CN201361029Y - Portable sleep-apnea detecting and analyzing instrument - Google Patents
Portable sleep-apnea detecting and analyzing instrument Download PDFInfo
- Publication number
- CN201361029Y CN201361029Y CNU2009200501052U CN200920050105U CN201361029Y CN 201361029 Y CN201361029 Y CN 201361029Y CN U2009200501052 U CNU2009200501052 U CN U2009200501052U CN 200920050105 U CN200920050105 U CN 200920050105U CN 201361029 Y CN201361029 Y CN 201361029Y
- Authority
- CN
- China
- Prior art keywords
- module
- sleep apnea
- analysis instrument
- portable sleep
- sleep
- 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.)
- Expired - Fee Related
Links
Images
Landscapes
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
The utility model relates to a portable sleep-apnea detecting and analyzing instrument, which is characterized in that the detecting and analyzing instrument is formed by connecting a micro-processing module (1), an A/D (analog to digital) conversion module (2), a thoracoabdominal-respiration sensing module(3), a display module (4), an oronasal-airflow sensing module (5), an electrocardio-extracting and amplifying module (6), a USB (universal serial bus) interface module (7), a SD (secure digital) memory module (8), a vibration wake-up module (9), a keyboard (10), a clock circuit (11) and a pulmonary impedance measuring module (12); and signal outputting terminals of the thoracoabdominal-respiration sensing module(3), the oronasal-airflow sensing module (5) and the electrocardio-extracting and amplifying module (6) are respectively connected with an I/O (input and output) port of the micro-processing module (1) through the A/D conversion module. The portable sleep-apnea detecting and analyzing instrument can detect the time and the frequency of the sleep apnea, realizes the spectral analysis of heart rate variability, stores the related data of sleep apnea episodes, and displays the detection results and various detection curves. The sleep-apnea detecting and analyzing instrument has the advantages of simple structure, small volume, low manufacturing cost and portability.
Description
Technical field
This utility model relates to portable sleep apnea check and analysis instrument, is a kind of real-time detection, record, analyzes the isolated plant of sleep apnea and type automatically.Belong to medical electric diagnostic instruments technical field.
Background technology
(Sleep Apnea Syndromes SAS), shows as occur temporary respiratory arrest repeatedly in sleep sleep apnea syndrome, and every night about 7 hours in the sleep, asphyxia can reach more than 30 times and at every turn more than 10 seconds.At present hospital is commonly used leads hypnotic instrument or the breathing diagnostic apparatus is diagnosed by clinical monitoring more.The patient need stay institute's monitoring, owing to changed patient's living environment and upset patient's sleep habit, be difficult to obtain real hypnograph, and complicated operation, cost an arm and a leg, the analysis result time and effort consuming reaches 300 meters recorder chart and need expend the analysis of 2～3 hours ability of those skilled in the art and finish, therefore, this lead hypnotic instrument or breathe diagnostic apparatus be not suitable for using in general general hospital.
Replace lead sleep-respiratory monitoring though domestic many monitoring center have used easy monitoring means more, adopt the breast impedance method such as CN1559344A, CN2865564Y adopts the respiratory air flow detection method.Though these two kinds of methods can more directly be obtained respiratory curve, its function ratio is more single, just obtains respiration case, therefore, described breast impedance method and respiratory air flow detection method, its clinical practice is subjected to bigger limitation.
Detecting in the technology of breathing in disclosed lung impedance method, all is the driving source that adopts single-frequency, utilizes bridge method to obtain the variation of lung impedance.Very little by the variation impedance that hands human body respiration process is produced, generally need tens thousand of times amplification just can detect.Because tested crowd's individual difference, there is different frequency characteristics in its lung impedance, when adopting the bridge measurement impedance, because resistance and electric capacity generally all are to adopt resistance box and capacitive on the counter-jib, volume is big, and range of accommodation is smaller, and precision is not high yet, regulate relatively difficulty of bridge balance, so its scope of application is more limited.
The utility model content
The purpose of this utility model, be in order to lead hypnotic instrument detection of complex in order overcoming more, to cost an arm and a leg, influence the deficiency that the patient sleeps, and when adopting bridge measurement lung impedance variation, electric bridge is regulated difficulty, precision is not high and the shortcoming of function singleness, a kind of portable sleep apnea check and analysis instrument is provided, this check and analysis instrument can realize to the patient whole night sleep detection, playback testing result and show various analysis waveform.
The purpose of this utility model can reach by the following technical programs:
Portable sleep apnea check and analysis instrument, its construction features is: extract amplification module, usb interface module, SD memory module, vibration wake module, keyboard, clock circuit and lung impedance measurement module by micro treatment module, A/D modular converter, breast abdominal respiration sensing module, display module, mouth and nose air-flow sensing module, electrocardio and be formed by connecting; The signal output part of breast abdominal respiration sensing module, mouth and nose air-flow sensing module and electrocardio extraction amplification module is connected the I/O port of micro treatment module respectively by the A/D modular converter, the I/O mouth of usb interface module, SD memory module, clock circuit and lung impedance measurement module is connected an I/O port of micro treatment module respectively, the outfan of keyboard connects an input of micro treatment module, the input of vibration wake module connects an outfan of micro treatment module, and an outfan of micro treatment module connects the input of display module.
The purpose of this utility model can also reach by taking following technical scheme:
A kind of improvement project of the present utility model is: microprocessor module can be made of 32 singlechip chip UC1 and peripheral cell thereof, and this chip internal is integrated with MCI interface, USB interface, the I that is used to read and write the SD card
2C interface and SPI interface.
A kind of improvement project of the present utility model is: the A/D modular converter can be made of high-speed low-power-consumption eight passages, 12 A/D conversion chip UC9 and peripheral cell thereof, and this chip is connected with microprocessor UC1 by four line SPI interfaces.
A kind of improvement project of the present utility model is: breast abdominal respiration sensing module can be formed by connecting by three-axis moving pick off and three-dimensional amplification filtering circuit, and the outfan of three-axis moving pick off 31 connects an input of analog-to-digital conversion module by three-dimensional amplification filtering circuit.
A kind of improvement project of the present utility model is: the vibration wake module can be made of the vibration probe that is built-in with the micro-vibration motor, and this vibration probe can be fixed on any position of health.
A kind of improvement project of the present utility model is: mouth and nose air-flow sensing module can be made of temperature sensor and the adjustable shunting a reference source of three ends, and its principle is to utilize temperature sensor measurement respiratory air flow variations in temperature to obtain breath signal.
A kind of improvement project of the present utility model is: electrocardio extraction amplification module can involve buffer, difference amplifier, band filter, 50Hz wave trap by low pass filtered, baseline level adjusts circuit and driven-right-leg circuit is formed by connecting.
A kind of improvement project of the present utility model is: lung impedance measurement module can be made of impedance transformation chip and peripheral cell thereof.
The utlity model has following outstanding beneficial effect:
1, this utility model not only can detect the time and the number of times of sleep apnea, and can realize the heart rate variability spectrum analysis, the required related data of storage sleep-respiratory incident, and show testing result and various monitoring curve.
2, this utility model is owing to adopt modular construction, therefore have simple for structure, volume is little, low cost of manufacture, portable advantage.Can realize sleep detection, playback testing result and various analysis waveform whole night, also can data be sent to hospital for diagnosis and long preservation by the Internet to the patient.
Description of drawings
Fig. 1 is a system structure sketch map of the present utility model.
Fig. 2 is breast abdominal respiration motion-sensing modular structure figure of the present utility model.
Fig. 3 is that electrocardiosignal of the present utility model is amplified and the filtration module structure chart.
Fig. 4 is microprocessor module of the present utility model and peripheral interface circuit schematic diagram.
Fig. 5 is lung impedance measurement module principle figure of the present utility model.
Fig. 6 is a mouth and nose respiratory air flow sensing module schematic diagram of the present utility model.
The specific embodiment
Specific embodiment:
As shown in Figure 1, an embodiment of the present utility model is formed by connecting by micro treatment module 1, A/D modular converter 2, breast abdominal respiration sensing module 3, display module 4, mouth and nose air-flow sensing module 5, electrocardio extraction amplification module 6, usb interface module 7, SD memory module 8, vibration wake module 9, keyboard 10, clock circuit 11 and lung impedance measurement module 12; The signal output part of breast abdominal respiration sensing module 3, mouth and nose air-flow sensing module 5 and electrocardio extraction amplification module 6 is connected the I/O port of micro treatment module 1 respectively by A/D modular converter 2, the I/O mouth of usb interface module 7, SD memory module 8, clock circuit 11 and lung impedance measurement module 12 is connected an I/O port of micro treatment module 1 respectively, the outfan of keyboard 10 connects an input of micro treatment module 1, the input of vibration wake module 9 connects an outfan of micro treatment module 1, and an outfan of micro treatment module 1 connects the input of display module 4.
As shown in Figure 2, the three-axis moving pick off 31 (probe) of breast abdominal respiration sensing module 3 can be fixed on chest or abdominal part, the 3-axis acceleration sensing chip ADXL330 that the probe internal fixation has ADI to produce, ADXL330 is a kind of little range that signal conditioning circuit provides aanalogvoltage output that has, little profile, the three axis accelerometer of low-power consumption, can measure the static weight acceleration, and by motion, impact or vibrate the dynamic acceleration that produces, its output is three road analog voltage signals that are directly proportional with each axial acceleration, through three tunnel (X, Y, Z) analogue signal is amplified and deliver to analog to digital conversion circuit 2 after 32 filtering of three road 0.7Hz low-pass filter circuits through amplifying circuit 31.In three road analog voltage signals, Z-direction is detected breath signal perpendicular to the signal of breast abdomen in-plane just, and other two-way is the moving signal of detected body.At follow-up date processing with in analyzing, the moving signal of body is used for constructing sef-adapting filter, the moving precision that detects to improve of disturbing of filtering body.
As shown in Figure 3, electrocardio extraction amplification module 6 comprises that low pass filtered involves buffer 61, difference amplifier 62, band filter 63,50Hz wave trap 64, baseline level adjustment circuit 65 and driven-right-leg circuit 66.Electrocardiosignal at first is higher than the 300Hz high fdrequency component through the RC low-pass filter circuit of a two-stage with filtering, enters buffer 61.Buffer connects into voltage follower by the OP4177 operational amplifier of ADI company, and it can improve the input impedance of whole amplifying circuit, reduces output impedance.Difference amplifier 62 uses the instrument amplifier AD8221 of ADI company adjustable gain high cmrr as pre-amplifier, and amplification is made as octuple.Band filter 63 is made up of RC high pass filter and second order Butterworth LPF, and the cut-off frequency of RC high pass filter is 0.05Hz, and the cut-off frequency of low pass filter is 112Hz, and amplification is 1.57 times.50Hz wave trap 64 adopts active twin-T network band elimination filter, and getting Q-value is 2.5 effectively filtering 50Hz power frequency interference.Baseline level adjustment circuit 65 is made up of accurate voltage reference chip ref3025 and emitter follower that TI company produces, and output voltage is 1.25V, is used for the steady baseline level.Driven-right-leg circuit 66 be used to reduce the interference of displacement current and reduce human body and ground between the common mode current potential.
As shown in Figure 4, micro treatment module 1 is made of 32 singlechip chip UC1, and its model is LPC2368.This chip internal is integrated with MCI interface, USB interface, the I that is used to read and write SD memory module 8
2C interface, SPI interface; The MCI interface is connected with the deck UC6 of SD memory module 8, and QC1 is the on and off switch of SD card.UC4 is the colour liquid crystal display device circuit, and QC3 is a colour liquid crystal display device bias light on-off circuit.
A/D modular converter 2 is made of high-speed low-power-consumption eight passages, 12 A/D conversion chip UC9, and its model is AD7888.This chip is connected with microprocessor UC1 by four line SPI interfaces.Voltage Reference chip Ur2 provides the high precision reference voltage of 2.5V for UC9.This module is electrocardiosignal, breast abdomen motor message, mouth and nose respiratory air flow conversion of signals a digital signal respectively with the sample frequency of 250HZ, and by microprocessor transformation result is deposited in the SD card.
Described vibration wake module 9 drives the vibration probe that the micro-vibration motor is arranged in external by QC4, this probe can be fixed on any position of health, surpass last prescribing a time limit when detecting asphyxia, the QC4 conducting, the rotation of vibrating motor cam makes vibration probe produce vibration, reaches and wakes purpose up.
As shown in Figure 5, lung impedance measurement module 12 is made of impedance transformation chip AD5933, this impedance transformation chip is the impedance transformation chip of a kind of high precision of ADI company production, and the kernel of this chip comprises three formants: the first is used to provide Direct Digital Frequency Synthesizers (DDS) waveform generator of frequency scanning; It two is 12bit, the 1MSPS analog-digital converters that are used for the response of measuring transducer; It three is the DSP engines that can carry out 1024 point discrete Fourier conversion (DFT) computings at last to the ADC measurement data.Microprocessor (LPC2368) can pass through I
2C interface (15,16 pins of Uc11) transmits order and receives measurement result to AD5933.When carrying out the lung impedance measurement, microprocessor (LPC2368) at first passes through I
2C interface sets the measuring frequency point, send startup command then, digital frequency synthesizer (DDS) waveform generator in the sheet produces the pumping signal of an assigned frequency and injects human body by chest electrode 1, obtain response signal by chest electrode 2, this response signal is carried out 1024 point samplings by the analog-digital converter in the sheet, carries out DFT by the DSP engine in the sheet then and handles.The data word of real part (R) and imaginary part (I) is returned in the DFT computing, and microprocessor (LPC2368) reads real part data and imaginary data by the I2C interface, thereby finishes a lung impedance measurement.
As shown in Figure 6, mouth and nose air-flow sensing module 5 constitutes the respiratory air flow sensing module, and its principle is to utilize temperature sensor measurement respiratory air flow variations in temperature to obtain breath signal.TL431 among Fig. 4 is the adjustable shunting a reference source of three ends with good thermal stability of being produced by Texas Instruments (TI), and it and potentiometer VR1 regulate the reference power source that produces 3.096V; Rc82 in the accompanying drawing 4, Rc83, VR2, Pt100 constitute measuring bridge (Rc82=Rc83 wherein, VR2 is 200 precision resistances), when the resistance value of the resistance value of Pt100 and VR2 is unequal, the pressure difference signal of a mV level of electric bridge output, the voltage signal of output expectation size after this pressure difference signal process amplifier AD8534 amplification filtering, this signal is directly delivered to modulus conversion chip.
In the present embodiment, display module 4 is made of the colour liquid crystal display device of routine, and its model can Philips PCF8833; Usb interface module 7, SD card memory module 8, keyboard 10 and clock circuit 11 can be respectively be made of the USB interface chip of routine or module, conventional SD storage chip, conventional input keyboard and conventional clock circuit.
The portable sleep apnea check and analysis of this utility model instrument is to realize by following steps:
1) electrocardioelectrode, mouth and nose air-flow sensor probe, breast abdomen motion-sensing probe, lung impedance measurement electrode are connected to patient's human body corresponding site, open portable sleep apnea check and analysis instrument power supply, system enters initialize routine: system at first carries out initialization to the USB module, comprises that USB clock division, endpoint transmission pattern and packet size are provided with.Secondly SD memory module (SD card) is carried out initialization, comprise whether card is inserted into, whether block whether write-protect, card, then utilize described liquid crystal display screen to show error message if find mistake by the FAT16 format.By modulus conversion chip each probe is carried out 1024 point samplings at last, and each probe waveform is shown on described liquid crystal display screen, whether correctly connect to analyze each probe;
2) after the system initialization success confirms that also each probe connects correctly, enter frequency scanning and lung impedance measurement program, under the general breathing state, Automatic Program is in 20KHZ to 50KHZ scope, adopt split half method to change measuring circuit driving source frequency, at least measure the lung complex impedance waveform of two breathing cycles at each Frequency point, and calculate the poor of the maximum of complex impedance real part and minima, by the relatively maximum of each Frequency point complex impedance real part and the sensitive frequency point of difference to determine that this patient's lung complex impedance real part changes of minima;
3) finish 1), 2) after two steps, the user presses the START button of portable sleep apnea check and analysis instrument, system enters logging program, mouth and nose breath signal, electrocardiosignal, breast abdominal respiration motor message are deposited in after analog digital conversion in the SD memory module (SD card), the sensitive frequency value that lung impedance measurement module B step obtains is set to the driving source frequency, carry out the lung complex impedance measurement by this fixed frequency, and the real part of complex impedance and imaginary part are deposited in the SD memory module (SD card);
4) after the monitoring and record finished whole night, the log file of SD memory module (SD card) is copied to master computer, the analysis software on the master computer is handled and is analyzed record data.Analysis software on the master computer will be distinguished the type of sleep apnea according to following condition when retrieving the sleep apnea incident and take place: if mouth and nose airless signal and the breast abdomen has the respiratory movement signal then is judged to obstructive sleep apnea; Surpass threshold values if the real part of mouth and nose airless signal while breast abdomen apnea motor message and lung complex impedance changes, then be judged to maincenter type sleep apnea; If changing above threshold values, the real part of mouth and nose airless signal while breast abdomen apnea motor message and lung complex impedance then is judged to the mixed type sleep apnea;
5) analysis software on the master computer at first utilizes the slope threshold method to carry out the identification of R ripple to the ECG signal, calculates the RR interval of heart beating one by one.For getting rid of the mistake that dystopy heart beating and QRS omission cause, utilize sliding window average filter method with its filtering.Utilize local detection method that RR interval data sequence is carried out detection then, obtain heart rate variability signals HRV.HRV with the variation of heart beating number of times as a kind of stochastic signal, adopt empirical modal analysis method (Empirical Mode Decomposition, EMD) with the HRV signal decomposition be one group of intrinsic mode functions (Instrinsic Mode Function, IMF), then each IFM component is carried out the Hilbert conversion, obtain the Hilbert spectrum, extract instantaneous phase and instantaneous energy eigenvalue, and judge the position of sleep apnea generation and the light and heavy degree of distribution and judgement sleep-apnea shape according to eigenvalue.
As everyone knows, (heart rate variability HRV) is meant the sinus rate time-variance between the cardiac cycle one by one to heart rate variability, is reflection sympathetic nerve and parasympathetic nervous tension force and equilibrated important indicator thereof.Clinical research is verified, and sleep apnea can cause the fluctuation of heart rate, and generally when sleep apnea just takes place and interval, heart beating is tending towards slowly, and then breathes between convalescent period, and overrunning appears in heart beating.The symptom of sleep apnea is heavy more, and the fluctuation of heart rate is just obvious more.Therefore can detect the light and heavy degree of sleep apnea and differentiation symptom according to this undulatory property.But because this fluctuation is very small, must could detects by special spectral analysis method and obtain, so yet there are no the report that utilizes HRV to detect sleep apnea and judgement sleep apnea light and heavy degree.
This utility model is a multichannel respiratory physiological signal monitoring analysis system, and this utility model extracts electrocardiosignal by electrocardioelectrode, through sending into analog to digital conversion circuit after amplification, the filtering, transformation result is deposited in the SD memory module (SD card); Obtain breath signal by mouth and nose air-flow sensing circuit, deposit in through analog digital conversion and transformation result in the SD memory module (SD card); By breast abdomen motion-sensing circuit extraction breast abdominal respiration motor message, deposit in (SD card) through analog digital conversion and transformation result; By lung complex impedance measurement circuit measuring lung complex impedance and the real part of complex impedance and imaginary part are deposited in respectively in the SD card, the SD card of a 2G capacity, can 300 hours Monitoring Data of continuous record, so can realize whole night sleep monitor.SD card internal data is stored according to the FAT16 form, after finishing monitoring, can transfer of data be arrived computer by USB interface of the present utility model, or directly take out the SD card data file on the SD card is copied to master computer, carry out date processing and analysis for the analysis software that is installed on the master computer.Analysis software on the computer can be retrieved the number of times and the time out of sleep apnea automatically, can distinguish the type of sleep apnea, can obtain heart rate data and heart rate variability is carried out spectrum analysis and power spectrumanalysis ecg-r wave identification.When sleep monitor, if be provided with vibration arousal function of the present utility model, then this utility model is in data acquisition, can also carry out analyzing and processing to the data of gathering by the Data Management Analysis software that is solidificated in microprocessor internal, when finding that the apneic time surpasses last prescribing a time limit, Vibration on Start-up wake-up circuit then, the vibration by the oscillator probe wakes the patient up.
Claims (8)
1, portable sleep apnea check and analysis instrument is characterized in that: extract amplification module (6), usb interface module (7), SD memory module (8), vibration wake module (9), keyboard (10), clock circuit (11) and lung impedance measurement module (12) by micro treatment module (1), A/D modular converter (2), breast abdominal respiration sensing module (3), display module (4), mouth and nose air-flow sensing module (5), electrocardio and be formed by connecting; Breast abdominal respiration sensing module (3), the signal output part that mouth and nose air-flow sensing module (5) and electrocardio extract amplification module (6) is connected the I/O port of micro treatment module (1) respectively by A/D modular converter (2), usb interface module (7), SD memory module (8), the I/O mouth of clock circuit (11) and lung impedance measurement module (12) is connected an I/O port of micro treatment module (1) respectively, the outfan of keyboard (10) connects an input of micro treatment module (1), the input of vibration wake module (9) connects an outfan of micro treatment module (1), and an outfan of micro treatment module (1) connects the input of display module (4).
2, portable sleep apnea check and analysis instrument according to claim 1, it is characterized in that: microprocessor module (1) is made of 32 singlechip chip UC1 and peripheral cell thereof, and this chip internal is integrated with MCI interface, USB interface, the I that is used to read and write the SD card
2C interface and SPI interface.
3, portable sleep apnea check and analysis instrument according to claim 1, it is characterized in that: A/D modular converter (2) is made of high-speed low-power-consumption eight passages, 12 A/D conversion chip UC9 and peripheral cell thereof, and this chip is connected with microprocessor UC1 by four line SPI interfaces.
4, portable sleep apnea check and analysis instrument according to claim 1, it is characterized in that: breast abdominal respiration sensing module (3) is formed by connecting by three-axis moving pick off (31) and three-dimensional amplification filtering circuit (32), and the outfan of three-axis moving pick off (31) connects an input of A/D modular converter (2) by three-dimensional amplification filtering circuit (32).
5, portable sleep apnea check and analysis instrument according to claim 1 is characterized in that: vibration wake module (9) is made of the vibration probe that is built-in with the micro-vibration motor, and this vibration probe is fixed on people's body part.
6, portable sleep apnea check and analysis instrument according to claim 1 is characterized in that: mouth and nose air-flow sensing module (5) is made of temperature sensor and the adjustable shunting a reference source of three ends.
7, portable sleep apnea check and analysis instrument according to claim 1 is characterized in that: electrocardio extraction amplification module (6) involves buffer (61), difference amplifier (62), band filter (63), 50Hz wave trap (64), baseline level adjustment circuit (65) and driven-right-leg circuit (66) by low pass filtered and is formed by connecting.
8, portable sleep apnea check and analysis instrument according to claim 1, it is characterized in that: lung impedance measurement module (12) is made of impedance transformation chip and peripheral cell thereof.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNU2009200501052U CN201361029Y (en) | 2009-01-14 | 2009-01-14 | Portable sleep-apnea detecting and analyzing instrument |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNU2009200501052U CN201361029Y (en) | 2009-01-14 | 2009-01-14 | Portable sleep-apnea detecting and analyzing instrument |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN201361029Y true CN201361029Y (en) | 2009-12-16 |
Family
ID=41471683
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNU2009200501052U Expired - Fee Related CN201361029Y (en) | 2009-01-14 | 2009-01-14 | Portable sleep-apnea detecting and analyzing instrument |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN201361029Y (en) |
Cited By (26)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103079433A (en) * | 2011-03-03 | 2013-05-01 | 世健科技有限公司 | A baby monitoring mat based on fiber optic sensor |
| CN103202687A (en) * | 2012-01-12 | 2013-07-17 | 谢汝石 | Obstructive sleep apnea-hypopnea syndrome patient preliminary screening system |
| WO2014086262A1 (en) * | 2012-12-07 | 2014-06-12 | 河南华南医电科技有限公司 | Thoracic impedance measurement device based on microcontroller |
| WO2014094415A1 (en) * | 2012-12-20 | 2014-06-26 | 中山大学 | Method and apparatus for identifying sleep breathing pattern based on bioimpedance |
| CN103932697A (en) * | 2014-04-28 | 2014-07-23 | 郭士金 | Remote and wireless electrocardio monitoring system |
| CN103948390A (en) * | 2014-05-15 | 2014-07-30 | 中国医学科学院生物医学工程研究所 | Respiration obstruction part detecting instrument |
| CN104257353A (en) * | 2014-10-22 | 2015-01-07 | 南京邮电大学 | Sleep apnea syndrome detecting system |
| CN104274173A (en) * | 2014-10-31 | 2015-01-14 | 思澜科技（成都）有限公司 | Bio-impedance-based wearable sleep respiration state monitoring system |
| CN104545888A (en) * | 2014-12-27 | 2015-04-29 | 迪姆软件(北京)有限公司 | Sleep apnea collecting and analyzing system based on dynamic electrocardiogram and respiratory wave collection |
| CN105030215A (en) * | 2015-07-08 | 2015-11-11 | 北京大学 | Cardiac impedance signal analysis device |
| CN106377262A (en) * | 2016-10-03 | 2017-02-08 | 北京化工大学 | Portable sleeping breath monitoring device |
| CN106725489A (en) * | 2017-01-04 | 2017-05-31 | 上海汉赫电子科技有限公司 | A kind of sleeping respiration interference testing apparatus |
| WO2017112960A1 (en) * | 2015-12-23 | 2017-06-29 | Invicta Medical, Inc. | Method and apparatus for predicting disordered breathing |
| CN106999143A (en) * | 2014-12-12 | 2017-08-01 | 皇家飞利浦有限公司 | acoustic monitoring system, monitoring method and monitoring computer program |
| TWI602542B (en) * | 2016-06-28 | 2017-10-21 | 慶旺科技股份有限公司 | Wise Baby Nest |
| US10195426B2 (en) | 2014-01-07 | 2019-02-05 | Invicta Medical, Inc. | Method and apparatus for treating sleep apnea |
| CN109330582A (en) * | 2018-08-31 | 2019-02-15 | 苏州心生智能科技有限公司 | Heart rate and its characteristic index detection method based on ECG Signal Analysis |
| CN109691990A (en) * | 2017-10-20 | 2019-04-30 | 纳智源科技（唐山）有限责任公司 | Sleep apnea low detection device and method |
| CN110037702A (en) * | 2019-04-22 | 2019-07-23 | 江苏人先医疗科技有限公司 | A kind of monitoring of respiration method and device |
| CN111397725A (en) * | 2020-03-20 | 2020-07-10 | 符霞 | Automatic monitoring system and method for intelligent vibration frequency spectrum sensor |
| CN111568388A (en) * | 2020-04-30 | 2020-08-25 | 清华大学 | Non-contact mouth respiration detection device and method and storage medium |
| CN111820871A (en) * | 2019-04-17 | 2020-10-27 | 联发科技股份有限公司 | Physiological state monitoring device and related method |
| US11491324B2 (en) | 2019-10-16 | 2022-11-08 | Invicta Medical, Inc. | Adjustable devices for treating sleep apnea, and associated systems and methods |
| CN115399750A (en) * | 2022-07-25 | 2022-11-29 | 知心健(南京)科技有限公司 | Method for measuring respiratory impedance |
| US11617888B2 (en) | 2020-11-04 | 2023-04-04 | Invicta Medical, Inc. | Implantable electrodes with remote power delivery for treating sleep apnea, and associated systems and methods |
| US11964154B1 (en) | 2023-06-07 | 2024-04-23 | Invicta Medical, Inc. | Signal delivery devices to treat sleep apnea, and associated methods and systems |
-
2009
- 2009-01-14 CN CNU2009200501052U patent/CN201361029Y/en not_active Expired - Fee Related
Cited By (34)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103079433A (en) * | 2011-03-03 | 2013-05-01 | 世健科技有限公司 | A baby monitoring mat based on fiber optic sensor |
| US9572517B2 (en) | 2011-03-03 | 2017-02-21 | Ospicon Company Limited | Baby monitoring mat based on fiber optic sensor |
| CN103202687A (en) * | 2012-01-12 | 2013-07-17 | 谢汝石 | Obstructive sleep apnea-hypopnea syndrome patient preliminary screening system |
| WO2014086262A1 (en) * | 2012-12-07 | 2014-06-12 | 河南华南医电科技有限公司 | Thoracic impedance measurement device based on microcontroller |
| WO2014094415A1 (en) * | 2012-12-20 | 2014-06-26 | 中山大学 | Method and apparatus for identifying sleep breathing pattern based on bioimpedance |
| US10195427B2 (en) | 2014-01-07 | 2019-02-05 | Invicta Medical, Inc. | Method and apparatus for treating sleep apnea |
| US10195426B2 (en) | 2014-01-07 | 2019-02-05 | Invicta Medical, Inc. | Method and apparatus for treating sleep apnea |
| CN103932697A (en) * | 2014-04-28 | 2014-07-23 | 郭士金 | Remote and wireless electrocardio monitoring system |
| CN103948390A (en) * | 2014-05-15 | 2014-07-30 | 中国医学科学院生物医学工程研究所 | Respiration obstruction part detecting instrument |
| CN104257353A (en) * | 2014-10-22 | 2015-01-07 | 南京邮电大学 | Sleep apnea syndrome detecting system |
| CN104274173A (en) * | 2014-10-31 | 2015-01-14 | 思澜科技（成都）有限公司 | Bio-impedance-based wearable sleep respiration state monitoring system |
| CN106999143A (en) * | 2014-12-12 | 2017-08-01 | 皇家飞利浦有限公司 | acoustic monitoring system, monitoring method and monitoring computer program |
| CN104545888A (en) * | 2014-12-27 | 2015-04-29 | 迪姆软件(北京)有限公司 | Sleep apnea collecting and analyzing system based on dynamic electrocardiogram and respiratory wave collection |
| CN105030215A (en) * | 2015-07-08 | 2015-11-11 | 北京大学 | Cardiac impedance signal analysis device |
| WO2017112960A1 (en) * | 2015-12-23 | 2017-06-29 | Invicta Medical, Inc. | Method and apparatus for predicting disordered breathing |
| TWI602542B (en) * | 2016-06-28 | 2017-10-21 | 慶旺科技股份有限公司 | Wise Baby Nest |
| CN106377262B (en) * | 2016-10-03 | 2019-05-17 | 北京化工大学 | A kind of Portable sleep respiration monitoring device |
| CN106377262A (en) * | 2016-10-03 | 2017-02-08 | 北京化工大学 | Portable sleeping breath monitoring device |
| CN106725489A (en) * | 2017-01-04 | 2017-05-31 | 上海汉赫电子科技有限公司 | A kind of sleeping respiration interference testing apparatus |
| CN109691990A (en) * | 2017-10-20 | 2019-04-30 | 纳智源科技（唐山）有限责任公司 | Sleep apnea low detection device and method |
| CN109691990B (en) * | 2017-10-20 | 2024-02-20 | 纳智源科技（唐山）有限责任公司 | Sleep apnea hypopnea detection device and method |
| CN109330582A (en) * | 2018-08-31 | 2019-02-15 | 苏州心生智能科技有限公司 | Heart rate and its characteristic index detection method based on ECG Signal Analysis |
| CN111820871B (en) * | 2019-04-17 | 2023-11-03 | 联发科技股份有限公司 | Physiological state monitoring device and related method |
| CN111820871A (en) * | 2019-04-17 | 2020-10-27 | 联发科技股份有限公司 | Physiological state monitoring device and related method |
| CN110037702A (en) * | 2019-04-22 | 2019-07-23 | 江苏人先医疗科技有限公司 | A kind of monitoring of respiration method and device |
| US11491324B2 (en) | 2019-10-16 | 2022-11-08 | Invicta Medical, Inc. | Adjustable devices for treating sleep apnea, and associated systems and methods |
| CN111397725A (en) * | 2020-03-20 | 2020-07-10 | 符霞 | Automatic monitoring system and method for intelligent vibration frequency spectrum sensor |
| CN111568388A (en) * | 2020-04-30 | 2020-08-25 | 清华大学 | Non-contact mouth respiration detection device and method and storage medium |
| CN111568388B (en) * | 2020-04-30 | 2021-09-07 | 清华大学 | Non-contact mouth respiration detection device and method and storage medium |
| US11617888B2 (en) | 2020-11-04 | 2023-04-04 | Invicta Medical, Inc. | Implantable electrodes with remote power delivery for treating sleep apnea, and associated systems and methods |
| US11883668B2 (en) | 2020-11-04 | 2024-01-30 | Invicta Medical, Inc. | Implantable electrodes with remote power delivery for treating sleep apnea, and associated systems and methods |
| US11986658B2 (en) | 2020-11-04 | 2024-05-21 | Invicta Medical, Inc. | Implantable electrodes with remote power delivery for treating sleep apnea, and associated systems and methods |
| CN115399750A (en) * | 2022-07-25 | 2022-11-29 | 知心健(南京)科技有限公司 | Method for measuring respiratory impedance |
| US11964154B1 (en) | 2023-06-07 | 2024-04-23 | Invicta Medical, Inc. | Signal delivery devices to treat sleep apnea, and associated methods and systems |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN201361029Y (en) | Portable sleep-apnea detecting and analyzing instrument | |
| CN102302361B (en) | Device for monitoring heart rate and physical state | |
| CN200987666Y (en) | Portable sleep monitor | |
| De Chazal et al. | Assessment of sleep/wake patterns using a non-contact biomotion sensor | |
| CN200987667Y (en) | Portable sleep monitor | |
| CN106667435A (en) | Intelligent sensing mattress for monitoring sleep | |
| CN206792383U (en) | Non-intrusion type sleep monitor mattress | |
| Chang et al. | Wireless portable electrocardiogram and a tri-axis accelerometer implementation and application on sleep activity monitoring | |
| CN106175772A (en) | A kind of sleep apnea monitoring method and system | |
| CN202723829U (en) | Intelligent cough monitoring and evaluation system | |
| CN106175770B (en) | The judgement system of apnea during a kind of sleep | |
| CN102274009A (en) | Respiratory and heartbeat signal processing circuit based on piezoelectric sensor | |
| CN103690168A (en) | Method and system for detecting obstructive sleep apnea syndrome | |
| CN102289618A (en) | Electrocardiosignal-based identity recognition method and device | |
| CN113633260B (en) | Polysomnography, computer equipment and readable storage medium | |
| Cinel et al. | Wearable respiratory rate sensor technology for diagnosis of sleep apnea | |
| CN204909917U (en) | Intelligent sheet of sleep guardianship and medical diagnosis based on cloth sensor | |
| CN108523868A (en) | Self-calibration system and method for blood pressure measurement | |
| CN205795657U (en) | A kind of device gathering sleep procedure centric(al) impact signal | |
| CN202235373U (en) | Cough monitor | |
| Jayarathna et al. | Polymer sensor embedded, IOT enabled t-shirt for long-term monitoring of sleep disordered breathing | |
| Liu et al. | Design of a wearable multi-sensor system for physical activity assessment | |
| CN109171691A (en) | A kind of sleep-respiratory detection system and its detection method | |
| CN205814324U (en) | For detecting the device of obstructive respiration obstacle | |
| CN1584529A (en) | Non-electrode sleeping status and breathing obstacle sensor |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C17 | Cessation of patent right | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20091216 Termination date: 20120114 |