CN105326491A - Self-adaptive variable threshold-value filtering method of photoelectric reflecting type pulse and heart rate sensor - Google Patents
Self-adaptive variable threshold-value filtering method of photoelectric reflecting type pulse and heart rate sensor Download PDFInfo
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- CN105326491A CN105326491A CN201510754255.1A CN201510754255A CN105326491A CN 105326491 A CN105326491 A CN 105326491A CN 201510754255 A CN201510754255 A CN 201510754255A CN 105326491 A CN105326491 A CN 105326491A
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Abstract
The invention discloses a self-adaptive variable threshold-value filtering method of a photoelectric reflecting type pulse and heart rate sensor, and relates to a medical electronic measuring method. The self-adaptive variable threshold-value filtering method is characterized in that since the amplitude of a dicrotic wave is directly proportional to the amplitude of a pulse wave causing the dicrotic wave, a threshold value is set after a voltage peak caused by a normal pulse wave is measured at a certain time, and the threshold-value voltage is one third of the voltage peak value caused by the normal pulse wave; sampling values which are smaller than the threshold value are all considered as interference values caused by the pulse wave, a sampling value is not considered as a voltage rising process of the normal pulse wave until the sampling value is greater than the threshold value, and a moment can be remembered when the voltage peak of the pulse wave appears again; the time difference between twice pulses can be measured through the time difference between the two voltage peaks, and further a heart rate value can be calculated; a voltage fluctuation signal, which is caused by vascular pulsation, of a human tissue can be monitored in real time, the interference caused by the dicrotic wave can be effectively removed, and the non-contact type heart rate measuring stability can be increased to a large extent.
Description
Technical field
The present invention relates to a kind of medical electronics measuring method, be specially a kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method.
Background technology
Hurtless measure monitoring technology is the important directions of future medicine engineering development, and containing abundant physiologic information in human pulse signal, also causes the great interest of clinician gradually.It is extract from electrocardiosignal that traditional pulses measure method mainly contains three kinds: one; Two is that the fluctuation that detects from pressure transducer during Measure blood pressure is to calculate pulse heart rate; Three is photoplethymographs.First two method extracts the activity that signal all can limit measured, if long-time use can increase measured's physiology and psychological discomfort.And photoplethymograph pulses measure measure as monitoring in one of the most general method, its have method simple, wear conveniently, reliability high.The ultimate principle of photoplethymograph utilizes tissue to cause light transmittance difference to carry out pulses measure when vascular pulsation.When light beam is through human peripheral blood vessel, because the congested volume change of arteriopalmus causes the light transmittance of light beam to change, now received the light reflected through tissue by photoelectric comparator, change the signal of telecommunication into and amplified and export.Because pulse to be beaten with cycle of heart and periodically variable signal, the also cyclically-varying of pulsation capacity of blood vessel, therefore, the change in electric cycle of photoelectric comparator is exactly pulse.Can be converted by the time difference gathering adjacent two pulse signal peak values and obtain heart rate.
But owing to there is dicrotic wave in photoplethymograph measuring process, cause interference to cause heart rate measurements inaccurate to measurement result.At present in order to remove the impact of dicrotic wave, existing algorithm is all that time delay a period of time measures next pulse peak value, is removed the impact of dicrotic wave by time delay process after measurement pulse peak value.But because the interval between every twice pulse of human body is not the same, cause the time of dicrotic wave after pulse peak value also different, at this moment remove pulse wave by related method thereof just inaccurate.
Due to dicrotic wave amplitude and cause its amplitude proportional relation of pulse wave, therefore, the present invention proposes a kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, automatically adjusts threshold value by adaptive algorithm, filter the interference of dicrotic wave, obtain pulse heart rate exactly.
Existing algorithm: after recording the voltage peak that normal pulse ripple causes certain a moment, after time delay a period of time, again measure wave voltage uphill process of fighting, until after pulse wave voltage peak occurs, remember this moment next time.By this twice voltage peak time only poor time difference that can record twice pulse, and then try to achieve heart rate value.Because in time delay, dicrotic wave passes through, so the interference of dicrotic wave can be removed.
But because the interval between every twice pulse of human body is not the same, the time that after the time of the voltage peak also just caused at normal pulse ripple, dicrotic wave occurs is different, this due to delay time be fixing, so just likely there is the phenomenon that dicrotic wave is not removed.If increase delay time also there will be, normal pulse ripple is got rid of.So existing algorithm measurement precision is not high.
After the T1 moment records the voltage peak Vi that normal pulse ripple causes, after delay time dT, again measure wave voltage uphill process of fighting, until after pulse wave voltage peak occurs, remember this moment T2 next time.By this twice voltage peak time only poor time difference that can record twice pulse | T2-T1|, and then try to achieve heart rate value.Because dicrotic wave in time delay dT passes through, so can remove the interference of dicrotic wave.
But because the interval between every twice pulse of human body is not the same, the time that after the time of the voltage peak also just caused at normal pulse ripple, dicrotic wave occurs is different, this due to delay time dT be fixing, so just likely there is the phenomenon that dicrotic wave is not removed.If increase delay time dT also there will be, normal pulse ripple is got rid of.So existing algorithm measurement precision is not high.
Summary of the invention
The object of the present invention is to provide a kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, the method by normal pulse wave voltage peak threshold come filtering dicrotic wave interference, avoid the unfixed problem of dicrotic wave time of occurrence, because normal pulse wave voltage peak value is all different each time, and threshold value all sets based on this sampling pulse wave voltage peak 1/3rd each time, so also achieve the setting of self-adapting changeable threshold value, improve certainty of measurement.
The object of the invention is to be achieved through the following technical solutions:
A kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, described method due to dicrotic wave amplitude and cause its amplitude proportional relation of pulse wave, after at a time recording the voltage peak that normal pulse ripple causes, set a threshold value, this threshold voltage is 1/3rd of the voltage peak that normal pulse ripple causes; In ensuing sampling, sampled value all thinks the interference value that pulse wave causes below threshold value, until after occurring that sampled value is greater than threshold value, sampled value just thinks normal normal pulse wave voltage uphill process, after again occurring that pulse wave voltage peak occurs, remember this moment; By this twice voltage peak time only poor time difference that can record twice pulse, and then try to achieve heart rate value;
Its flow process is as follows:
(1), after setting dicrotic wave threshold value initial value, program starts Infinite Cyclic and calculates heart rate value;
(2) be, that 2ms samples by sampling time interval;
(3), according to sampled value and a front sampled value each time make comparisons, searching pulse ascent stage;
(4), occur that crest voltage is found at flex point place at ascent stage;
(5), by crest voltage and dicrotic wave threshold value compare, if crest voltage is less than dicrotic wave threshold value, be the interference of dicrotic wave, filter this value, turn back to (2) step and carry out resampling; If crest voltage is greater than dicrotic wave threshold value, be normal pulse crest value, enter into (6) step;
(6), dicrotic wave threshold value is upgraded;
(7), heart rate value is calculated;
(8), export heart rate value, turn back to (2) step, carry out next round sampling;
A kind of described photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, the concrete numerical value of described algorithm is as follows:
(1), set filtering dicrotic wave threshold value E, initial value is 1V;
(2), to sensor carry out periodic samples, the sampling period is for being 2 milliseconds, if each sampled voltage read is V
i(i=1,2,3 ... m);
(3), when occurring V continuously
i>V
i-1time, represent that pulse wave is in ascent stage, record sampled value each time;
(4), in ascent stage, there is V
i<V
i-1time, represent and occurred peak value at ascent stage, record this crest voltage;
(5) if when this crest voltage is less than threshold value E, then think that this crest voltage is caused by dicrotic wave, return (2) step; If when this crest voltage is greater than threshold value E, then think that this crest voltage is caused by normal pulse ripple, program continues to run;
(6), record crest voltage, writing time point, upgrading dicrotic wave threshold value E is 1/3rd of new crest voltage;
(7), poor according to double normal pulse crest value voltage time, calculate heart rate value;
(8), export heart rate value, return (2) step, carry out next round sampling.
Beneficial effect of the present invention: the present invention can the voltage fluctuation signal that causes when vascular pulsation of Real-Time Monitoring tissue, effectively can remove the interference that dicrotic wave causes.Because the tissue of different people is different to sensor response, or same person fluctuate the strong and weak difference of voltage fluctuation signal caused due to the position pulse wave that causes of difference of wearable sensors, present invention employs a kind of self-adapting changeable threshold filter method and filter dicrotic wave, obtain heart rate value exactly.Based on this method, obtain accuracy and the stability indicator of innovating the pulse heart rate detection equipment after improving, greatly be better than International Organization for Standardization ISO and domestic industry standard index, its concrete beneficial effect can be embodied in the improvement of following medical measurement index parameter: (1) same person, after wearable sensors change in location, the heart rate value calculated and true heart rate value error are at positive and negative 5 beats/min; (2) different people, because tissue is different to sensor response, the heart rate value calculated and true heart rate value error are at positive and negative 5 beats/min.Therefore the present invention significantly can improve the stability of heart rate non-contact measurement.
Accompanying drawing explanation
Fig. 1 is the waveform schematic diagram that photoplethymograph measures pulse wave;
Fig. 2 is the flow chart of the inventive method.
Map parameter: 1 is normal pulse wave voltage waveform, and 2 is dicrotic pulse wave voltage waveform.T1 is the current normal pulse wave voltage peak value sampling moment, and T2 is normal pulse wave voltage peak value sampling moment next time, and dT is that twice normal pulse wave voltage time to peak is poor, and Vi is normal pulse wave voltage peak value, and E is front positive threshold value.
Detailed description of the invention
Embodiment
With reference to the accompanying drawings and in conjunction with example, the present invention is described in further detail.
As shown in Figure 1, as shown in Fig. 11, but there is a dicrotic wave voltage waveform 2 below at normal pulse wave voltage waveform 1 in the normal pulse wave voltage waveform that photoplethymograph is measured.
In order to remove the interference of dicrotic wave voltage waveform 2,
Algorithm of the present invention: due to dicrotic wave amplitude and cause its amplitude proportional relation of pulse wave, after the T1 moment records the voltage peak Vi that normal pulse ripple causes, set a threshold value E, this threshold voltage E is 1/3rd of the voltage peak Vi that normal pulse ripple causes.In ensuing sampling, sampled value all thinks the interference value that pulse wave causes below threshold value, until after occurring that sampled value is greater than threshold value, sampled value just thinks normal normal pulse wave voltage uphill process, after again occurring that pulse wave voltage peak occurs, remember this moment T2.By this twice voltage peak time only poor time difference that can record twice pulse, and then try to achieve heart rate value.Because the present invention carrys out the interference of filtering dicrotic wave by normal pulse wave voltage peak threshold, avoid the unfixed problem of dicrotic wave time of occurrence.Because normal pulse wave voltage peak value is all different each time, and threshold value all sets based on this sampling pulse wave voltage peak 1/3rd each time, so also achieve the setting of self-adapting changeable threshold value.Improve certainty of measurement.
According to the flow chart of this algorithm design as shown in Figure 2:
(1), after setting dicrotic wave threshold value initial value E, program starts Infinite Cyclic and calculates heart rate value;
(2) be, that 2ms samples by sampling time interval;
(3), according to sampled value and a front sampled value each time make comparisons, searching pulse ascent stage;
(4), occur that crest voltage is found at flex point place at ascent stage;
(5), by crest voltage and dicrotic wave threshold value compare, if crest voltage is less than dicrotic wave threshold value, we think the interference of dicrotic wave, filter this value, turn back to (2) step and carry out resampling; If crest voltage is greater than dicrotic wave threshold value, we think normal pulse crest value, enter into (6) step;
(6), dicrotic wave threshold value is upgraded;
(7), heart rate value is calculated;
(8), export heart rate value, turn back to (2) step, carry out next round sampling;
According to Fig. 2, flow process is done in conjunction with concrete numerical value again and is further illustrated as follows:
(1), set filtering dicrotic wave threshold value E, initial value is 1V;
(2), to sensor carry out periodic samples, the sampling period is for being 2 milliseconds, if each sampled voltage read is Vi (i=1,2,3 ... m);
(3), when occurring Vi>Vi-1 continuously, representing that pulse wave is in ascent stage, recording sampled value each time;
(4), when there is Vi<Vi-1 in ascent stage, represent and occurred peak value at ascent stage, record this crest voltage;
(5) if when this crest voltage is less than threshold value E, then think that this crest voltage is caused by dicrotic wave, return (2) step; If when this crest voltage is greater than threshold value E, then think that this crest voltage is caused by normal pulse ripple, program continues to run;
(6), record crest voltage, writing time point, upgrading dicrotic wave threshold value E is 1/3rd of new crest voltage;
(7), poor according to double normal pulse crest value voltage time, calculate heart rate value;
(8), export heart rate value, return (2) step, carry out next round sampling.
Claims (2)
1. a photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method, it is characterized in that, described method due to dicrotic wave amplitude and cause its amplitude proportional relation of pulse wave, after at a time recording the voltage peak that normal pulse ripple causes, set a threshold value, this threshold voltage is 1/3rd of the voltage peak that normal pulse ripple causes; In ensuing sampling, sampled value all thinks the interference value that pulse wave causes below threshold value, until after occurring that sampled value is greater than threshold value, sampled value just thinks normal normal pulse wave voltage uphill process, after again occurring that pulse wave voltage peak occurs, remember this moment; By this twice voltage peak time only poor time difference that can record twice pulse, and then try to achieve heart rate value;
Its flow process is as follows:
(1), after setting dicrotic wave threshold value initial value, program starts Infinite Cyclic and calculates heart rate value;
(2) be, that 2ms samples by sampling time interval;
(3), according to sampled value and a front sampled value each time make comparisons, searching pulse ascent stage;
(4), occur that crest voltage is found at flex point place at ascent stage;
(5), by crest voltage and dicrotic wave threshold value compare, if crest voltage is less than dicrotic wave threshold value, be the interference of dicrotic wave, filter this value, turn back to (2) step and carry out resampling; If crest voltage is greater than dicrotic wave threshold value, be normal pulse crest value, enter into (6) step;
(6), dicrotic wave threshold value is upgraded;
(7), heart rate value is calculated;
(8), export heart rate value, turn back to (2) step, carry 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 concrete numerical value of described algorithm is as follows:
(1), set filtering dicrotic wave threshold value E, initial value is 1V;
(2), to sensor carry out periodic samples, the sampling period is for being 2 milliseconds, if each sampled voltage read is V
i(i=1,2,3 ... m);
(3), when occurring V continuously
i>V
i-1time, represent that pulse wave is in ascent stage, record sampled value each time;
(4), in ascent stage, there is V
i<V
i-1time, represent and occurred peak value at ascent stage, record this crest voltage;
(5) if when this crest voltage is less than threshold value E, then think that this crest voltage is caused by dicrotic wave, return (2) step; If when this crest voltage is greater than threshold value E, then think that this crest voltage is caused by normal pulse ripple, program continues to run;
(6), record crest voltage, writing time point, upgrading dicrotic wave threshold value E is 1/3rd of new crest voltage;
(7), poor according to double normal pulse crest value voltage time, calculate heart rate value;
(8), export heart rate value, return (2) step, carry out next round sampling.
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Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106725396A (en) * | 2016-12-08 | 2017-05-31 | 上海交通大学 | A kind of noninvasive blood pressure measuring device by shooting and measuring method based on double pulse waves |
| CN111803041A (en) * | 2020-06-19 | 2020-10-23 | 浙江澍源智能技术有限公司 | Human body pulse peak prediction method and device |
| CN113034779A (en) * | 2019-12-24 | 2021-06-25 | 深圳怡化电脑股份有限公司 | Quality detection method, device and equipment of thickness sensor and readable medium |
| CN115014408A (en) * | 2021-09-17 | 2022-09-06 | 荣耀终端有限公司 | Electronic device |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7044918B2 (en) * | 1998-12-30 | 2006-05-16 | Masimo Corporation | Plethysmograph pulse recognition processor |
| US20060264766A1 (en) * | 2003-03-17 | 2006-11-23 | Matteo Bonan | Automated method for discriminating the cardiac beat |
| US20080082009A1 (en) * | 2006-09-28 | 2008-04-03 | Nellcor Puritan Bennett Inc. | System and method for pulse rate calculation using a scheme for alternate weighting |
| CN101361652A (en) * | 2007-08-07 | 2009-02-11 | 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 |
| CN102247129A (en) * | 2011-06-15 | 2011-11-23 | 西安电子科技大学 | Method for identifying untypical wave crests and wave troughs of pulse wave |
| CN102293639A (en) * | 2011-06-30 | 2011-12-28 | 芜湖圣美孚科技有限公司 | Pulse condition signal time domain feature extraction method |
| CN102334986A (en) * | 2011-07-08 | 2012-02-01 | 重庆大学 | Method for identifying dicrotic notch point in arterial tension signal |
-
2015
- 2015-11-09 CN CN201510754255.1A patent/CN105326491B/en not_active Expired - Fee Related
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7044918B2 (en) * | 1998-12-30 | 2006-05-16 | Masimo Corporation | Plethysmograph pulse recognition processor |
| US20110288383A1 (en) * | 1998-12-30 | 2011-11-24 | Diab Mohamed K | Plethysmograph pulse recognition processor |
| US20060264766A1 (en) * | 2003-03-17 | 2006-11-23 | Matteo Bonan | Automated method for discriminating the cardiac beat |
| US20080082009A1 (en) * | 2006-09-28 | 2008-04-03 | Nellcor Puritan Bennett Inc. | System and method for pulse rate calculation using a scheme for alternate weighting |
| CN101361652A (en) * | 2007-08-07 | 2009-02-11 | 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 |
| CN102247129A (en) * | 2011-06-15 | 2011-11-23 | 西安电子科技大学 | Method for identifying untypical wave crests and wave troughs of pulse wave |
| CN102293639A (en) * | 2011-06-30 | 2011-12-28 | 芜湖圣美孚科技有限公司 | Pulse condition signal time domain feature extraction method |
| CN102334986A (en) * | 2011-07-08 | 2012-02-01 | 重庆大学 | Method for identifying dicrotic notch point in arterial tension signal |
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106725396A (en) * | 2016-12-08 | 2017-05-31 | 上海交通大学 | A kind of noninvasive blood pressure measuring device by shooting and measuring method based on double pulse waves |
| CN106725396B (en) * | 2016-12-08 | 2019-12-10 | 上海交通大学 | Non-invasive beat-to-beat blood pressure measuring device and method based on double pulse waves |
| CN113034779A (en) * | 2019-12-24 | 2021-06-25 | 深圳怡化电脑股份有限公司 | Quality detection method, device and equipment of thickness sensor and readable medium |
| 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 |
| CN111803041A (en) * | 2020-06-19 | 2020-10-23 | 浙江澍源智能技术有限公司 | Human body pulse peak prediction method and device |
| CN115014408A (en) * | 2021-09-17 | 2022-09-06 | 荣耀终端有限公司 | Electronic device |
| CN115014408B (en) * | 2021-09-17 | 2023-08-01 | 荣耀终端有限公司 | Electronic equipment |
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