CN102551727A - Respiratory information detecting method and device - Google Patents
Respiratory information detecting method and device Download PDFInfo
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- CN102551727A CN102551727A CN2012100072250A CN201210007225A CN102551727A CN 102551727 A CN102551727 A CN 102551727A CN 2012100072250 A CN2012100072250 A CN 2012100072250A CN 201210007225 A CN201210007225 A CN 201210007225A CN 102551727 A CN102551727 A CN 102551727A
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Abstract
A respiratory information detecting device comprises a respiratory signal collection unit, a pre-amplification unit, a demodulation unit, a gain and offset unit, an analog-to-digital (A/D) conversion unit, a signal processing unit and a display. The A/D conversion unit is a multi-bit conversion unit of at least 16 bits. The inventive method and device is characterized by adopting a multi-bit A/D (more than or equal to 16 bit) conversion scheme, pre-amplifying a respiratory signal by low-power gain, directly acquiring the original respiratory signal by using multi-bit A/D conversion, analyzing and identifying minutiae features of the original respiratory signal by using software in MCU to obtain respiratory waveform approximate to a real signal as well as base resistance information of human body, and setting amplitude threshold of respiratory rate calculation by using the base resistance information of human body. Due to adopting the multi-bit A/D conversion, a hardware circuit has a relatively wide variable resistance detection range, the respiration measurement accuracy is improved, and the hardware circuit is simplified.
Description
Technical field
The present invention relates to detection method, particularly the method and the checkout gear of the detection of human body respiration information.
Background technology
Respiration parameter is an important physiological parameter of clinical monitoring, suffocates even when dead when breathing appears in the patient, and the breathing through custodial care facility suffocates and reports to the police and can in time remind the medical worker to note conditions of patients, the patient's that avoids delay golden hour.Clinically, impedance method is adopted in the monitoring of respiration parameter usually, because impedance method can be obtained respiration parameter in the monitoring EGC parameter, does not need extra adnexa, realizes simply therefore being used widely.
It is the high-frequency carrier signal that custodial care facility produces certain frequency that impedance method is measured the ultimate principle of breathing, and through cardiac diagnosis lead-line this carrier signal is coupled to human body.When relative motion does not take place in the thoracic cavity of human body, be changeless with respect to the equiva lent impedance of breathing carrier signal.When human body causes the thoracic cavity that relative motion takes place owing to breathing, then can produce small impedance variation with respect to high-frequency carrier signal.This small impedance variation can be with breathing carrier modulation; After signal amplification after hardware circuit will be modulated, demodulation, the filtering, be input to A/D, carry out data acquisition by A/D; And with transfer of data to MCU, move corresponding algorithm through MCU and obtain breathing rate and breathe warning message.
As stated, the breathing modulation signal that contains the human body impedance change information must pass through amplification, demodulation and just can obtain breath signal, but through containing higher DC component in the breath signal of demodulation usually; As being 4000 Europe in base resistance, become resistance under 0.5 ohm the situation, the DC component is about about 8000 times of AC component in theory; Dynamic range is so big; If amplify AC, DC component with same gain, then when amplifying the AC component, the DC component causes hardware circuit saturated already.Even more serious is, the DC component is not fixed, be that the variation with basic impedance changes, and the size of basic impedance varies with each individual.In addition, in the clinical monitoring process, if patient moving then can produce bigger change resistance, this change resistance is enough to cause hardware circuit saturated.In order to address the above problem, the prior art scheme adopts capacity coupled method usually, but because the bandwidth of breathing is 0.1～2.5Hz; Its time constant reaches about 1.6S; Big time constant like this, in case patient moving causes hardware circuit saturated, then hardware circuit is very long recovery time.Because there is above-mentioned defective in Capacitance Coupled; The part technical scheme is optimized this, adopts to be called " scheme that a kind of DC component is offset automatically ", in this scheme; Utilize the breath signal after single-chip microcomputer is gathered demodulation in real time; And the breath signal of gathering handled, calculating its DC component in real time, the voltage signal of the equal size of DA output through single-chip microcomputer and the breath signal DC component after the demodulation subtract each other; Then can reduce the DC component in the breath signal significantly, obtain breath signal through amplifying once more after the above-mentioned processing.In " a kind of DC component automatically offset scheme ", the problem of existence is that scheme is very complicated, and single-chip microcomputer is introduced easily in the process of offsetting breath signal DC component and disturbed, and the breath signal of same low frequency is detected cause adverse effect.
To sum up, because technology limitation in the past, the respiration measurement circuit generally adopts low level A/D; Because breath signal is very faint,, need complicated amplifying circuit if adopt low level A/D then need significantly gain to breath signal; Perhaps need add coupling capacitance, hardware bucking circuit etc., cause software and hardware very complicated, and under the situation of human motion; This hardware circuit is easily saturated and be difficult to influence respiration parameter clinical monitoring effect from the fast quick-recovery of saturation.
The weak point of concluding prior art is:
1, anti-movement effects is poor, and in the clinical monitoring process, if patient moving, then the change capacitance-resistance of motion generation is prone to exceed measuring range, cause hardware saturated, and respiratory waveform is difficult to fast quick-recovery;
2, because hardware dynamic is limited in scope, cause the respiratory waveform distortion after hardware is saturated easily, cause the breathing rate mistake in computation.
3, low level A/D scheme, hardware circuit is complicated, introduces more respiratory noise easily, and the calculating of algorithm to breathing rate is breathed in influence;
4, hardware bucking circuit needs constantly to detect and breathes the DC component and can offset the voltage signal of above-mentioned DC component through output after the single-chip microcomputer computing, cause soft, hardware designs is very complicated;
5, the precision of hardware filtering device is difficult to breath signal is accurately handled owing to receive the influence of device discreteness.
Summary of the invention
The present invention provides a kind of respiration information detection method and device; Utilization is carried out pretreatment to signal; And further adopt the mode of multidigit A/D conversion and software LPF and detection computations, poor, circuit structure complicacy of anti-movement effects and the distored technical problem of respiratory waveform in the solution prior art.
The present invention be the demodulating unit that solves the problems of the technologies described above prime amplifying unit that this respiration information checkout gear that provides comprises successively the breath signal collecting unit that is used to gather breath signal that connects, breath signal is amplified, demodulation breath signal, to breath signal amplify and the gain of setovering and bias unit, to breath signal carry out low-pass filtering treatment low-pass filter unit, be used for the A/D converting unit of breath signal digital-to-analogue conversion, the signal processing unit that signal is handled and calculated and the display unit that the data result is shown, said A/D converting unit is at least 16 a multidigit converting unit.Said signal processing unit comprises breath signal pretreatment unit and breathing rate computing unit; Said breath signal pretreatment unit is used for breath signal is carried out pretreatment, eliminates baseline and noise in the breath signal, obtains human body base resistance information; Said breathing rate computing unit is used for the amplitude threshold according to the preset respiratory wave of human body base resistance information, according to the crest value and the trough value of this amplitude threshold detection respiratory wave, calculates breathing rate according to this crest value and trough value again.Said breath signal pretreatment unit comprises: low-pass filtering module, high-pass filtering module and breathing base resistance detection module; Said low-pass filtering module is used for breath signal is carried out low-pass filtering treatment, eliminates high-frequency noise and respiratory waveform is carried out smoothing processing; Said high-pass filtering module links to each other with said low-pass filtering module, is used for that breath signal is carried out high-pass filtering and handles, and the baseline of respiratory waveform is eliminated; Said breathing base resistance detection module links to each other with said low-pass filtering treatment, is used for the breath signal after the low-pass filtering treatment is detected, and obtains human body base resistance information.
This respiration information detection method may further comprise the steps: A. gathers and breathes amplitude-modulated signal, and carries out prime and amplify;
B. the breath signal that amplifies through prime is carried out demodulation, and from breath signal, obtain the respiration information envelope;
C. the breath signal to demodulation output gains once more, and breath signal is biased to proper A/D input voltage range;
This method is further comprising the steps of:
D. the breath signal of handling in the C step is carried out low-pass filtering treatment, with the high-frequency noise filtering in the breath signal;
E. the breath signal of handling among the step D being carried out the A/D conversion, is digital breath signal with the simulated respiration conversion of signals;
F. this numeral breath signal is carried out pretreatment, eliminate the baseline of breath signal, obtain the respiratory waveform data, and obtain breathing resistance information and the basic resistance information of breathing of becoming according to the respiratory waveform data; This step also comprises step by step following: the breath signal after F1. changes A/D carries out low-pass filtering treatment; F2. the data that obtained in the F1 step are carried out high-pass filtering and handle, eliminate the baseline in the breath signal, obtain corresponding in the breath signal AC component that breath signal becomes resistance information, and obtain breath signal change resistance information according to this AC component; F3. the data that obtained in the F1 step are breathed the base resistance and detect processing, obtain the corresponding DC component of breathing basic resistance information in the breath signal, and obtain breath signal base resistance information according to this DC component; G. according to breathing base resistance information calculations breathing rate; And according to this breathing rate acquisition breathing warning message; Calculate in the process of breathing rate, according to the breath signal base resistance information that obtains the amplitude threshold of respiratory wave is preset, its this amplitude threshold comprises upper threshold value and lower threshold value; And obtain the crest value and the trough value of respiratory waveform according to this preset amplitude threshold, calculate and obtain breathing rate through obtaining crest value and trough value; The step of the crest value of said acquisition respiratory waveform and trough value does, when some the respiratory waveform numerical value in the respiratory waveform is higher than the upper threshold value of setting, and the size of those respiratory waveform numerical value relatively, its maximum is crest value; When some the respiratory waveform numerical value in the respiratory waveform is lower than preset lower threshold value; The size that compares those respiratory waveform numerical value; Its minima is crest value, calculates in the process of breathing rate, behind crest numerical value that obtains respiratory waveform and trough numerical value; Interval to respiratory waveform crest, trough sampled point is handled, thereby calculates breathing rate; H. respiratory waveform, breathing rate and breathing warning message are shown.
Method and apparatus characteristics of the present invention are that multidigit A/D (> 16bit is set) scheme; Gain after the preparatory amplification of breath signal through low power; Directly adopt multidigit A/D to obtain primary breath signal; Utilize the software among the MCU that the minutia of original breath signal is analyzed identification, obtain human body base resistance information, the amplitude threshold that human body base resistance information setting breathing rate capable of using calculates when obtaining more the respiratory waveform near actual signal.Owing to adopt multidigit A/D, hardware circuit has the change resistance detection range of broad, has improved the respiration measurement accuracy under the weak signal, has simplified hardware circuit.Contrast with prior art; The present invention uses multidigit A/D; Make measuring method of the present invention have wideer breath signal dynamic range, can measure bigger breathing and become the resistance signal, and the breath signal of having avoided patient moving to cause is difficult to the problem of fast quick-recovery after saturated.Simplified the breathing hardware circuit, reduced the introducing of electrical noise on the hardware circuit, replaced analog filter with digital filter; Have bigger design flexibility, more excellent filtering performance calculates the resistance of breathing base through breathing the DC component; Utilize and breathe the amplitude threshold that base resistance setting breathing rate calculates; Make breathing rate more stable calculation, more convenient, kept the more details of original breath signal, guaranteed the accuracy of feeble respiration signal measurement.
Description of drawings
Fig. 1 is the sketch map of respiration information detection method of the present invention.
Fig. 2 is the sketch map of respiration information checkout gear of the present invention.
Fig. 3 is one of embodiment of respiration information detection method of the present invention.
Fig. 4 be respiration information detection method of the present invention embodiment two.
The specific embodiment
In conjunction with above-mentioned description of drawings specific embodiment of the present invention.
By knowing among Fig. 2; Respiration information checkout gear of the present invention comprises successively bill unit 209 and master computer unit 210 on the breath signal collecting unit 201, prime amplifying unit 202, demodulating unit 203, gain and the bias unit 204 that connect, low-pass filter unit 205, A/D converting unit 206, breath signal pretreatment unit 207, breathing rate computing unit, breathing rate, the warning message, and said A/D converting unit is at least 16 a multidigit converting unit.Said breath signal collecting unit 201 is through the sensor acquisition breath signal; This breath signal is for breathing amplitude-modulated signal; Should breathe amplitude-modulated signal and be sent to prime amplifying unit 202; Breathe amplitude-modulated signal through 202 pairs of said prime amplifying units then and carry out the low power gain and amplify, and then the signal after will amplifying is input to demodulating unit 203 and carries out demodulation, the breath signal after the demodulation is gained and bias unit 204 carries out the amplification of breath signal once more through breathing; And the breath signal after will amplifying carries out bias treatment, and this breath signal is biased to suitable voltage range; And then this breath signal is input to low-pass filter unit 205 carries out low-pass filtering treatment, the noise signal of filtering high frequency.The breath signal that will carry out low-pass filtering treatment is sent to A/D converting unit 206 and carries out analog digital conversion, and the simulated respiration conversion of signals is become digital breath signal.Digital signal after the said conversion is sent to breath signal pretreatment unit 207 carry out pretreatment, eliminate baseline and noise in the breath signal, obtain human body base resistance information simultaneously; Wherein said breath signal pretreatment unit 207 comprises: low-pass filtering module 2071, high-pass filtering module 2072, breathing base resistance detection module 2073.Should be sent to low-pass filtering module 2071 by the numeral breath signal, low-pass filtering module 2071 carries out low-pass filtering treatment, is used for eliminating the high-frequency noise of breath signal, simultaneously respiratory waveform is carried out smoothing processing; The breath signal that will carry out after the low-pass filtering treatment is sent to high-pass filtering module 2072 respectively and breathes base resistance detection module 2073; 2072 pairs of these breath signals of wherein said high-pass filtering module carry out high pass to be handled, and is used to eliminate baseline, obtains level and smooth respiratory waveform.Said breathing base resistance detection module 2073 is used for this breath signal is detected, and obtains human body base resistance information.The breath data that obtains through respiratory waveform pretreatment unit 207 is sent to breathing rate computing unit 208; Level and smooth respiratory waveform that obtains and human body base resistance information are sent to breathing rate computing unit 208; Said breathing rate computing unit 208 is according to the amplitude threshold of preset respiratory wave; Detect the crest and the trough value of respiratory wave; Obtain breathing rate through further processing then, obtain breathing warning message according to this breathing rate.Wherein said preset threshold value comprises that upper threshold value follows lower threshold value; If the numerical value of some respiratory waveform is higher than preset upper threshold value in the respiratory waveform, then, confirm crest value through the size of those numerical value relatively, promptly in those numerical value maximum be crest value; If the numerical value of some respiratory waveform is lower than preset lower threshold value in the respiratory waveform, then, confirm the trough value through the size of those numerical value relatively, promptly in those numerical value minimum be the trough value; Crest value and trough value according to the respiratory waveform that obtains calculate breathing rate; The transmission that bill unit 209 is used for respiratory waveform, breathing rate and breathing warning message on said breathing rate, the warning message is sent to master computer unit 210 with those information; Said master computer unit 210 is used for the demonstration to respiratory waveform, breathing rate and breathing warning message.
Bill unit all is arranged in the single-chip microcomputer on said breath signal pretreatment unit 207, breathing rate computing unit 208 and breathing rate, the warning message; Said A/D converting unit 206 can be a high-resolution modulus conversion chip independently, also can be the inner integrated high-resolution analog-digital converter of single-chip microcomputer., and said A/D converting unit is at least 16 multidigit converting unit, wherein said A/D converting unit 206 connects the breath signal pretreatment unit 207 of said single-chip microcomputer through the communication modes of SPI, I2S or I2C.
By knowing among Fig. 3, respiration information checkout gear of the present invention comprises with lower unit:
Breath signal collecting unit 201 through pick off, is accomplished the collection to breath signal, and the signal of being gathered is for breathing amplitude-modulated signal.
Prime amplifying unit 202 comprises operational amplifier U1～U3, and resistance R 1～R7 is used for said breathing amplitude-modulated signal is amplified in advance.The voltage signal of said breath signal collecting unit 201 outputs is Vi+ and Vi-, and inputs to the in-phase input end of operational amplifier U1 and U2 respectively.The inverting input of said operational amplifier U1 and U2 connects together through resistance R 1; Resistance R 2 is connected between the outfan and inverting input of operational amplifier U1; Resistance R 3 is connected between the outfan and inverting input of operational amplifier U2, generally, makes R2=R3; Can calculate circuit gain, concrete computing formula is:
Wherein A1 representes, breathes the amplitude-modulated signal amplification multiple, and R1 and R2 are the resistance of resistance, has this formula can know that preamplifying circuit will breathe amplitude-modulated signal and amplify A1 times.
As shown in Figure 3, the differential signal of the double operational difference amplifier output that said operational amplifier U1 and U2 constitute inserts inverting input and the in-phase input end of operational amplifier U3 through resistance R 4 and R5.Outfan and the inverting input of resistance R 7 concatenation operation amplifier U3 constitute negative feedback.The in-phase input end of resistance R 6 concatenation operation amplifier U3 is to ground.Generally, get R4=R5, R6=R7 in the case, can obtain this Amplifier Gain, and concrete computing formula is:
It is the differential signal coverlet operational amplifier amplification multiple that A2 representes operational amplifier U1, U2 output.
Demodulating unit 203 comprises resistance R 8, diode D1, capacitor C 1.The outfan of operational amplifier U3 is connected to the positive pole of breathing diode D1 in the demodulator circuit through resistance R 8, and the negative pole of diode D1 is connected to an end of capacitor C 1, the other end ground connection of capacitor C 1.Resistance R 8, diode D1, capacitor C 1 have constituted diode and have breathed demodulator circuit, accomplish the demodulation to said breath signal.
Gain and bias unit 204; Comprise operational amplifier U4, resistance R 9, R10; The output of diode detection circuit is connected to the in-phase input end of operational amplifier U4; Resistance R 9 one ends are connected to reference voltage, and the other end is connected to the inverting input of operational amplifier U4, outfan and the inverting input of resistance R 10 concatenation operation amplifier U4.Described reference voltage V REF can be the filtered DC component of DA output voltage, PWM ripple, fixed voltage source dividing potential drop or the reference voltage output of single-chip microcomputer.The gain that said gain and bias unit provide is A3, and concrete computing formula is:
That is to say that the in-phase amplifier that operational amplifier U4 constitutes has amplified A3 doubly with breath signal once more.
Said gain and bias unit 204 are used for the proper A/D input range with the biasing of the breath signal after the demodulation.The number of elements of said gain and bias unit can further be simplified, and with operational amplifier U4 deletion, can accomplish the effect and the function of said gain and bias unit too, shown in figure four; The signal of the output of demodulator circuit will be without operational amplifier U4, but is directly inputted to the A/D converting unit, accomplishes the conversion to data by the A/D converting unit.
Low-pass filter unit 205 comprises resistance R 11, capacitor C 2, and the outfan of operational amplifier U4 is connected to an end of resistance R 11, and the other end of resistance R 11 is connected to an end of capacitor C 2, the other end ground connection of C2.Low-pass filter unit 205 is accomplished breath signal filtering, removes high-frequency noise, then filtered signal is input to the AD converting unit.
A/D converting unit 206; Comprise integrated circuit U5, said integrated circuit U5 is high resolution A/D switching device, and the input of said integrated circuit U5 is connected to an end of capacitor C 2; And communicate through spi bus and single-chip microcomputer, data are sent in the single-chip microcomputer through spi bus.Wherein high resolution A/D transducer can be a high-resolution modulus conversion chip independently, also can be the inner integrated high-resolution analog-digital converter of single-chip microcomputer.
The pretreatment that breath signal pretreatment unit 207 is accomplished breath signal, the baseline of elimination breath signal carries out smoothing processing to breath signal, and obtains human body base resistance information; Set the amplitude threshold that breathing rate calculates according to the base resistance information of this human body.The pretreatment unit 207 of breath signal comprises low-pass filtering module 2071, high-pass filtering module 2072, breathes base resistance detection module 2073.Breath signal through the conversion of A/D converting unit inputs to low-pass filtering module 2071, and this breath signal is carried out low-pass filtering treatment, eliminates the high-frequency noise in the breath signal; The breath signal that carries out after the low-pass filtering treatment divides two-way output, and one the tunnel transfers to high-pass filtering module 2072, this breath signal is carried out high-pass filtering handle, and the baseline of filtering respiratory wave is eliminated the low frequency wonder of breath signal simultaneously.Another road transfers to breathes base resistance detection module 2073, and breath signal is detected, and obtains human body base resistance information.
Breathing rate computing unit 208 is accomplished breathing rate and is calculated; Breathing rate computing unit 208 is according to predetermined amplitude threshold; Detect the crest value and the trough value of respiratory wave, obtain breathing rate according to said crest value and trough value again, and obtain breathing warning message according to breathing rate.
Bill unit 209 is sent to master computer unit 210 with respiratory waveform, breathing rate, breathing warning message on breathing rate, the warning message.
By knowing among Fig. 1, respiration information detection method of the present invention has comprised following steps:
Breath signal acquisition step 101: through the sensor acquisition breath signal, the signal of being gathered is for breathing amplitude-modulated signal.
Prime amplification procedure 102: the breathing amplitude-modulated signal to being gathered amplifies in advance, improves the amplitude of breathing amplitude-modulated signal.
Demodulation step 103: the breathing amplitude-modulated signal to after the preparatory amplification carries out demodulation, from breathe amplitude-modulated signal, obtains the breath signal envelope, and this breath signal envelope has been represented real breath signal.Through containing DC component and AC component in the breath signal after the demodulation, the base resistance information of the corresponding human body of this DC component, the change resistance information of the corresponding human body of this AC component.When the base of human body hinders greatly, also bigger through the DC component of the breath signal after the demodulation.When the resistance of the base of human body hour, then the DC component of breath signal is also less.Promptly, can obtain the base resistance information of human body according to the size of this DC component.
Gain and biasing step 104: the breath signal to demodulation output gains with preset gain constant once more, improves the amplitude of breath signal with this, simultaneously breath signal is biased to proper A/D input voltage range; Usually, the A/D input voltage range is 0-5V.And, can on hardware, increase bias voltage usually in order breath signal to be biased to proper A/D input voltage range, and produce DC level through this bias voltage, breath signal is biased to proper A/D scope.
LPF step 105: to gain and bias treatment after breath signal carry out low-pass filtering treatment, filter away high frequency noise reduces the hardware noise of breath signal, improves the signal to noise ratio of breath signal.
A/D switch process 106: convert mimic breath signal the breath signal of numeral into, wherein A/D converter is generally selected for use be more than or equal 16 A/D converter.Adopting multidigit A/D to realize data transaction, is in order can when gamut measured breathing base resistance signal, to have enough resolution to gather and to breathe the resistance information that becomes.Especially under the comparatively faint situation of breath signal, the multidigit A/D converter has the dynamic range of signals of broad, with the accuracy that improves respiration measurement greatly.Multidigit A/D is connected with chip microcontroller through multiple communication modes such as SPI, I2S or I2C.This multidigit A/D promptly can be an A/D device independently, also can be A/D integrated on the single-chip microcomputer sheet.
Breath signal pre-treatment step 107: through the pretreatment of breath signal being eliminated the baseline of breath signal; Suppress the noise on the breath signal; Obtain respiratory waveform data stably; DC component according to respiratory waveform obtains breathing basic resistance information simultaneously, and this is breathed basic resistance information and is used for follow-up breathing rate calculating.The practical implementation process is: at first the breath signal after the A/D conversion is carried out buffer memory; And the breath signal of buffer memory carried out low-pass filtering treatment; Noise in the filtering breath signal and power frequency are disturbed, and wherein this low-pass filtering treatment also has breath signal is carried out level and smooth effect.Respiratory waveform after level and smooth is divided into two-way and carries out subsequent treatment; Said wherein one road respiratory waveform data are carried out high-pass filtering to be handled; Utilize high-pass filtering to handle and eliminate the baseline in the breath signal, obtain the AC component in the breath signal, this AC component promptly corresponds to the change resistance information of breath signal.Said other one road respiratory waveform data are breathed the base resistance detect processing; Owing to aforementioned breath signal has been carried out gain and bias treatment, the DC component that therefore obtains containing in the breath signal through low-pass filtering treatment also must be mapped through linear operation processing ability and the resistance of human body base.Wherein the method handled of this linear operation is, the DC component data divided by preset gain constant, and is deducted because the DC level that aforementioned bias voltage is introduced.Through the DC component that obtains after the above-mentioned computing, be the corresponding DC component of human body base resistance, can obtain corresponding human body base resistance information through this DC component.
Breathing rate calculation procedure 108: the pretreated breath data of said breath signal is handled, calculated breathing rate and obtain breathing warning message according to breathing rate.The practical implementation process is: obtain corresponding breathing base resistance information according to aforesaid breathing DC component, according to this base resistance information the amplitude threshold of respiratory wave is preset.For concrete respiratory wave, set upper and lower two amplitude thresholds, be respectively upper threshold value and lower threshold value.If some the respiratory waveform numerical value in the respiratory waveform data surpasses the upper threshold value of setting, then obtain its crest value through the size that compares those respiratory waveform numerical value.If some the respiratory waveform numerical value in the respiratory waveform data is lower than lower threshold value, then obtain its valley through the size that compares those respiratory waveform numerical value.Behind the crest of the respiratory waveform that obtains, the trough numerical value, the interval of the sampled point of the crest of respiratory waveform, trough is handled, can be calculated breathing rate.The breathing rate that obtains according to aforementioned calculation, and then obtain breathing warning message, wherein breathe warning message and comprise: breathing suffocates reports to the police and high and low breathing rate warning etc.
Send out step 109 on breathing rate, the warning message: with being dealt into master computer on respiratory waveform, breathing rate, the breathing warning message.
Master computer step display 110: master computer is accomplished the demonstration to respiratory waveform, breathing rate, breathing warning message.
Above content is to combine concrete preferred implementation to the further explain that the present invention did, and can not assert that practical implementation of the present invention is confined to these explanations.For the those of ordinary skill of technical field under the present invention, under the prerequisite that does not break away from the present invention's design, can also make some simple deduction or replace, all should be regarded as belonging to protection scope of the present invention.
Claims (10)
1. respiration information detection method, this method may further comprise the steps: A. gathers and breathes amplitude-modulated signal, and carries out prime and amplify;
B. the breath signal that amplifies through prime is carried out demodulation, and from breath signal, obtain the respiration information envelope;
C. the breath signal to demodulation output gains once more, and breath signal is biased to proper A/D input voltage range;
It is characterized in that: this method is further comprising the steps of:
D. the breath signal of handling in the C step is carried out low-pass filtering treatment, with the high-frequency noise filtering in the breath signal;
E. the breath signal of handling among the step D being carried out the A/D conversion, is digital breath signal with the simulated respiration conversion of signals;
F. this numeral breath signal is carried out pretreatment, eliminate the baseline of breath signal, obtain the respiratory waveform data, and obtain breathing resistance information and the basic resistance information of breathing of becoming according to the respiratory waveform data; G. hinder the information calculations breathing rate according to breathing base, and obtain to breathe warning message according to this breathing rate; H. respiratory waveform, breathing rate and breathing warning message are shown.
2. respiration information detection method according to claim 1 is characterized in that: also comprise step by step following in the step F: the breath signal after F1. changes A/D carries out low-pass filtering treatment; F2. the data that obtained in the F1 step are carried out high-pass filtering and handle, eliminate the baseline in the breath signal, obtain corresponding in the breath signal AC component that breath signal becomes resistance information, and obtain breath signal change resistance information according to this AC component; F3. the data that obtained in the F1 step are breathed the base resistance and detect processing, obtain the corresponding DC component of breathing basic resistance information in the breath signal, and obtain breath signal base resistance information according to this DC component.
3. according to the respiration information detection method described in claim 1 or 2; It is characterized in that: calculate in the process of breathing rate at step G; Breath signal base resistance information according to obtaining is preset the amplitude threshold of respiratory wave; Its this amplitude threshold comprises upper threshold value and lower threshold value, and obtains the crest value and the trough value of respiratory waveform according to this preset amplitude threshold, calculates and obtains breathing rate through obtaining crest value and trough value.
4. respiration information detection method according to claim 3; It is characterized in that: the step of the crest value of said acquisition respiratory waveform and trough value does; When some the respiratory waveform numerical value in the respiratory waveform is higher than the upper threshold value of setting; Compare the size of those respiratory waveform numerical value, its maximum is crest value; When some the respiratory waveform numerical value in the respiratory waveform is lower than preset lower threshold value, compare the size of those respiratory waveform numerical value, its minima is crest value.
5. according to the respiration information detection method described in the claim 3; It is characterized in that: among the step G in calculating the process of breathing rate; Behind crest numerical value that obtains respiratory waveform and trough numerical value; Interval to respiratory waveform crest, trough sampled point is handled, thereby calculates breathing rate.
6. respiration information checkout gear is characterized in that: the prime amplifying unit that this device comprises the breath signal collecting unit that is used to gather breath signal that connects successively, amplify breath signal, the demodulating unit of demodulation breath signal, to breath signal amplify and the gain of setovering and bias unit, to breath signal carry out low-pass filtering treatment low-pass filter unit, be used for the A/D converting unit of breath signal digital-to-analogue conversion, the signal processing unit that signal is handled and calculated and the display unit that the data result is shown.
7. respiration information checkout gear according to claim 6 is characterized in that: said A/D converting unit is at least 16 a multidigit converting unit.
8. respiration information checkout gear according to claim 6 is characterized in that: said signal processing unit comprises breath signal pretreatment unit and breathing rate computing unit; Said breath signal pretreatment unit is used for breath signal is carried out pretreatment, eliminates baseline and noise in the breath signal, obtains human body base resistance information; Said breathing rate computing unit is used for the amplitude threshold according to the preset respiratory wave of human body base resistance information, according to the crest value and the trough value of this amplitude threshold detection respiratory wave, calculates breathing rate according to this crest value and trough value again.
9. respiration information checkout gear according to claim 8 is characterized in that: said breath signal pretreatment unit comprises: low-pass filtering module, high-pass filtering module and breathing base resistance detection module; Said low-pass filtering module is used for breath signal is carried out low-pass filtering treatment, eliminates high-frequency noise and respiratory waveform is carried out smoothing processing; Said high-pass filtering module links to each other with said low-pass filtering module, is used for that breath signal is carried out high-pass filtering and handles, and the baseline of respiratory waveform is eliminated; Said breathing base resistance detection module links to each other with said low-pass filtering treatment, is used for the breath signal after the low-pass filtering treatment is detected, and obtains human body base resistance information.
10. respiration information checkout gear according to claim 6 is characterized in that: said A/D converting unit connects said signal processing unit through the communication modes of SPI, I2S or I2C.
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| CN105675527A (en) * | 2016-01-21 | 2016-06-15 | 深圳市理邦精密仪器股份有限公司 | Light emitting control method and light emitting control device for light sources |
| CN106039516A (en) * | 2016-06-24 | 2016-10-26 | 广州医软智能科技有限公司 | Oxygen inhalation face mask for apnea alarm |
| CN109009023A (en) * | 2018-08-03 | 2018-12-18 | 深圳市大耳马科技有限公司 | A kind of extracting method of breath signal, device, processing equipment and system |
| CN109222928A (en) * | 2018-08-03 | 2019-01-18 | 深圳市大耳马科技有限公司 | Extracting method, device, processing equipment and the system of breath signal |
| CN109646005A (en) * | 2018-12-10 | 2019-04-19 | 中国科学院电子学研究所 | Forced vital capacity calculation method, device, electronic equipment and storage medium |
| CN112516541A (en) * | 2020-11-25 | 2021-03-19 | 常州利明屏蔽有限公司 | Auxiliary training system used before MR and CT examination |
| CN112781645A (en) * | 2019-11-08 | 2021-05-11 | 深圳市理邦精密仪器股份有限公司 | Respiration signal simulation circuit and respiration signal simulation method |
| CN114176542A (en) * | 2021-12-24 | 2022-03-15 | 江西洪都航空工业集团有限责任公司 | Method for evaluating instantaneous physiological state of pilot |
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| CN103300861A (en) * | 2013-05-08 | 2013-09-18 | 深圳市科曼医疗设备有限公司 | Impedance respiration measuring system |
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| CN112781645A (en) * | 2019-11-08 | 2021-05-11 | 深圳市理邦精密仪器股份有限公司 | Respiration signal simulation circuit and respiration signal simulation method |
| CN112781645B (en) * | 2019-11-08 | 2023-11-07 | 深圳市理邦精密仪器股份有限公司 | Respiratory signal simulation circuit and respiratory signal simulation method |
| CN112516541A (en) * | 2020-11-25 | 2021-03-19 | 常州利明屏蔽有限公司 | Auxiliary training system used before MR and CT examination |
| CN114176542A (en) * | 2021-12-24 | 2022-03-15 | 江西洪都航空工业集团有限责任公司 | Method for evaluating instantaneous physiological state of pilot |
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