CN205338955U - Physiological signal's monitoring system - Google Patents
Physiological signal's monitoring system Download PDFInfo
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- CN205338955U CN205338955U CN201521126097.7U CN201521126097U CN205338955U CN 205338955 U CN205338955 U CN 205338955U CN 201521126097 U CN201521126097 U CN 201521126097U CN 205338955 U CN205338955 U CN 205338955U
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- 238000012544 monitoring process Methods 0.000 title claims abstract description 56
- 230000036391 respiratory frequency Effects 0.000 claims abstract description 5
- 230000000241 respiratory effect Effects 0.000 claims description 38
- 238000005259 measurement Methods 0.000 claims description 13
- 238000001514 detection method Methods 0.000 claims description 8
- 238000006243 chemical reaction Methods 0.000 claims description 6
- 238000000034 method Methods 0.000 claims description 5
- 238000005086 pumping Methods 0.000 claims description 4
- 230000003321 amplification Effects 0.000 claims description 3
- 238000003199 nucleic acid amplification method Methods 0.000 claims description 3
- 238000001914 filtration Methods 0.000 abstract description 3
- 230000005611 electricity Effects 0.000 abstract 2
- 230000029058 respiratory gaseous exchange Effects 0.000 description 10
- 238000010586 diagram Methods 0.000 description 8
- 210000000115 thoracic cavity Anatomy 0.000 description 7
- 230000002685 pulmonary effect Effects 0.000 description 5
- 238000006073 displacement reaction Methods 0.000 description 2
- 238000000605 extraction Methods 0.000 description 2
- 239000007789 gas Substances 0.000 description 2
- 238000012545 processing Methods 0.000 description 2
- 238000004088 simulation Methods 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 210000004072 lung Anatomy 0.000 description 1
- 230000001131 transforming effect Effects 0.000 description 1
- 238000009423 ventilation Methods 0.000 description 1
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- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
The utility model provides a physiological signal's monitoring system, includes measuring electrode and breathes wave form monitoring passageway that its characterized in that includes: modulated circuit, demodulation circuit and a low pass filter of signal source and order connection, measuring electrode is used for with skin exposure by monitoring person and detects the signal of telecommunication, the signal source is used for providing preset frequency's alternating current signal, the signal source is connected with the measuring electrode electricity, provides the drive signal who inputs by monitoring person for measuring electrode, modulated circuit is connected with measuring electrode and signal source electricity respectively, and the signal of telecommunication that detects the signal I (Fc) and the measuring electrode of signal source output carries out amplitude modulation, export make after the signal, the demodulation circuit carries out demodulation, signal after the output demodulation to modulating the back signal, low pass filter has the frequency bandwidth that matches with respiratory frequency, carries out being breathed the signal after filtering is handled to signal after the demodulation. Breathe wave form monitoring passageway and electrocardio wave form monitoring passageway sharing measuring electrode.
Description
Technical field
The present invention relates to the monitoring system of physiological signal, be specifically related to the monitoring system of a kind of respiratory waveform based on impedance detection.
Background technology
The current monitoring to respiratory waveform is by the extraction of ecg wave form is realized.In the monitoring to ecg wave form, owing to respiratory movement can cause the displacement of electrode and skin contact region, thus baseline drift can be caused, then pass through and the baseline drift in ecg wave form is extracted, it is possible to obtain the respiratory waveform being similar to.
This technical scheme is such as suitable in comparing the quiet patient dossed clinic.But, this technical scheme not can effectively solve the problem that due to the interference that respiratory waveform is extracted by the baseline drift that brings of moving, for instance for active neonate or the people in being kept in motion.Reason is in that monitored person is when motion, also result in the displacement of electrode and skin contact region equally, and the baseline drift thus brought overlaps with respiratory waveform frequency range in frequency range, thus being difficult to extract respiratory waveform from motion artifacts, and then it is wrong to cause that respiratory waveform gathers.
Summary of the invention
For this problem, the present invention proposes the monitoring system of a kind of respiratory waveform based on impedance detection.The inventive concept of the present invention is: in whole respiratory, upon exhalation, and pulmonary gases reduces, and the equiva lent impedance of whole pulmonary reduces；During air-breathing, pulmonary gases increases, and the equiva lent impedance of whole pulmonary increases, from there through the equiva lent impedance size of monitoring pulmonary, it is possible to obtain respiratory waveform accurately, including frequency and respiratory depth (relative ventilation volume number).
A kind of respiratory waveform based on impedance detection is provided to monitor system in an embodiment, including measuring electrode and respiratory waveform monitoring channel, it is characterized in that, described respiratory waveform monitoring channel includes: signal source and the modulation circuit, demodulator circuit and the first low pass filter that are linked in sequence；Measure electrode be used for the contact skin with monitored person and detect the signal of telecommunication；Signal source is for providing the AC signal of preset frequency, and described signal source electrically connects with measuring electrode, provides input directly to the pumping signal of monitored person for measuring electrode；Modulation circuit electrically connects with measurement electrode and signal source respectively, and the signal of telecommunication that the signal I (Fc) export signal source and measurement electrode detect carries out amplitude modulation(PAM), signal after output modulation；Signal after modulation is demodulated by demodulator circuit, signal after output demodulation；Low pass filter has the frequency bandwidth mated with respiratory frequency, and after being filtered process, signal after demodulation is obtained breath signal.
Further, signal source is current source, and what measure electrode detection is voltage signal.
Further, the frequency of current source output signal is more than 1KHz.
Further, signal source includes the first signal source and secondary signal source, and described first signal source electrically connects with measuring electrode, and described secondary signal source electrically connects with modulation circuit.
Further, the first low pass filter is the low pass filter of 2Hz-4Hz.
Further, the monitoring system of physiological signal is wearable cardioelectric monitor module.
Further, the monitoring system of physiological signal also includes: be connected to the first amplifier between modulation circuit and demodulator circuit, it is connected to the first electric capacity (CT) between signal source and modulation circuit, and the second electric capacity (CR) being connected between described modulation circuit and the first amplifier, described first amplifier amplification frequency is 2Hz-4Hz.
Further, the monitoring system of physiological signal also includes the first analog-digital converter and the processor that are connected with the outfan of the first low pass filter, the breath signal that first low pass filter is exported by described first analog-digital converter carries out analog digital conversion, and the breath signal after conversion is exported processor, the breath signal process after change is respiratory waveform data by described processor.
Further, the monitoring system of physiological signal also includes ecg wave form monitoring channel, and described respiratory waveform monitoring channel shares with ecg wave form monitoring channel and measures electrode.
Further, ecg wave form monitoring channel includes the second amplifier, the second low pass filter and the second analog-digital converter that are linked in sequence, and described second low pass filter is the frequency low pass filter less than 1KHz.
Accompanying drawing explanation
Fig. 1 is respiratory impedance monitoring model equivalent schematic；
Fig. 2 is monitoring of respiration passage and cardioelectric monitor channel circuit schematic diagram；
Fig. 3 is the schematic diagram having OFF signal；
Fig. 4 is the comparison diagram of respiratory waveform according to embodiments of the present invention and the respiratory waveform of conventional example.
Detailed description of the invention
The present invention is described in further detail in conjunction with accompanying drawing below by detailed description of the invention.
In embodiments of the present invention, utilize the relevant voltage change that the size variation of lung impedance is brought in respiratory that respiratory waveform is monitored.
Provide the monitoring system of a kind of physiological signal in the present embodiment, as in figure 2 it is shown, specifically include measurement electrode 100, cardioelectric monitor passage 200 and monitoring of respiration passage 300；Measuring electrode 100 be used for the contact skin with monitored person and detect the signal of telecommunication, cardioelectric monitor passage 200 is for detecting the electrocardiosignal of monitored person, in order to be subsequently generated ecg wave form；Monitoring of respiration passage 300 is for detecting the breath signal of monitored person, in order to be subsequently generated respiratory waveform.Cardioelectric monitor passage 200 and monitoring of respiration passage 300 all electrically connect with measurement electrode 100, share and measure electrode 100.
Monitoring of respiration passage 300 includes signal source 301 and the modulation circuit 302, demodulator circuit 303 and the first low pass filter 304 that are linked in sequence.
Signal source 301, for providing the AC signal of preset frequency, in the present embodiment, adopts one signal source 301, signal source 301 respectively with measurement electrode 100 and modulation circuit 302.In the present embodiment, signal source 300 is current source, and the signal of its output can be high frequency square wave current signal or sine-wave current signal, and in the present embodiment, the frequency of the current signal of current source output is more than 1KHz, for instance for 30KHz.When signal source 300 is current source, measure electrode detection to be voltage signal.In other embodiments, signal source can also be voltage source, and accordingly, what measure electrode detection can be current signal.
When signal source 301 is connected with measurement electrode 100, the pumping signal of monitored person is provided input directly to for measuring electrode, as shown in Figure 1, after this pumping signal is applied on monitored person's health (such as thoracic cavity 400) so that signal source 300, formation current loop between measurement electrode 100 and thoracic cavity 400.Fig. 1 is respiratory impedance monitoring model equivalent schematic.In fig. 1 it is assumed that the constant value impedance in thoracic cavity is RB, it is Δ R by breathing the transforming impedance caused, by high frequency square wave alternating current I (FC) input in thoracic cavity, it is consequently formed loop.Thoracic impedance RBNamely waveform voltage signal on+Δ R is breath signal waveform.In such cases, measure in the voltage signal that detects of electrode 100 except comprising the bioelectrical signals produced because of heartbeat, be also superimposed with because of thoracic impedance RBThe voltage signal that+Δ R produces.
When signal source 301 electrically connects with modulation circuit 302, provide envelope waveform or carrier waveform for modulation circuit 302.
Modulation circuit 302 electrically connects with measurement electrode and signal source respectively, signal I (F signal source exportedc) and measure the signal of telecommunication that detects of electrode and carry out amplitude modulation(PAM), output modulation signal.
Modulation signal will be demodulated by demodulator circuit 303, output demodulation signal.
First low pass filter 304 is for carrying out low-pass filtering to demodulation signal, and in the present embodiment, low pass filter 304 has the frequency bandwidth mated with respiratory frequency, can obtain breath signal after demodulation signal is filtered process.Such as, it is generally the case that the respiratory frequency of people, less than heart rate, is generally 2-4Hz, therefore, the filtering bandwidth of the first low pass filter 304 may be set to 2Hz-4Hz so that the breath signal in demodulation signal passes through, and electrocardiosignal is filtered out.
The present embodiment also includes: the first amplifier 305 being connected between modulation circuit and demodulator circuit, be connected to the first electric capacity C between signal source and modulation circuitT, and the second electric capacity C being connected between described modulation circuit and the first amplifierR.First amplifier amplification frequency, for modulation signal is amplified, in order to emphatically breath signal is amplified, is set to 2Hz-4Hz so that it is mate with the frequency of breath signal by the first amplifier 305.First electric capacity CTWith the second electric capacity CREffect be every directly.
Ecg wave form monitoring channel 200 includes the second amplifier the 201, second low pass filter 202 and the second analog-digital converter 203 being linked in sequence, and the second low pass filter 202 is the frequency low pass filter less than 1KHZ.
Fig. 2 is monitoring of respiration passage and cardioelectric monitor channel circuit schematic diagram.In fig. 2, the voltage signal measuring electrode 100 detection is input to respiratory waveform monitoring channel on the one hand, is input to ecg wave form monitoring channel on the other hand.
For ecg wave form monitoring channel, measure electrode breath signal and electrocardiosignal to be transferred in ecg wave form monitoring channel (ECGChannel), by amplifier gain amplifier and low pass filter, it is possible to obtaining analog electrocardiogram signal, wherein this low filter frequency is lower than 1KHz.Then analog electrocardiogram signal simulation/digital signal conversion in analog-digital converter (ADC), thus obtaining numeral electrocardiosignal, the treated device of this numeral electrocardiosignal generates EGC waveform data after processing.This processor can be digital signal processor (DSP) or single-chip microcomputer.
For respiratory waveform monitoring channel, on the one hand, high frequency square wave alternating current I (Fc) by capacitance CrRemove direct current signal, as modulating signal and inputting modulation circuit；On the other hand, thoracic impedance RBVoltage signal (i.e. breath signal) on+Δ R also inputs modulation circuit by measurement electrode with electrocardiosignal simultaneously.Voltage signal is modulated by modulation circuit by amplitude modulation mode, transfers to F after modulationCFrequency range, then after modulation, signal passes through capacitance CRRemove direct current signal.The reason being incorporated herein modulation circuit is in that, the respiratory of human body is very slow, thus causing respiratory signal frequency extremely low and easily with substantial amounts of noise signal.If breath signal being modulated high frequency by modulation circuit, then can effectively remove noise.
Breath signal and electrocardiosignal is amplified followed by amplifier.The operating frequency of this amplifier is 2Hz-4Hz, is the frequency range of breath signal, and therefore amplifier simply amplifies breath signal.
Then the breath signal being exaggerated and electrocardiosignal enter demodulator circuit, simultaneously same frequency FCDemodulation signal enter demodulator circuit be demodulated.Obtain pure breath signal and electrocardiosignal subsequently.
Then this pure breath signal and electrocardiosignal input low pass filter, this low-pass filter frequency is 2Hz-4Hz, is namely the frequency range of breath signal, thus can remove the higher electrocardiosignal of frequency and obtain pure simulated respiration signal.
Then simulation/digital signal conversion in simulated respiration signal input analog-to-digital converter (ADC), thus obtaining numeral breath signal.
Then numeral breath signal is input in processor, and treated device generates respiratory waveform data and shows on screen after processing.
Fig. 3 is the schematic diagram having OFF signal.In figure 3, signal 1 is high-frequency square-wave signal, is namely current source signal I (Fc), also it is modulation signal.This signal is not only injected into human body and forms current loop with torso model, and is used as modulation signal to modulate the voltage signal corresponding to breath signal.Signal 2 modulated by modulation circuit after breath signal.Signal 3 is the demodulation signal for demodulating breath signal, and the frequency of this signal is identical with the frequency of signal 1.The breath signal that signal 4 is ultimately formed, this signal can show that the frequency of human body respiration effect.
Fig. 4 is the respiratory waveform comparison diagram of respiratory waveform according to embodiments of the present invention and conventional example.Figure is according to Conventional implementations in fig. 4, the upper, and namely ecg wave form carries out the schematic diagram of the obtained respiratory waveform signal of signal extraction；Figure below is the schematic diagram of respiratory waveform signal obtained according to the embodiment of the present invention.By comparing it can be found that: the respiratory waveform signal of upper figure does not only have substantial amounts of burr signal, and certainty of measurement also will lower than the waveshape signal of figure below.Therefore compared to Conventional implementations, there is clear superiority according to the embodiment of the present invention.
In the another kind of embodiment of the present invention, signal source can also include the first signal source and secondary signal source, and the first signal source electrically connects with measuring electrode, and secondary signal source electrically connects with modulation circuit.
This utility model is illustrated by use above specific case, is only intended to help and understands this utility model, not in order to limit this utility model.For this utility model person of ordinary skill in the field, according to the thought of the present invention, it is also possible to make some simple deductions, deformation or replacement.
Claims (10)
1. a monitoring system for physiological signal, including measuring electrode and respiratory waveform monitoring channel, it is characterised in that described respiratory waveform monitoring channel includes: signal source and the modulation circuit, demodulator circuit and the first low pass filter that are linked in sequence；
Described measurement electrode is used for the contact skin with monitored person and detects the signal of telecommunication；
Described signal source is for providing the AC signal of preset frequency, and described signal source electrically connects with measuring electrode, provides input directly to the pumping signal of monitored person for measuring electrode；
Described modulation circuit electrically connects with measurement electrode and signal source respectively, signal I (F signal source exportedc) and measure the signal of telecommunication that detects of electrode and carry out amplitude modulation(PAM), signal after output modulation；Signal after modulation is demodulated by described demodulator circuit, signal after output demodulation；
Described low pass filter has the frequency bandwidth mated with respiratory frequency, and after being filtered process, signal after demodulation is obtained breath signal.
2. the monitoring system of physiological signal as claimed in claim 1, it is characterised in that described signal source is current source, and described measurement electrode detection is voltage signal.
3. the monitoring system of physiological signal as claimed in claim 2, it is characterised in that the signal of described current source output is high frequency square wave current signal or sine-wave current signal, the frequency of described current source output signal is more than 1KHz.
4. the monitoring system of physiological signal as claimed in claim 1, it is characterised in that described signal source includes the first signal source and secondary signal source, described first signal source electrically connects with measuring electrode, and described secondary signal source electrically connects with modulation circuit.
5. the monitoring system of the physiological signal as according to any one of claim 1-4, it is characterised in that described first low pass filter is the low pass filter of 2Hz-4Hz.
6. the monitoring system of physiological signal as claimed in claim 5, it is characterised in that the monitoring system of described physiological signal is wearable cardioelectric monitor module.
7. the monitoring system of physiological signal as claimed in claim 5, it is characterised in that also include: the first amplifier being connected between modulation circuit and demodulator circuit, be connected to the first electric capacity (C between signal source and modulation circuitT), and the second electric capacity (C being connected between described modulation circuit and the first amplifierR), described first amplifier amplification frequency is 2Hz-4Hz.
8. the monitoring system of physiological signal as claimed in claim 1, it is characterized in that, also include the first analog-digital converter and the processor that are connected with the outfan of the first low pass filter, the breath signal that first low pass filter is exported by described first analog-digital converter carries out analog digital conversion, and the breath signal after conversion is exported processor, the breath signal process after change is respiratory waveform data by described processor.
9. the monitoring system of physiological signal as claimed in claim 1, it is characterised in that also include ecg wave form monitoring channel, described respiratory waveform monitoring channel shares with ecg wave form monitoring channel and measures electrode.
10. the monitoring system of the physiological signal described in claim 9, it is characterized in that, described ecg wave form monitoring channel includes the second amplifier, the second low pass filter and the second analog-digital converter that are linked in sequence, and described second low pass filter is the frequency low pass filter less than 1KHz.
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| CN201521126097.7U CN205338955U (en) | 2015-12-29 | 2015-12-29 | Physiological signal's monitoring system |
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Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107485375A (en) * | 2017-09-19 | 2017-12-19 | 姚尚龙 | One kind is used for neonatal physiologic index monitoring system |
| CN110267592A (en) * | 2016-12-21 | 2019-09-20 | 通用电气公司 | ECG sensor with the protection of capacitor defibrillation |
| CN110881965A (en) * | 2018-09-11 | 2020-03-17 | 苹果公司 | Contact detection for physiological sensors |
| CN111528830A (en) * | 2020-05-20 | 2020-08-14 | 广东工业大学 | Electrocardiogram monitoring device |
-
2015
- 2015-12-29 CN CN201521126097.7U patent/CN205338955U/en not_active Expired - Fee Related
Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110267592A (en) * | 2016-12-21 | 2019-09-20 | 通用电气公司 | ECG sensor with the protection of capacitor defibrillation |
| CN110267592B (en) * | 2016-12-21 | 2022-02-11 | 通用电气公司 | ECG sensor with capacitive defibrillation protection |
| CN107485375A (en) * | 2017-09-19 | 2017-12-19 | 姚尚龙 | One kind is used for neonatal physiologic index monitoring system |
| CN110881965A (en) * | 2018-09-11 | 2020-03-17 | 苹果公司 | Contact detection for physiological sensors |
| CN110881965B (en) * | 2018-09-11 | 2022-10-04 | 苹果公司 | Contact detection for physiological sensors |
| US11478193B2 (en) | 2018-09-11 | 2022-10-25 | Apple Inc. | Contact detection for physiological sensor |
| US11484267B2 (en) | 2018-09-11 | 2022-11-01 | Apple Inc. | Contact detection for physiological sensor |
| US11980480B2 (en) | 2018-09-11 | 2024-05-14 | Apple Inc. | Contact detection for physiological sensor |
| CN111528830A (en) * | 2020-05-20 | 2020-08-14 | 广东工业大学 | Electrocardiogram monitoring device |
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Granted publication date: 20160629 |