human heart bounce impact force detection system | |
| CN217907965U (en) | Irreversible electroporation therapy apparatus | |
| CN106510691A (en) | Electrocardiograph signal acquisition front end | |
| Sandra et al. | Simulation study of a contactless, capacitive ECG system | |
| Szakacs-Simon et al. | Signal conditioning techniques for health monitoring devices | |
| CN206534637U (en) | Induction type pressure electrocardio measuring device | |
| CN104188651A (en) | Electrocardiogram monitoring device and control method of electrocardiogram monitoring device | |
| Stork et al. | Non-contact ECG Monitoring for Driver | |
| RU174958U1 (en) | Biopotential Amplifier with Electrode Break Diagnostics | |
| CN206261586U (en) | Electromyographic signal collection circuit and Wearable device |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |