CN105326491B - A kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method - Google Patents
A kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method Download PDFInfo
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- CN105326491B CN105326491B CN201510754255.1A CN201510754255A CN105326491B CN 105326491 B CN105326491 B CN 105326491B CN 201510754255 A CN201510754255 A CN 201510754255A CN 105326491 B CN105326491 B CN 105326491B
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Abstract
A kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, it is related to a kind of medical electronics measuring method, due to dicrotic wave amplitude and cause the amplitude proportional relation of its pulse wave, after voltage peak caused by a time measuring normal pulse ripple, a threshold value is set, which is 1/3rd of voltage peak caused by normal pulse ripple；Be regarded as pulse wave caused by interference value of the sampled value below threshold value, until there is sampled value more than after threshold value, sampled value is just considered normal normal pulse wave voltage uphill process, after occurring the appearance of pulse wave voltage peak again, remembers the moment；By this twice the voltage peak time it is only poor can measure the time difference of pulse twice, and then acquire heart rate value；The present invention can monitor tissue caused voltage fluctuation signal in vascular pulsation in real time, can effectively remove interference caused by dicrotic wave.The stability of heart rate non-contact measurement can be greatly improved.
Description
Technical field
The present invention relates to a kind of medical electronics measuring methods, are specially that a kind of photo-electric reflection type pulse heart rate sensor is adaptive
Answer variable thresholding filtering method.
Background technology
Hurtless measure monitoring technology is the important directions of future medicine engineering development, and contains what is enriched in human pulse signal
Physiologic information also gradually causes the great interest of clinician.There are mainly three types of traditional pulses measure methods：First, from the heart
It is extracted in electric signal；Second is that from measurement blood pressure when the fluctuation that detects of pressure sensor calculate pulse heart rate；Third, photocapacitance
Area method.First two method extraction signal can all limit the activity of measured, if use for a long time can increase measured's physiology with
Psychological discomfort.And photoplethymograph pulses measure has side as one of most common method in monitoring measurement
Method is simple, wears the features such as convenient, reliability is high.The basic principle of photoplethymograph is to utilize tissue in vascular pulsation
Light transmittance difference is caused to carry out pulses measure.When light beam is through human peripheral blood vessel, since arteriopalmus hyperemia volume becomes
Change causes the light transmittance of light beam to change, and receives the light reflected through tissue by photoelectric transformer at this time, is changed into electricity
Signal is simultaneously amplified and is exported.Since pulse was beaten and periodically variable signal with the cycle of heart, pulsation blood vessel holds
Product also cyclically-varying, therefore, the change in electric cycle of photoelectric transformer is exactly pulse.Believed by gathering two neighboring pulse
The time difference of number peak value can convert to obtain heart rate.
But since, there are dicrotic wave, measurement result, which is interfered, causes heart rate measurement in photoplethymograph measurement process
As a result it is inaccurate.Currently in order to the influence of removal dicrotic wave, existing algorithm is all the delay after a pulse peak value is measured
A period of time measures next pulse peak value, removes the influence of dicrotic wave by delay process.But since human body is per pulse twice
Between time interval be not the same, cause time of the dicrotic wave after pulse peak value also different, at this moment by prolonging
It is just inaccurate that slow method removes pulse wave.
Due to dicrotic wave amplitude and cause the amplitude proportional relation of its pulse wave, the present invention proposes a kind of
Photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method passes through adaptive algorithm adjust automatically threshold value, filter
Fall the interference of dicrotic wave, obtain pulse heart rate exactly.
Existing algorithm：After certain a moment measures voltage peak caused by normal pulse ripple, after a period of time that is delayed,
Wave voltage uphill process of fighting is measured again, after pulse wave voltage peak occurs next time, remembers the moment.By this twice
The voltage peak time is only poor can to measure the time difference of pulse twice, and then acquires heart rate value.Due to dicrotic wave in time delay
Pass through, it is possible to remove the interference of dicrotic wave.
But since the time interval between the every pulse twice of human body is not the same, also just caused by normal pulse ripple
The time that dicrotic wave occurs after the time of voltage peak is different, this is because delay time is fixed, it can so just having
The phenomenon that dicrotic wave does not remove can occur.Normal pulse ripple is got rid of if increasing delay time and being also present with.It is so existing
There is the algorithm measurement precision not high.
After the T1 moment measures voltage peak Vi caused by normal pulse ripple, after delay time dT, measurement again is fought
Wave voltage uphill process after pulse wave voltage peak occurs next time, remembers moment T2.Pass through this voltage peak twice
Only poor time difference that can measure pulse twice time | T2-T1 |, and then acquire heart rate value.Due to dicrotic wave in time delay dT
Pass through, it is possible to remove the interference of dicrotic wave.
But since the time interval between the every pulse twice of human body is not the same, also just caused by normal pulse ripple
The time that dicrotic wave occurs after the time of voltage peak is different, this is because delay time dT is fixed, so just having
It is likely to occur the phenomenon that dicrotic wave does not remove.Normal pulse ripple is got rid of if increasing delay time dT and being also present with.Institute
It is not high with existing algorithm measurement precision.
The content of the invention
It is an object of the invention to provide a kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter sides
Method, this method filter out dicrotic pulse wave interference by normal pulse wave voltage peak threshold, avoid dicrotic wave time of occurrence not
The problem of fixed, since normal pulse wave voltage peak value is all different each time, and each subthreshold is all based on this
/ 3rd setting of pulse wave voltage peak is sampled, so also achieving the setting of self-adapting changeable threshold value, improves measurement essence
Degree.
The purpose of the present invention is what is be achieved through the following technical solutions：
A kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, the method is due to dicrotic wave
Amplitude and cause the amplitude proportional relation of its pulse wave, at a time measure voltage peak caused by normal pulse ripple
Afterwards, a threshold value is set, which is 1/3rd of voltage peak caused by normal pulse ripple；In next sampling
In, be regarded as pulse wave caused by interference value of the sampled value below threshold value until there is sampled value more than after threshold value, samples
Value is just considered normal normal pulse wave voltage uphill process, after occurring the appearance of pulse wave voltage peak again, when remembeing this
It carves；By this twice the voltage peak time it is only poor can measure the time difference of pulse twice, and then acquire heart rate value；
Its flow is as follows：
(1), after dicrotic wave threshold value initial value is set, program starts Infinite Cyclic and calculates heart rate value；
(2), sampled by sampling time interval for 2ms；
(3), made comparisons according to sampled value each time with a preceding sampled value, find pulse ascent stage；
(4), occur finding crest voltage at inflection point in ascent stage；
(5), it is weight if crest voltage is less than dicrotic wave threshold value by crest voltage compared with dicrotic wave threshold value
It fights the interference of ripple, filters the value, resampling is carried out back to (2) step；It is just if crest voltage is more than dicrotic wave threshold value
Normal pulse crest value, enters (6) step；
(6), dicrotic wave threshold value is updated；
(7), heart rate value is calculated；
(8), heart rate value is exported, back to (2) step, carries out next round sampling；
A kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, the algorithm are specific
Numerical value is as follows：
(1), setting filters out dicrotic wave threshold value E, initial value 1V；
(2), periodic samples are carried out to sensor, the sampling period is 2 milliseconds, if the sampled voltage read every time is Vi
(i=1,2,3…m)；
(3), when continuously there is Vi>Vi-1When, it represents that pulse wave is in ascent stage, records sampled value each time；
(4), occurs V in ascent stagei<Vi-1When, it represents peak value occur in ascent stage, records the crest voltage；
(5) if, the crest voltage is when being less than threshold value E, then it is assumed that the crest voltage is as caused by dicrotic wave, returns to the
(2) step；If the crest voltage is more than threshold value E, then it is assumed that the crest voltage is as caused by normal pulse ripple, and program continues
Operation；
(6), crest voltage is recorded, records time point, update dicrotic wave threshold value E is 1/3rd of new crest voltage；
(7), it is poor according to normal pulse crest value voltage time twice in succession, calculate heart rate value；
(8), heart rate value is exported, returns to (2) step, carries out next round sampling.
Beneficial effects of the present invention：The present invention can monitor tissue caused voltage fluctuation in vascular pulsation in real time
Signal can effectively remove interference caused by dicrotic wave.Since the tissue of different people is different to sensor response or same
One people voltage fluctuation signal caused by pulse wave fluctuation caused by the position difference of wearable sensors is strong and weak different, this hair
It is bright to employ a kind of self-adapting changeable threshold filter method and filter dicrotic wave, obtain heart rate value exactly.Based on this method, obtain
Innovate accuracy and the stability indicator of improved pulse heart rate detection equipment, be significantly better than International Organization for standardization ISO and
Domestic professional standard index, specific advantageous effect can be embodied in the improvement of following medical measurement index parameter：(1) it is same
Individual, after wearable sensors change in location, the heart rate value being calculated is with true heart rate value error at positive and negative 5 beats/min；(2)
Different people, since tissue is different to sensor response, the heart rate value being calculated is with true heart rate value error positive and negative 5
Beat/min.Therefore the present invention can greatly improve the stability of heart rate non-contact measurement.
Description of the drawings
Fig. 1 is the waveform diagram that photoplethymograph measures pulse wave；
Fig. 2 is the flow chart of the method for the present invention.
Map parameter：1 is normal pulse wave voltage waveform, and 2 be dicrotic pulse wave voltage waveform.T1 is current normal pulse ripple electricity
Voltage crest value sampling instant, T2 are the normal pulse wave voltage peak value sampling moment next time, and dT is normal pulse wave voltage peak twice
It is worth the time difference, Vi is normal pulse wave voltage peak value, and E is preceding positive threshold value.
Specific embodiment
Embodiment
The present invention is described in further detail with reference to the accompanying drawings and with reference to example.
As shown in Figure 1, the normal pulse wave voltage waveform of photoplethymograph measurement is as shown in Fig. 11, but in normal pulse
There are a dicrotic wave voltage waveforms 2 below for wave voltage waveform 1.
In order to remove the interference of dicrotic wave voltage waveform 2,
Inventive algorithm：Due to dicrotic wave amplitude and cause the amplitude proportional relation of its pulse wave, at the T1 moment
After voltage peak Vi caused by measuring normal pulse ripple, a threshold value E is set, caused by threshold voltage E is normal pulse ripple
/ 3rd of voltage peak Vi.In next sampling, sampled value below threshold value be regarded as pulse wave caused by
Interference value, until there is sampled value more than after threshold value, sampled value is just considered normal normal pulse wave voltage uphill process, when again
It is secondary occur pulse wave voltage peak appearance after, remember moment T2.By this twice the voltage peak time only poor can measure two
The time difference of secondary pulse, and then acquire heart rate value.Since the present invention is to filter out weight by normal pulse wave voltage peak threshold
It fights wave interference, avoids the unfixed problem of dicrotic wave time of occurrence.Since normal pulse wave voltage peak value is all each time
It is different, and each subthreshold is all based on this 1/3rd setting of sampling pulse wave voltage peak, so also realizing
The setting of self-adapting changeable threshold value.Improve measurement accuracy.
It is as shown in Figure 2 according to the flow chart that this algorithm designs：
(1), after dicrotic wave threshold value initial value E is set, program starts Infinite Cyclic and calculates heart rate value；
(2), sampled by sampling time interval for 2ms；
(3), made comparisons according to sampled value each time with a preceding sampled value, find pulse ascent stage；
(4), occur finding crest voltage at inflection point in ascent stage；
(5), by crest voltage compared with dicrotic wave threshold value, if crest voltage is less than dicrotic wave threshold value, we
It is considered the interference of dicrotic wave, filters the value, resampling is carried out back to (2) step；If crest voltage is more than dicrotic wave
Threshold value, it is believed that be normal pulse crest value, enter (6) step；
(6), dicrotic wave threshold value is updated；
(7), heart rate value is calculated；
(8), heart rate value is exported, back to (2) step, carries out next round sampling；
Flow combination concrete numerical value is done described further below again according to Fig. 2：
(1), setting filters out dicrotic wave threshold value E, initial value 1V；
(2), periodic samples are carried out to sensor, the sampling period is 2 milliseconds, if the sampled voltage read every time is Vi
(i=1,2,3…m)；
(3), when continuously there is Vi>During Vi-1, represent that pulse wave is in ascent stage, record sampled value each time；
(4), occurs Vi in ascent stage<It during Vi-1, represents peak value occur in ascent stage, records peak value electricity
Pressure；
(5) if, the crest voltage is when being less than threshold value E, then it is assumed that the crest voltage is as caused by dicrotic wave, returns to the
(2) step；If the crest voltage is more than threshold value E, then it is assumed that the crest voltage is as caused by normal pulse ripple, and program continues
Operation；
(6), crest voltage is recorded, records time point, update dicrotic wave threshold value E is 1/3rd of new crest voltage；
(7), it is poor according to normal pulse crest value voltage time twice in succession, calculate heart rate value；
(8), heart rate value is exported, returns to (2) step, carries out next round sampling.
Claims (2)
- A kind of 1. photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, which is characterized in that the method Amplitude and the amplitude proportional relation for causing its pulse wave due to dicrotic wave, at a time measure normal pulse ripple and cause Voltage peak after, set a threshold value, which is 1/3rd of voltage peak caused by normal pulse ripple；It is connecing In the sampling got off, be regarded as pulse wave caused by interference value of the sampled value below threshold value is more than until there is sampled value After threshold value, sampled value is just considered normal normal pulse wave voltage uphill process, occurs when occurring pulse wave voltage peak again Afterwards, the moment is remembered；By this twice the voltage peak time difference can measure the time difference of pulse twice, and then acquire heart rate Value；Its flow is as follows：(1), after dicrotic wave threshold value initial value is set, program starts Infinite Cyclic and calculates heart rate value；(2), sampled by sampling time interval for 2ms；(3), made comparisons according to sampled value each time with a preceding sampled value, find pulse ascent stage；(4), occur finding crest voltage at inflection point in ascent stage；(5), it is dicrotic wave if crest voltage is less than dicrotic wave threshold value by crest voltage compared with dicrotic wave threshold value Interference, filter the value, back to (2) step carry out resampling；It is normal arteries and veins if crest voltage is more than dicrotic wave threshold value It fights crest value, enters (6) step；(6), dicrotic wave threshold value is updated；(7), heart rate value is calculated；(8), heart rate value is exported, back to (2) step, carries out next round sampling.
- 2. a kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method according to claim 1, It is characterized in that, the method concrete numerical value is as follows：(1), setting filters out dicrotic wave threshold value E, initial value 1V；(2), periodic samples are carried out to sensor, the sampling period is 2 milliseconds, if the sampled voltage read every time is Vi(i=1, 2,3…m)；(3), when continuously there is Vi>Vi-1When, it represents that pulse wave is in ascent stage, records sampled value each time；(4), occurs V in ascent stagei<Vi-1When, it represents peak value occur in ascent stage, records the crest voltage；(5) if, the crest voltage be less than threshold value E when, then it is assumed that the crest voltage be as caused by dicrotic wave, return (2) Step；If the crest voltage is more than threshold value E, then it is assumed that the crest voltage is as caused by normal pulse ripple, and program is after reforwarding Row；(6), crest voltage is recorded, records time point, update dicrotic wave threshold value E is 1/3rd of new crest voltage；(7), it is poor according to normal pulse crest value voltage time twice in succession, calculate heart rate value；(8), heart rate value is exported, returns to (2) step, carries out next round sampling.
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| CN113034779B (en) * | 2019-12-24 | 2023-12-22 | 深圳怡化电脑股份有限公司 | Quality detection method, device and equipment for thickness sensor and readable medium |
| CN111803041B (en) * | 2020-06-19 | 2024-05-24 | 浙江澍源智能技术有限公司 | Human pulse peak prediction method and device |
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| US6463311B1 (en) * | 1998-12-30 | 2002-10-08 | Masimo Corporation | Plethysmograph pulse recognition processor |
| ITRM20030117A1 (en) * | 2003-03-17 | 2004-09-18 | Matteo Bonan | AUTOMATED METHOD OF DISCRIMINATION OF HEART RATE. |
| US7922665B2 (en) * | 2006-09-28 | 2011-04-12 | Nellcor Puritan Bennett Llc | System and method for pulse rate calculation using a scheme for alternate weighting |
| CN101361652B (en) * | 2007-08-07 | 2012-06-27 | 深圳迈瑞生物医疗电子股份有限公司 | Adaptive threshold waveform peak valley identification method and device |
| CN102247129B (en) * | 2011-06-15 | 2013-06-12 | 西安电子科技大学 | Method for identifying untypical wave crests and wave troughs of pulse wave |
| CN102293639B (en) * | 2011-06-30 | 2013-03-13 | 芜湖圣美孚科技有限公司 | Pulse condition signal time domain feature extraction method |
| CN102334986B (en) * | 2011-07-08 | 2013-09-25 | 重庆大学 | Method for identifying dicrotic notch point in arterial tension signal |
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