CN102551727B - Respiratory information detecting method and device - Google Patents
Respiratory information detecting method and device Download PDFInfo
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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, method and checkout gear that particularly human body respiration information detects.
Background technology
Respiration parameter is an important physiological parameter of clinical monitoring, when breathing appears in patient, suffocates when even dead, and the breathing by custodial care facility suffocates and reports to the police and can remind in time medical worker to note conditions of patients, the patient's that avoids delay golden hour.Clinically, the monitoring of respiration parameter adopts impedance method conventionally, because impedance method can be obtained respiration parameter in monitoring EGC parameter, does not need extra adnexa, realizes simply, is therefore 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 by cardiac diagnosis lead-line, this carrier signal is coupled to human body.When relative motion does not occur in the thoracic cavity of human body, with respect to the equiva lent impedance of breathing carrier signal, be changeless.When human body causes thoracic cavity that relative motion occurs due to breathing, with respect to high-frequency carrier signal, can produce small impedance variation.This small impedance variation can will be breathed carrier modulation, hardware circuit, by after the signal amplification after this modulation, demodulation, filtering, is input to A/D, by A/D, carries out data acquisition, and transfer data to MCU, by MCU, move corresponding algorithm and obtain breathing rate and breathe warning message.
As mentioned above, the breathing modulation signal that contains human body impedance change information must just can obtain breath signal through amplification, demodulation, but by conventionally containing higher DC component in the breath signal of demodulation, as being 4000 Europe in base resistance, variable resistance is that in the situation of 0.5 ohm, DC component is about 8000 times of left and right of AC component in theory, dynamic range is so big, if amplify AC, DC component with same gain,, when amplifying AC component, DC component causes hardware circuit saturated already.More seriously, DC component is not what fix, be that the variation with base impedance changes, and the size of base impedance varies with each individual.In addition, in clinical monitoring process, if patient moving can produce larger variable resistance, this variable resistance is enough to cause hardware circuit saturated.In order to address the above problem, prior art scheme adopts capacity coupled method conventionally, but because the bandwidth of breathing is 0.1～2.5Hz, its time constant reaches 1.6S left and right, large time constant like this, once patient moving causes hardware circuit saturated, hardware circuit is very long recovery time.Because Capacitance Coupled exists above-mentioned defect, part technical scheme is optimized this, employing is called " a kind of scheme of DC component automotive resistance ", in this scheme, utilize the breath signal after the demodulation of single-chip microcomputer Real-time Collection, and the breath signal gathering is processed, calculate in real time its DC component, by the equal big or small voltage signal of DA output of single-chip microcomputer and the breath signal DC component after demodulation, subtract each other, can significantly reduce the DC component in breath signal, after above-mentioned processing, again amplify and obtain breath signal.In " a kind of scheme of DC component automotive resistance ", the problem of existence is that scheme is very complicated, and single-chip microcomputer is easily introduced and disturbed in the process of offsetting breath signal DC component, and the breath signal of same low frequency is detected and causes adverse effect.
To sum up, restriction due to conventional art, respiration measurement circuit generally adopts low level A/D, because breath signal is very faint, if adopt low level A/D to need breath signal significantly to gain, need complicated amplifying circuit, or need to add coupling capacitance, hardware bucking circuit etc., cause software and hardware very complicated, and the in the situation that of human motion, this hardware circuit is easily saturated and be difficult to, from the fast quick-recovery of saturation, affect respiration parameter clinical monitoring effect.
Concluding the deficiencies in the prior art part is:
1, anti-movement effects is poor, and in clinical monitoring process, if patient moving, the variable resistance that motion produces easily exceeds measuring range, cause hardware saturated, and respiratory waveform is difficult to fast quick-recovery;
2,, because hardware dynamic is limited in scope, the saturated rear respiratory waveform distortion that easily causes of hardware, causes breathing rate mistake in computation.
3, low level A/D scheme, hardware circuit is complicated, easily introduces more respiratory noise, and the calculating of algorithm to breathing rate is breathed in impact;
4, hardware bucking circuit, needs constantly to detect the voltage signal of breathing DC component and can offsetting above-mentioned DC component by output after single-chip microcomputer computing, causes soft and hardware design very complicated;
5, the precision of hardware filtering device, owing to being subject to the impact of device discreteness, is difficult to breath signal accurately to be processed.
Summary of the invention
The invention provides a kind of respiratory information detecting method and device, utilization is carried out pretreatment to signal, and the mode that further adopts multidigit A/D conversion and software low-pass filtering and detection computations, solves the technical problem that in prior art, anti-movement effects is poor, circuit structure is complicated and respiratory waveform distorts.
The present invention for solve the problems of the technologies described above this respiration information checkout gear providing comprise successively connect for gathering the breath signal collecting unit of breath signal, the prime amplifying unit that breath signal is amplified, the demodulating unit of demodulation breath signal, gain and bias unit that breath signal is amplified and setovered, breath signal is carried out to the low-pass filter unit of low-pass filtering treatment, A/D converting unit for breath signal digital-to-analogue conversion, the signal processing unit that signal is processed and calculated and the display unit that data result is shown, the multidigit converting unit that described A/D converting unit is at least 16.Described signal processing unit comprises breath signal pretreatment unit and breathing rate computing unit; Described breath signal pretreatment unit, for breath signal is carried out to pretreatment, is eliminated baseline and noise in breath signal, obtains human body base resistance information; Described breathing rate computing unit, for according to the amplitude threshold of the default respiratory wave of human body base resistance information, detects crest value and the trough value of respiratory wave according to this amplitude threshold, then calculates breathing rate according to this crest value and trough value.Described breath signal pretreatment unit comprises: low-pass filtering module, high-pass filtering module and breathing base resistance detection module; Described low-pass filtering module, for breath signal is carried out to low-pass filtering treatment, is eliminated high-frequency noise and respiratory waveform is carried out to smoothing processing; Described high-pass filtering module is connected with described low-pass filtering module, for breath signal is carried out to high-pass filtering processing, the baseline of respiratory waveform is eliminated; Described breathing base resistance detection module is connected with described low-pass filtering treatment, for the breath signal to after low-pass filtering treatment, detects, and obtains human body base resistance information.
This respiratory information detecting method comprises the following steps: A. gathers and breathes amplitude-modulated signal, and carries out prime amplification;
B. the breath signal amplifying through prime is carried out to demodulation, and from breath signal, obtain respiration information envelope;
C. the breath signal of demodulation output is gained again, and breath signal is biased to suitable A/D input voltage range;
The method is further comprising the steps of:
D. the breath signal of processing in C step is carried out to low-pass filtering treatment, by the high-frequency noise filtering in breath signal;
E. the breath signal of processing in step D is carried out to A/D conversion, simulated respiration signal is converted to digital breath signal;
F. this numeral breath signal is carried out to pretreatment, eliminate the baseline of breath signal, obtain respiratory waveform data, and obtain breathing variable resistance information and breathe base resistance information according to 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 obtain in F1 step are carried out to high-pass filtering processing, eliminate the baseline in breath signal, obtain corresponding in breath signal the AC component of breath signal variable resistance information, and obtain breath signal variable resistance information according to this AC component; F3. the data that obtain in F1 step are breathed to base resistance Check processing, obtain the corresponding DC component of breathing base resistance information in breath signal, and obtain breath signal base resistance information according to this DC component; G. according to breathing base resistance information, calculate breathing rate, and obtain and breathe warning message according to this breathing rate, calculate in the process of breathing rate, according to the breath signal base resistance information obtaining, the amplitude threshold of respiratory wave is preset, its this amplitude threshold comprises upper threshold value and lower threshold value, and according to crest value and the trough value of this default amplitude threshold acquisition respiratory waveform, by obtaining crest value and trough value, calculate acquisition breathing rate; The step of the crest value of described acquisition respiratory waveform and trough value is, some the respiratory waveform numerical value in respiratory waveform higher than set upper threshold value time, the size of those respiratory waveform numerical value relatively, its maximum is crest value; Some respiratory waveform numerical value in respiratory waveform is during lower than default lower threshold value, the size that compares those respiratory waveform numerical value, its minima is crest value, calculate in the process of breathing rate, after obtaining the crest numerical value and trough numerical value of respiratory waveform, interval to respiratory waveform crest, trough sampled point is processed, thereby calculates breathing rate; H. respiratory waveform, breathing rate and breathing warning message are shown.
Method and apparatus feature of the present invention is that multidigit A/D (>16bit) scheme is set, by low power, gain after breath signal pre-amplification, directly adopt multidigit A/D to obtain original breath signal, utilize the software in MCU to analyze identification to the minutia of original breath signal, when obtaining the respiratory waveform that more approaches actual signal, obtain human body base resistance information, the amplitude threshold that can utilize human body base resistance information setting breathing rate to calculate.Owing to adopting multidigit A/D, hardware circuit has wider variable resistance detection range, has improved the respiration measurement accuracy under weak signal, has simplified hardware circuit.Be compared with the prior art, the present invention uses multidigit A/D, make measuring method of the present invention there is wider breath signal dynamic range, can measure larger breathing variable 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 breathing hardware circuit, reduced the introducing of electrical noise on hardware circuit, with digital filter, replaced analog filter, have larger design flexibility, more excellent filtering performance, hinders by breathing DC component calculating breathing base, utilize and breathe the amplitude threshold that breathing rate calculating is set in base resistance, breathing rate is calculated more stable, more convenient, retained the more details of original breath signal, guaranteed the accuracy of feeble respiration signal measurement.
Accompanying drawing explanation
Fig. 1 is the schematic diagram of respiratory information detecting method of the present invention.
Fig. 2 is the schematic diagram of respiration information checkout gear of the present invention.
Fig. 3 is one of embodiment of respiratory information detecting method of the present invention.
Fig. 4 be respiratory information detecting method of the present invention embodiment two.
The specific embodiment
In conjunction with above-mentioned accompanying drawing explanation specific embodiments of the invention.
Known in 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, warning message, the multidigit converting unit that described A/D converting unit is at least 16.Described breath signal collecting unit 201 is by sensor acquisition breath signal, this breath signal is for breathing amplitude-modulated signal, this breathing amplitude-modulated signal is sent to prime amplifying unit 202, then through 202 pairs of described prime amplifying units, breathe amplitude-modulated signal and carry out low power gain amplification, and then the signal after amplifying is input to demodulating unit 203 carries out demodulation, breath signal after demodulation is gained by breathing and bias unit 204 carries out the amplification of breath signal again, and the breath signal after amplifying is carried out to bias treatment, 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 carries out low-pass filtering treatment is sent to A/D converting unit 206 and carries out analog digital conversion, convert simulated respiration signal to digital breath signal.Digital signal after described conversion is sent to breath signal pretreatment unit 207 and carry out pretreatment, eliminate baseline and noise in 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.This numeral breath signal is sent to low-pass filtering module 2071, and low-pass filtering module 2071 carries out low-pass filtering treatment, for eliminating the high-frequency noise of breath signal, respiratory waveform is carried out to smoothing processing simultaneously; The breath signal carrying out after low-pass filtering treatment is sent to respectively to high-pass filtering module 2072 and breathes base resistance detection module 2073; 2072 pairs of these breath signals of wherein said high-pass filtering module carry out high pass processing, for eliminating baseline, obtain level and smooth respiratory waveform.Described breathing base resistance detection module 2073, for this breath signal is detected, obtains human body base resistance information.The breath data obtaining through respiratory waveform pretreatment unit 207 is sent to breathing rate computing unit 208; The level and smooth respiratory waveform obtaining and human body base resistance information are sent to breathing rate computing unit 208, described breathing rate computing unit 208 is according to the amplitude threshold of default respiratory wave, detect crest and the trough value of respiratory wave, then by further processing, obtain breathing rate, according to this breathing rate, obtain breathing warning message.Wherein said default threshold value comprises that upper threshold value follows lower threshold value; If the numerical value of some respiratory waveform is higher than default upper threshold value in respiratory waveform,, by the size of those numerical value relatively, determine crest value, in those numerical value maximum be crest value; If the numerical value of some respiratory waveform is lower than default lower threshold value in respiratory waveform,, by the size of those numerical value relatively, determine trough value, in those numerical value minimum be trough value; According to crest value and the trough value of the respiratory waveform obtaining, calculate breathing rate; On described breathing rate, warning message, bill unit 209, for the transmission to respiratory waveform, breathing rate and breathing warning message, is sent to master computer unit 210 by those information; Described master computer unit 210 is for the demonstration to respiratory waveform, breathing rate and breathing warning message.
On described breath signal pretreatment unit 207, breathing rate computing unit 208 and breathing rate, warning message, bill unit is all arranged in single-chip microcomputer, described A/D converting unit 206 can be high-resolution modulus conversion chip independently, can be also the inner integrated high-resolution analog-digital converter of single-chip microcomputer., and the described A/D converting unit multidigit converting unit that is at least 16, wherein said A/D converting unit 206 connects the breath signal pretreatment unit 207 of described single-chip microcomputer by the communication modes of SPI, I2S or I2C.
Known in Fig. 3, respiration information checkout gear of the present invention comprises with lower unit:
Breath signal collecting unit 201, by sensor, completes the collection to breath signal, and the signal gathering is for breathing amplitude-modulated signal.
Prime amplifying unit 202, comprises operational amplifier U1～U3, and resistance R 1～R7, for carrying out pre-amplification to described breathing amplitude-modulated signal.The voltage signal of described breath signal collecting unit 201 outputs is Vi+ and Vi-, and inputs to respectively the in-phase input end of operational amplifier U1 and U2.The inverting input of described operational amplifier U1 and U2 connects together by 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, make R2=R3, can calculate circuit gain, specific formula for calculation is:
Wherein A1 represents, breathes the multiple that amplitude-modulated signal amplifies, and the resistance that R1 and R2 are resistance has the known preamplifying circuit of this formula will breathe amplitude-modulated signal and amplified A1 doubly.
The differential signal of the double operational difference amplifier output that as shown in Figure 3, described operational amplifier U1 and U2 form is by inverting input and the in-phase input end of resistance R 4 and R5 access operational amplifier U3.Outfan and the inverting input of resistance R 7 concatenation operation amplifier U3, form 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 the gain of this amplifier, and specific formula for calculation is:
Be that A2 represents the multiple that the differential signal coverlet operational amplifier of operational amplifier U1, U2 output amplifies.
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 demodulator circuit by resistance R 8, the negative pole of diode D1 is connected to one end of capacitor C 1, the other end ground connection of capacitor C 1.Resistance R 8, diode D1, capacitor C 1 have formed diode and have breathed demodulator circuit, complete the demodulation to described 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 end are connected to reference voltage, 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 described gain and bias unit provide is A3, and specific formula for calculation is:
That is to say, the in-phase amplifier that operational amplifier U4 forms has amplified breath signal A3 doubly again.
Described gain and the bias unit 204 suitable A/D input range for the breath signal after demodulation is setovered.The number of elements of described gain and bias unit can further be simplified, and operational amplifier U4 is deleted, and can complete too effect and the function of described gain and bias unit, as shown in Figure IV; The signal of the output of demodulator circuit will be without operational amplifier U4, but is directly inputted to A/D converting unit, by the conversion of the complete paired data of 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 one end of resistance R 11, and the other end of resistance R 11 is connected to one end of capacitor C 2, the other end ground connection of C2.Low-pass filter unit 205 completes breath signal filtering, removes high-frequency noise, then filtered signal is input to AD converting unit.
A/D converting unit 206, comprise integrated circuit U5, described integrated circuit U5 is high resolution A/D switching device, and the input of described integrated circuit U5 is connected to one end of capacitor C 2, and communicate by spi bus and single-chip microcomputer, data are sent in single-chip microcomputer by spi bus.Wherein high resolution A/D transducer can be high-resolution modulus conversion chip independently, can be also the inner integrated high-resolution analog-digital converter of single-chip microcomputer.
Breath signal pretreatment unit 207 completes the pretreatment to breath signal, eliminates the baseline of breath signal, and breath signal is carried out to smoothing processing, and obtains human body base resistance information; According to the base resistance information of this human body, set the amplitude threshold that breathing rate calculates.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 to low-pass filtering treatment, eliminates the high-frequency noise in breath signal; The breath signal carrying out after low-pass filtering treatment divides two-way output, and a road transfers to high-pass filtering module 2072, and this breath signal is carried out to high-pass filtering processing, 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 completes breathing rate and calculates, breathing rate computing unit 208 is according to predetermined amplitude threshold, detect crest value and the trough value of respiratory wave, then obtain breathing rate according to described crest value and trough value, and obtain breathing warning message according to breathing rate.
On breathing rate, warning message, bill unit 209 is sent to master computer unit 210 by respiratory waveform, breathing rate, breathing warning message.
Known in Fig. 1, respiratory information detecting method of the present invention has comprised following steps:
Breath signal acquisition step 101: by sensor acquisition breath signal, the signal gathering is for breathing amplitude-modulated signal.
Prime amplification procedure 102: gathered breathing amplitude-modulated signal is carried out to pre-amplification, improve the amplitude of breathing amplitude-modulated signal.
Demodulation step 103: the breathing amplitude-modulated signal after pre-amplification is carried out to demodulation, obtain breath signal envelope from breathe amplitude-modulated signal, this breath signal envelope has represented real breath signal.In breath signal after demodulation, contain DC component and AC component, the base resistance information of the corresponding human body of this DC component, the variable resistance information of the corresponding human body of this AC component.When the base resistance of human body is larger, the DC component of the breath signal after demodulation is also larger.When the base resistance of human body hour, the DC component of breath signal is also less.According to the size of this DC component, can obtain the base resistance information of human body.
Gain and biasing step 104: the breath signal to demodulation output gains again with the gain constant of presetting, and with this, improves the amplitude of breath signal, breath signal is biased to suitable A/D input voltage range simultaneously; Conventionally, A/D input voltage range is 0-5V.And for breath signal being biased to suitable A/D input voltage range, conventionally can on hardware, increase bias voltage, and by this bias voltage, produce DC level, breath signal is biased to suitable A/D scope.
Low-pass filtering 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: the breath signal of simulation is converted to digital breath signal, wherein A/D converter is generally selected be more than or equal the A/D converter of 16.Adopting multidigit A/D to realize data transaction, is in order can, when gamut is measured breathing base resistance signal, to have enough resolution to gather and to breathe variable resistance information.Especially in the situation that breath signal is comparatively faint, multidigit A/D converter has wider dynamic range of signals, will greatly improve the accuracy of respiration measurement.Multidigit A/D is connected with chip microcontroller by communications such as SPI, I2S or I2C.This multidigit A/D can be A/D device independently, can be also A/D integrated on monolithic Bigpian.
Breath signal pre-treatment step 107: by the pretreatment of breath signal being eliminated to the baseline of breath signal, suppress the noise on breath signal, obtain respiratory waveform data stably, according to the DC component of respiratory waveform, obtain breathing base resistance information, this is breathed base resistance information and calculates for follow-up breathing rate simultaneously.Specific implementation process is: first the breath signal after A/D conversion is carried out to buffer memory, and the breath signal of buffer memory is carried out to low-pass filtering treatment, noise in filtering breath signal and power frequency are disturbed, and wherein this low-pass filtering treatment also has breath signal is carried out to level and smooth effect.Respiratory waveform after level and smooth is divided into two-way and carries out subsequent treatment, described wherein road respiratory waveform data are carried out to high-pass filtering processing, utilize high-pass filtering to process to eliminate the baseline in breath signal, obtain the AC component in breath signal, this AC component corresponds to the variable resistance information of breath signal.Described other road respiratory waveform data are breathed to base resistance Check processing, due to aforementioned, breath signal has been carried out to gain and bias treatment, the DC component that therefore obtains containing in breath signal through low-pass filtering treatment also must be mapped through linear operation processing ability and the resistance of human body base.The method that wherein this linear operation is processed is, DC component data, divided by default gain constant, and is deducted to the DC level of introducing due to aforementioned bias voltage.The DC component obtaining after above-mentioned computing, is human body base and hinders corresponding DC component, by this DC component, can obtain corresponding human body base resistance information.
Breathing rate calculation procedure 108: the pretreated breath data of described breath signal is processed, calculated breathing rate and obtain breathing warning message according to breathing rate.Specific implementation process is: according to aforesaid breathing DC component, obtain corresponding breathing base resistance information, 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 respiratory waveform data surpasses the upper threshold value of setting, by comparing the size of those respiratory waveform numerical value, obtain its crest value.If some the respiratory waveform numerical value in respiratory waveform data, lower than lower threshold value, obtains its valley by comparing the size of those respiratory waveform numerical value.After the crest of the respiratory waveform obtaining, trough numerical value, the interval of the sampled point of the crest of respiratory waveform, trough is processed, can be calculated breathing rate.According to the above-mentioned breathing rate calculating, and then obtain breathing warning message, wherein breathe warning message and comprise: breathe suffocate warning and high and low breathing rate warning etc.
On breathing rate, warning message, send out step 109: will on respiratory waveform, breathing rate, breathing warning message, be dealt into master computer.
Master computer step display 110: master computer completes the demonstration to respiratory waveform, breathing rate, breathing warning message.
Above content is in conjunction with concrete preferred implementation further description made for the present invention, can not assert that specific embodiment of the invention is confined to these explanations.For general technical staff of the technical field of the invention, without departing from the inventive concept of the premise, can also make some simple deduction or replace, all should be considered as belonging to protection scope of the present invention.
Claims (8)
1. a respiratory information detecting method, the method comprises the following steps: A. gathers and breathes amplitude-modulated signal, and carries out prime amplification;
B. the breath signal amplifying through prime is carried out to demodulation, and from breath signal, obtain respiration information envelope;
C. the breath signal of demodulation output is gained again, and breath signal is biased to suitable A/D input voltage range;
It is characterized in that: the method is further comprising the steps of:
D. the breath signal of processing in C step is carried out to low-pass filtering treatment, by the high-frequency noise filtering in breath signal;
E. the breath signal of processing in step D is directly carried out in the situation that not carrying out the counteracting of DC component A/D conversion, simulated respiration signal is converted to digital breath signal;
F. this numeral breath signal is carried out to pretreatment, eliminate the baseline of breath signal, obtain respiratory waveform data, and obtain breathing variable resistance information and breathe base resistance information according to respiratory waveform data; G. according to breathing base resistance information, calculate breathing rate, and obtain and breathe warning message according to this breathing rate; H. respiratory waveform, breathing rate and breathing warning message are shown;
At step G, calculate in the process of breathing rate, according to the breath signal base resistance information obtaining, the amplitude threshold of respiratory wave is preset, its this amplitude threshold comprises upper threshold value and lower threshold value, and according to crest value and the trough value of this default amplitude threshold acquisition respiratory waveform, by obtaining crest value and trough value, calculate acquisition breathing rate.
2. respiratory information detecting method according to claim 1, is characterized in that: in step F, also comprise step by step following: the breath signal after F1. changes A/D carries out low-pass filtering treatment; F2. the data that obtain in F1 step are carried out to high-pass filtering processing, eliminate the baseline in breath signal, obtain corresponding in breath signal the AC component of breath signal variable resistance information, and obtain breath signal variable resistance information according to this AC component; F3. the data that obtain in F1 step are breathed to base resistance Check processing, obtain the corresponding DC component of breathing base resistance information in breath signal, and obtain breath signal base resistance information according to this DC component.
3. respiratory information detecting method according to claim 1, it is characterized in that: the step of the crest value of described acquisition respiratory waveform and trough value is, some respiratory waveform numerical value in respiratory waveform higher than set upper threshold value time, the size that compares those respiratory waveform numerical value, its maximum is crest value; Some respiratory waveform numerical value in respiratory waveform is during lower than default lower threshold value, the size of those respiratory waveform numerical value relatively, and its minima is crest value.
4. according to the respiratory information detecting method described in claim 1, it is characterized in that: in step G in calculating the process of breathing rate, after obtaining the crest numerical value and trough numerical value of respiratory waveform, interval to respiratory waveform crest, trough sampled point is processed, thereby calculates breathing rate.
5. a respiration information checkout gear, it is characterized in that: this device comprise successively connect for gathering the breath signal collecting unit of breath signal, the prime amplifying unit that breath signal is amplified, the demodulating unit of demodulation breath signal, breath signal is carried out to the low-pass filter unit of low-pass filtering treatment, A/D converting unit for breath signal digital-to-analogue conversion, the signal processing unit that signal is processed and calculated and the display unit that data result is shown, and, carry out breath signal after low-pass filtering treatment and the in the situation that of canceling DC component not, directly carry out AD conversion,
Described signal processing unit comprises breath signal pretreatment unit and breathing rate computing unit; Described breath signal pretreatment unit, for breath signal is carried out to pretreatment, is eliminated baseline and noise in breath signal, obtains human body base resistance information; Described breathing rate computing unit, for according to the amplitude threshold of the default respiratory wave of human body base resistance information, detects crest value and the trough value of respiratory wave according to this amplitude threshold, then calculates breathing rate according to this crest value and trough value.
6. respiration information checkout gear according to claim 5, is characterized in that: the multidigit converting unit that described A/D converting unit is at least 16.
7. respiration information checkout gear according to claim 5, is characterized in that: described breath signal pretreatment unit comprises: low-pass filtering module, high-pass filtering module and breathing base resistance detection module; Described low-pass filtering module, for breath signal is carried out to low-pass filtering treatment, is eliminated high-frequency noise and respiratory waveform is carried out to smoothing processing; Described high-pass filtering module is connected with described low-pass filtering module, for breath signal is carried out to high-pass filtering processing, the baseline of respiratory waveform is eliminated; Described breathing base resistance detection module is connected with described low-pass filtering treatment, for the breath signal to after low-pass filtering treatment, detects, and obtains human body base resistance information.
8. respiration information checkout gear according to claim 7, is characterized in that: described A/D converting unit connects described signal processing unit by the communication modes of SPI, I2S or I2C.
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