CN107582040B - Method and device for monitoring heart rhythm - Google Patents
Method and device for monitoring heart rhythm Download PDFInfo
- Publication number
- CN107582040B CN107582040B CN201710906597.XA CN201710906597A CN107582040B CN 107582040 B CN107582040 B CN 107582040B CN 201710906597 A CN201710906597 A CN 201710906597A CN 107582040 B CN107582040 B CN 107582040B
- Authority
- CN
- China
- Prior art keywords
- light intensity
- intensity signal
- heart
- heart rhythm
- vector
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
- 230000033764 rhythmic process Effects 0.000 title claims abstract description 84
- 238000000034 method Methods 0.000 title claims abstract description 30
- 238000012544 monitoring process Methods 0.000 title claims abstract description 25
- 230000017531 blood circulation Effects 0.000 claims abstract description 25
- 238000004458 analytical method Methods 0.000 claims abstract description 13
- 230000010349 pulsation Effects 0.000 claims abstract description 6
- 210000000624 ear auricle Anatomy 0.000 claims description 46
- 230000005540 biological transmission Effects 0.000 claims description 27
- 238000005259 measurement Methods 0.000 claims description 22
- 239000011159 matrix material Substances 0.000 claims description 12
- 210000003743 erythrocyte Anatomy 0.000 claims description 10
- 208000001871 Tachycardia Diseases 0.000 claims description 7
- 208000006218 bradycardia Diseases 0.000 claims description 7
- 230000036471 bradycardia Effects 0.000 claims description 7
- 230000006794 tachycardia Effects 0.000 claims description 7
- 206010003119 arrhythmia Diseases 0.000 claims description 6
- 230000006793 arrhythmia Effects 0.000 claims description 6
- 230000001678 irradiating effect Effects 0.000 claims description 5
- 238000004364 calculation method Methods 0.000 claims description 4
- GNFTZDOKVXKIBK-UHFFFAOYSA-N 3-(2-methoxyethoxy)benzohydrazide Chemical compound COCCOC1=CC=CC(C(=O)NN)=C1 GNFTZDOKVXKIBK-UHFFFAOYSA-N 0.000 claims description 3
- 238000012935 Averaging Methods 0.000 claims description 3
- 210000000707 wrist Anatomy 0.000 abstract description 5
- 230000009286 beneficial effect Effects 0.000 abstract description 4
- 230000037081 physical activity Effects 0.000 abstract description 4
- 239000000284 extract Substances 0.000 abstract description 3
- 230000010354 integration Effects 0.000 abstract description 3
- 230000009466 transformation Effects 0.000 abstract description 3
- 238000001514 detection method Methods 0.000 description 9
- 238000012545 processing Methods 0.000 description 5
- 239000000463 material Substances 0.000 description 4
- 238000013186 photoplethysmography Methods 0.000 description 4
- 229920002430 Fibre-reinforced plastic Polymers 0.000 description 3
- 239000002131 composite material Substances 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 239000011151 fibre-reinforced plastic Substances 0.000 description 3
- 230000010247 heart contraction Effects 0.000 description 3
- 238000004519 manufacturing process Methods 0.000 description 3
- 208000024172 Cardiovascular disease Diseases 0.000 description 2
- 230000000747 cardiac effect Effects 0.000 description 2
- 230000007547 defect Effects 0.000 description 2
- 238000012806 monitoring device Methods 0.000 description 2
- 230000035945 sensitivity Effects 0.000 description 2
- 208000000059 Dyspnea Diseases 0.000 description 1
- 206010013975 Dyspnoeas Diseases 0.000 description 1
- 206010033557 Palpitations Diseases 0.000 description 1
- 230000005856 abnormality Effects 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 238000002565 electrocardiography Methods 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000001228 spectrum Methods 0.000 description 1
Classifications
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02B—CLIMATE CHANGE MITIGATION TECHNOLOGIES RELATED TO BUILDINGS, e.g. HOUSING, HOUSE APPLIANCES OR RELATED END-USER APPLICATIONS
- Y02B20/00—Energy efficient lighting technologies, e.g. halogen lamps or gas discharge lamps
- Y02B20/40—Control techniques providing energy savings, e.g. smart controller or presence detection
Landscapes
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
The invention discloses a heart rhythm monitoring method and a device, wherein, the method extracts a blood flow light intensity signal which periodically changes caused by heart pulsation and a tissue light intensity signal generated by background tissues through a component analysis method, thereby realizing heart rhythm monitoring without complex operation operations such as volume integration or Fourier transformation, having the advantage of rapid operation, and solving the problems of large calculated amount, long time consumption and the like of the traditional heart rhythm monitoring method; the device is an ear clip type measuring device, avoids wearing fingers and wrists with more human body activities, is comfortable and convenient to wear, can be applied to hospitals or families, has small volume, is beneficial to placement and carrying, and saves space.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a portable, accurate and rapid heart rhythm monitoring device and method.
Background
Heart rhythm is an important parameter reflecting the state of the heart, tachycardia or bradycardia being manifestations of many cardiovascular diseases. Today, the life-time is increasingly faster, and the heart rhythm monitoring has important significance for preventing and daily monitoring of cardiovascular diseases such as palpitation, dyspnea and the like. The traditional rhythm monitoring mode is stethoscope monitoring, auscultates through the stethoscope, and the error is great and can't monitor for a long time. In contrast, currently common and highly accurate cardiac rhythm monitoring methods are Electrocardiograph (ECG) and Photoplethysmography (PPG). Electrocardiography is a technique for recording, from a body surface, a pattern of changes in electrical activity produced by the heart for each cardiac cycle. The electrocardiogram not only can monitor the heart rhythm, but also can accurately measure various electrocardio parameters, and is the most accurate heart rhythm measuring method in the current medicine. Photoplethysmography is based on the principle that the absorption intensity of arterial blood to light changes with heart beat, and a fingertip or earlobe is irradiated with a light source (red light or infrared light) of a specific wavelength, and then a photoelectric signal is converted into an electrical signal. The heart rhythm may be obtained by analysis and calculation of the rhythm, period, amplitude of the electrical signal.
The electrocardiographic method is taken as an example of [ CN1186646A ], and the method has the defects that the monitoring equipment is complicated to wear, an electrode plate needs to be attached to a skin fixed position and forms a closed loop, so that the electrocardiographic method is very inconvenient to use and is not suitable for daily monitoring.
Taking [ CN105105737A ] as an example, the method almost adopts a Fourier transform method to extract the spectrum information of the photoplethysmography pulse wave, and has the disadvantages of overlarge operation cost and long time consumption.
Disclosure of Invention
Aiming at the defects of the technology, the invention provides a method and a device for monitoring the heart rhythm in real time and judging whether the heart rhythm abnormality of tachycardia, bradycardia or arrhythmia exists or not; the device is an ear clip type measuring device, avoids wearing fingers and wrists with more activities on a human body, and is good in portability, comfortable and convenient to wear.
The invention solves the problems by adopting the following technical scheme:
a method of heart rhythm monitoring comprising the steps of:
irradiating the earlobe of the measured person by using an infrared light source, and transmitting an earlobe transmission light intensity signal;
collecting an earlobe transmission light intensity signal containing a blood flow light intensity signal and a tissue light intensity signal;
component analysis is carried out on the earlobe transmission light intensity signal to obtain a blood flow light intensity signal which periodically changes due to heart pulsation and a tissue light intensity signal generated by background tissues, and a measurement parameter which has physical meaning of red blood cell concentration is calculated;
and obtaining the heart rhythm signal, the heart rate and the heart rhythm state according to the measured parameters.
The method extracts the blood flow light intensity signal periodically changed due to heart beating and the tissue light intensity signal generated by background tissues through the component analysis method, thereby realizing heart rhythm monitoring without complex operation operations such as volume integration or Fourier transformation, having the advantage of rapid operation, and solving the problems of large calculated amount, long time consumption and the like of the traditional heart rhythm monitoring method.
Further, the component analysis and calculation of the measurement parameters includes the steps of:
a. assuming that the number of the earlobe transmission light intensity signals collected simultaneously is n, taking the (1+5 x (j-1)) th original light intensity data to the (5+5 x (j-1)) th original light intensity data of each earlobe transmission light intensity signal along the time sequence each time to form a j vector, and the mathematical formula is expressed as follows:
wherein X (j) is the j-th vector, I i,k The light intensity signal is transmitted for the ith earlobe along the kth raw light intensity data of the time series.
b. Let C (j) represent the covariance matrix of the j-th vector. Firstly, decomposing covariance matrix features, and then solving eigenvalue lambda of covariance matrix i (j) (i=1, 2, … 5) and corresponding feature vector a i (j) (i=1, 2, … 5), finally according to λ i (j) The sizes are arranged in descending order such that lambda 1 (j)>λ 2 (j)>…>λ 5 (j) A. The invention relates to a method for producing a fibre-reinforced plastic composite The mathematical expression of C (j) is:
wherein ,Xil(j) and Xkl (j) Lambda is the element of the ith row and the ith column and the element of the kth row and the ith column in the jth vector respectively i (j) In descending order of C (j)Arrange the characteristic value of the i, a i (j) Lambda is lambda i (j) Corresponding feature vector, C ik (j) Is the element of the ith row and kth column of the covariance matrix C in the jth vector.
c. Suppose F 1 (j),F 2 (j),…,F 5 (j) Component 1 to component 5 of vector C (j) in this order, then a i (j) Is the base of the ith component of the jth vector. Each component F i (j) The mathematical expression of (2) is:
wherein ,Fi (j) The ith component of the jth vector contains the ith component of the n lobe transmitted light intensity signals.
d. Respectively to F i (j) The average value of each component is obtained by averaging, so that the average intensity of the tissue light intensity signal generated by the background tissue and the average intensity of the blood flow light intensity signal in the jth vector are obtained. The mathematical expression of the above steps is:
X 0 (j) Is the average intensity, X, of the tissue light intensity signal generated by the background tissue in the jth vector RBC (j) The average intensity of the blood flow intensity signal of the j-th vector.
e. The measurement parameters are defined as the average intensity of the blood flow intensity signal divided by the average intensity of the tissue intensity signal, and the real-time measurement parameters are calculated. The measured parameter is in direct proportion to the concentration of red blood cells, but is not affected by blood flow velocity, and the mathematical expression can be expressed as:
and c, carrying out component analysis on the earlobe transmission light intensity signals through the steps a to e to obtain a blood flow light intensity signal periodically changed due to heart pulsation and a tissue light intensity signal generated by background tissues, calculating measurement parameters with physical meaning of red blood cell concentration, and further obtaining a heart rhythm signal, a heart rate and a heart rhythm state according to the measurement parameters.
Further, the method for obtaining the heart rhythm signal, the heart rate and the heart rhythm state according to the measured parameters comprises the following steps:
f. repeating the steps a-e, wherein the time resolution of two adjacent measurement parameters of the time sequence is 10ms, and the time is the abscissa and the measurement parameter corresponding to the moment is the ordinate to represent the heart rhythm signal.
g. When the first peak is detected, the timing is started, and when the second peak is detected, the interval T of the first heartbeat pulse can be obtained from the time interval of the two peaks 1 And so on, the interval T of each heartbeat can be continuously obtained i . When m heart beat intervals are obtained, the heart rate is then represented by:
wherein Heartrate is the number of beats per minute, i.e. heart rate.
h. Judging the heart rate obtained in the step g, and if the heart rate is less than 60, judging that the heart rate state is bradycardia; if the heart rate is greater than 100, the heart rate state is tachycardia; if the heart rate is between 60 and 100, the heart rhythm is normal. If |T i -T i-1 |>0.12s, the heart rhythm state is arrhythmia.
And f, processing and judging the measured parameters through the steps h to obtain the heart rhythm signal, heart rate and heart rhythm state of the tested person.
A heart rhythm detection device comprising: the device comprises an ear clip device for clamping the earlobe of a tested person, an infrared light source embedded at the left side of the ear clip device, a photoelectric detector embedded at the right side of the ear clip device and corresponding to the infrared light source, a storage arithmetic unit connected with the photoelectric detector and a display connected with the storage arithmetic unit; the infrared light source is used for irradiating the earlobe of the tested person and transmitting an earlobe transmission light intensity signal; the photoelectric detector is used for receiving the transmitted light intensity signals of the earlobe, converting the light signals into electric signals and then transmitting the electric signals to the storage arithmetic unit; the storage arithmetic unit is used for processing the transmitted light intensity signals of the earlobe, and calculating and obtaining heart rhythm data; the display is used for displaying the real-time heart rhythm and the heart rhythm state processed by the storage arithmetic unit. The device is an ear clip type measuring device, avoids wearing fingers and wrists with more human body activities, is comfortable and convenient to wear, can be applied to hospitals or families, has small volume, is beneficial to placement and carrying, and saves space.
Further, a window is arranged at the position of the shell of the ear clip device corresponding to the infrared light source, and a material with high transmission rate of the wavelength of the emission light source is selected as the window position. The material with high transmission rate of the wavelength of the emission light source is selected, so that the transmission of infrared light is facilitated, and the photoelectric detector can better receive the transmitted light intensity signal of the earlobe.
Further, the photodetector collects signals by using a photodetector based on a CMOS camera. The photoelectric detector based on the CMOS camera has higher detection sensitivity and detection precision.
Further, the acquisition rate of the photodetector is set to 500fps.
Further, the storage arithmetic unit sets the heart rhythm conditions corresponding to four heart rhythm states of normal heart rhythm, bradycardia, tachycardia or arrhythmia, then judges and measures the heart rhythm to obtain a heart rhythm judgment heart rhythm state, and finally displays the heart rhythm state through a display. The heart rhythm state of the tested person can be displayed visually through the display.
The beneficial effects of the invention are as follows: according to the method and the device for monitoring the heart rhythm, the blood flow light intensity signals which periodically change due to heart beating and the tissue light intensity signals generated by background tissues are extracted through the component analysis method, so that the heart rhythm monitoring is realized, complex operation operations such as volume integration or Fourier transformation are not needed, the method has the advantage of rapid operation, and the problems of large calculated amount, long time consumption and the like of the traditional heart rhythm monitoring method are solved; the device is an ear clip type measuring device, avoids wearing fingers and wrists with more human body activities, is comfortable and convenient to wear, can be applied to hospitals or families, has small volume, is beneficial to placement and carrying, and saves space.
Drawings
The invention is further described below with reference to the drawings and examples.
FIG. 1 is a flow chart of a method of heart rhythm monitoring of the present invention;
FIG. 2 is a schematic diagram of a heart rhythm detection device of the present invention;
FIG. 3 is a left side view of a heart rhythm detection device of the present invention (without a storage operator and display);
fig. 4 is a right side view of a heart rhythm detection device of the present invention (without the storage operator and display).
Detailed Description
Referring to fig. 1, a heart rhythm monitoring method of the present invention includes the steps of:
irradiating the earlobe of the measured person by using an infrared light source, and transmitting an earlobe transmission light intensity signal;
collecting an earlobe transmission light intensity signal containing a blood flow light intensity signal and a tissue light intensity signal;
component analysis is carried out on the earlobe transmission light intensity signal to obtain a blood flow light intensity signal which periodically changes due to heart pulsation and a tissue light intensity signal generated by background tissues, and a measurement parameter which has physical meaning of red blood cell concentration is calculated;
and obtaining the heart rhythm signal, the heart rate and the heart rhythm state according to the measured parameters.
The method extracts the blood flow light intensity signal periodically changed due to heart beating and the tissue light intensity signal generated by background tissue by the component analysis method, thereby accurately and rapidly realizing heart rhythm monitoring and solving the problems of large calculated amount, long time consumption and the like of the traditional heart rhythm monitoring method.
The transmitted light intensity signal of the earlobe transmitted by the earlobe of the tested person is irradiated by an infrared light source, and is an unprocessed original light intensity signal containing heartbeat information.
Further, the component analysis and calculation of the measurement parameters includes the steps of:
a. assuming that the number of the earlobe transmission light intensity signals collected simultaneously is n, taking the (1+5 x (j-1)) th original light intensity data to the (5+5 x (j-1)) th original light intensity data of each earlobe transmission light intensity signal along the time sequence each time to form a j vector, and the mathematical formula is expressed as follows:
wherein X (j) is the j-th vector, I i,k The light intensity signal is transmitted for the ith earlobe along the kth raw light intensity data of the time series.
b. Let C (j) represent the covariance matrix of the j-th vector. Firstly, decomposing covariance matrix features, and then solving eigenvalue lambda of covariance matrix i (j) (i=1, 2, … 5) and corresponding feature vector a i (j) (i=1, 2, … 5), finally according to λ i (j) The sizes are arranged in descending order such that lambda 1 (j)>λ 2 (j)>…>λ 5 (j) A. The invention relates to a method for producing a fibre-reinforced plastic composite The mathematical expression of C (j) is:
wherein ,Xil(j) and Xkl (j) Lambda is the element of the ith row and the ith column and the element of the kth row and the ith column in the jth vector respectively i (j) The feature values of the ith are arranged in descending order of C (j), a i (j) Lambda is lambda i (j) Corresponding feature vector, C ik (j) Is the element of the ith row and kth column of the covariance matrix C in the jth vector.
c. Suppose F 1 (j),F 2 (j),…,F 5 (j) Component 1 to component 5 of vector C (j) in this order, then a i (j) Is the base of the ith component of the jth vector. Each component F i (j) The mathematical expression of (2) is:
wherein ,Fi (j) The ith component of the jth vector contains the ith component of the n lobe transmitted light intensity signals.
d.F i (j) The variance of (a) is the characteristic root lambda of C (j) i (j) A. The invention relates to a method for producing a fibre-reinforced plastic composite According to a statistical theory, the first component with the highest variance comprises main characteristics of the earlobe transmission light intensity signal data, and can be regarded as a low-frequency part of the earlobe transmission light intensity signal data, and corresponds to a tissue light intensity signal generated by background tissue; the variance of the remaining components is sequentially reduced and is far smaller than that of the first component, and the redundant characteristics of the transmitted light intensity signal data of the earlobe are included, so that the transmitted light intensity signal data of the earlobe can be regarded as a high-frequency part corresponding to the blood flow light intensity signal. To reduce errors, the invention respectively aims at F i (j) The average value of each component is obtained by averaging, so that the average intensity of the tissue light intensity signal generated by the background tissue and the average intensity of the blood flow light intensity signal in the jth vector are obtained. The mathematical expression of the above steps is:
X 0 (j) Is the average intensity, X, of the tissue light intensity signal generated by the background tissue in the jth vector RBC (j) The average intensity of the blood flow intensity signal of the j-th vector.
e. The measurement parameters are defined as the average intensity of the blood flow intensity signal divided by the average intensity of the tissue intensity signal, and the real-time measurement parameters are calculated. The measured parameter is in direct proportion to the concentration of red blood cells, but is not affected by blood flow velocity, and the mathematical expression can be expressed as:
and c, carrying out component analysis on the earlobe transmission light intensity signals through the steps a to e to obtain a blood flow light intensity signal periodically changed due to heart pulsation and a tissue light intensity signal generated by background tissues, calculating measurement parameters with physical meaning of red blood cell concentration, and further obtaining a heart rhythm signal, a heart rate and a heart rhythm state according to the measurement parameters.
Further, the method for obtaining the heart rhythm signal, the heart rate and the heart rhythm state according to the measured parameters comprises the following steps:
f. repeating the steps a-e, wherein the time resolution of two adjacent measurement parameters of the time sequence is 10ms, and the time is the abscissa and the measurement parameter corresponding to the moment is the ordinate to represent the heart rhythm signal.
g. When the first peak is detected, the timing is started, and when the second peak is detected, the interval T of the first heartbeat pulse can be obtained from the time interval of the two peaks 1 And so on, the interval T of each heartbeat can be continuously obtained i . When m heart beat intervals are obtained, the heart rate is then represented by:
wherein Heartrate is the number of beats per minute, i.e. heart rate. In a specific implementation, the value of m takes 10.
h. Judging the heart rate obtained in the step g, and if the heart rate is less than 60, judging that the heart rate state is bradycardia; if the heart rate is greater than 100, the heart rate state is tachycardia; if the heart rate is between 60 and 100, the heart rhythm is normal. If |T i -T i-1 |>0.12s, the heart rhythm state is arrhythmia.
And f, processing and judging the measured parameters through the steps h to obtain the heart rhythm signal, heart rate and heart rhythm state of the tested person.
Referring to fig. 2-4, a heart rhythm detection device includes: the ear clip device 2 is used for clamping the earlobe 1 of the tested person, the infrared light source 3 is embedded at the left side of the ear clip device 2, the photoelectric detector 4 is embedded at the right side of the ear clip device 2 and corresponds to the infrared light source 3, the storage arithmetic unit 5 is connected with the photoelectric detector 4, and the display 6 is connected with the storage arithmetic unit 5; the infrared light source 3 is used for irradiating the earlobe 1 of the tested person and transmitting an earlobe transmission light intensity signal; the photoelectric detector 4 is used for receiving the transmitted light intensity signal of the earlobe, converting the light signal into an electric signal and then transmitting the electric signal to the storage arithmetic unit 5; the storage arithmetic unit 5 is used for processing the transmitted light intensity signals of the earlobe, and calculating and obtaining heart rhythm data; the display 6 is used for displaying the real-time heart rhythm and the heart rhythm state processed by the storage arithmetic unit 5. The device is an ear clip type measuring device, avoids wearing fingers and wrists with more human body activities, has better portability, is comfortable and convenient to wear, and is more suitable for daily heart rhythm monitoring.
Furthermore, a window is arranged at the position of the shell of the ear clip device 2 corresponding to the infrared light source 3, and a material with high transmission rate of the wavelength of the emission light source is selected as the window position. The material with high transmission rate of the wavelength of the emission light source is selected, so that the transmission of infrared light is facilitated, and the photoelectric detector 4 can better receive the transmitted light intensity signal of the earlobe.
Further, each infrared light source 3 corresponds to a photodetector 4.
Further, the photodetector 4 collects signals by using a photodetector based on a CMOS camera. The photoelectric detector based on the CMOS camera has higher detection sensitivity and detection precision.
Further, the acquisition rate of the photodetector 4 is set to 500fps.
Further, the storage arithmetic unit 5 sets the heart rhythm conditions corresponding to four heart rhythm states of normal heart rhythm, bradycardia, tachycardia or arrhythmia, then judges and measures the heart rhythm to judge the heart rhythm state, and finally displays the heart rhythm state through the display 6. The heart rhythm status of the subject can be presented very intuitively by the display 6.
The implementation steps of the heart rhythm monitoring device are as follows: the ear clip device 2 is clipped on the earlobe 1 of the tested person, then the infrared light emitted by the infrared light source 3 irradiates to the earlobe 1, then the transmitted light intensity signal of the earlobe transmitted by the earlobe 1 is received by the photoelectric detector 4 and converted into an electric signal, the collected electric signal is transmitted to the storage arithmetic unit 5 for data processing, and finally the heart rhythm state information of the tested person is displayed by the display 6.
The present invention is not limited to the above embodiments, but is merely preferred embodiments of the present invention, and the present invention should be construed as being limited to the above embodiments as long as the technical effects of the present invention are achieved by the same means.
Claims (1)
1. A method of heart rhythm monitoring comprising the steps of:
irradiating the earlobe of the measured person by using an infrared light source, and transmitting an earlobe transmission light intensity signal;
collecting an earlobe transmission light intensity signal containing a blood flow light intensity signal and a tissue light intensity signal;
component analysis is carried out on the earlobe transmission light intensity signal to obtain a blood flow light intensity signal which periodically changes due to heart pulsation and a tissue light intensity signal generated by background tissues, and a measurement parameter which has physical meaning of red blood cell concentration is calculated;
obtaining a heart rhythm signal, a heart rate and a heart rhythm state according to the measured parameters;
the component analysis and calculation of the measurement parameters comprises the following steps:
(a) Assuming that the number of the earlobe transmission light intensity signals collected simultaneously is n, taking the (1+5 x (j-1)) th original light intensity data to the (5+5 x (j-1)) th original light intensity data of each earlobe transmission light intensity signal along the time sequence each time to form a j vector, and the mathematical formula is expressed as follows:
(1-1)
wherein ,for the j-th vector, ">Transmitting an intensity signal for the ith earlobeKth raw intensity data along the time series;
(b) Let C (j) represent the covariance matrix of the jth vector, firstly decompose the covariance matrix features, and then find the feature value of the covariance matrixAnd corresponding feature vector->Finally according toThe sizes are arranged in descending order such that +.>The mathematical expression of C (j) is:
(1-2)；
wherein , and />The elements of the ith row and the ith column and the elements of the kth row and the kth column in the jth vector,the characteristic values of the ith are arranged in descending order of C (j),>is->Corresponding feature vector, < > and->Is the j thElements of the ith row and the kth column of the covariance matrix C in the vector;
(c) Assume thatIn turn is vector +>Component 1 to component 5 of->Is the base of the ith component of the jth vector; each component->The mathematical expression of (2) is:
(1-3)；
wherein ,the ith component of the jth vector contains the ith component of the n earlobe transmitted light intensity signals;
(d) Respectively toAveraging to obtain the average value of each component, thereby obtaining the average intensity of the tissue light intensity signal generated by the background tissue and the average intensity of the blood flow light intensity signal in the jth vector; the mathematical expression of the above steps is:
(1-4)；
(1-5)；
for the mean intensity of the tissue intensity signal in the j-th vector, which is generated by the background tissue,/is>The mean intensity of the blood flow intensity signal for the j-th vector;
(e) Defining a measurement parameter as the average intensity of a blood flow light intensity signal divided by the average intensity of a tissue light intensity signal, and calculating a real-time measurement parameter; the measured parameter is in direct proportion to the concentration of red blood cells, but is not affected by blood flow velocity, and the mathematical expression can be expressed as:
(1-6)；
the method for obtaining the heart rhythm signal, heart rate and heart rhythm state according to the measured parameters comprises the following steps:
(f) Repeating the steps a-e, wherein the time resolution of two adjacent measurement parameters of the time sequence is 10ms, and the time is the abscissa and the measurement parameter corresponding to the moment is the ordinate to represent the heart rhythm signal;
(g) When the first peak is detected, the timing is started, and when the second peak is detected, the interval of the first heartbeat pulse can be obtained from the time interval of the two peaksBy analogy, the interval of each heartbeat can be obtained continuously>The method comprises the steps of carrying out a first treatment on the surface of the When m heart beat intervals are obtained, the heart rate is then represented by:
(1-7)；
wherein Heartrate is the number of beats per minute, i.e., heart rate;
(h) Judging the heart rate obtained in the step g, and if the heart rate is less than 60, judging that the heart rate state is bradycardia; if the heart rate is greater than 100, the heart rate state is tachycardia; if the heart rate is between 60 and 100, the heart rate state is normal; if it isThe heart rhythm state is arrhythmia.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710906597.XA CN107582040B (en) | 2017-09-29 | 2017-09-29 | Method and device for monitoring heart rhythm |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710906597.XA CN107582040B (en) | 2017-09-29 | 2017-09-29 | Method and device for monitoring heart rhythm |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN107582040A CN107582040A (en) | 2018-01-16 |
| CN107582040B true CN107582040B (en) | 2023-08-08 |
Family
ID=61048142
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201710906597.XA Active CN107582040B (en) | 2017-09-29 | 2017-09-29 | Method and device for monitoring heart rhythm |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN107582040B (en) |
Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109431484B (en) * | 2018-12-10 | 2023-11-28 | 佛山科学技术学院 | Device and method for identifying gender of egg embryo based on heart rate measurement |
| CN109480816A (en) * | 2018-12-18 | 2019-03-19 | 安徽华米信息科技有限公司 | Rhythm of the heart monitoring method, device, electronic equipment and computer readable storage medium |
| CN111067392A (en) * | 2019-12-18 | 2020-04-28 | 佛山科学技术学院 | Bath chair with pulse detection alarm |
| CN114403823A (en) * | 2022-01-20 | 2022-04-29 | 杭州纳境科技有限公司 | Heart rate blood oxygen detection method and device and wearable device |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1317293A (en) * | 2000-03-22 | 2001-10-17 | Ge医疗系统环球技术有限公司 | Image forming method and device thereof and supersonic imaging device |
| CN101485565A (en) * | 2009-02-13 | 2009-07-22 | 华中科技大学 | Laser speckle blood current imaging and analyzing method |
| TW201038253A (en) * | 2009-04-28 | 2010-11-01 | Univ Chung Yuan Christian | Measuring device of heart rate variability |
| CN104068841A (en) * | 2014-07-07 | 2014-10-01 | 成都康拓邦科技有限公司 | Measuring method and device for measuring systole time parameter |
| CN105212915A (en) * | 2015-11-06 | 2016-01-06 | 重庆医科大学 | Personalized at the real-time non-invasive detection methods of body blood pressure |
| CN105249951A (en) * | 2015-09-17 | 2016-01-20 | 深圳市和虎科技有限公司 | Ultra-low power consumption exercise heart rate detection wireless module |
| CN106691410A (en) * | 2016-12-13 | 2017-05-24 | 佛山科学技术学院 | Pulse and red blood cell concentration monitoring instrument and method |
| CN106890008A (en) * | 2017-02-15 | 2017-06-27 | 北京大学第三医院 | A kind of cerebrovascular analysis system |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7512431B2 (en) * | 2005-09-13 | 2009-03-31 | Medtronic, Inc. | Normalization method for a chronically implanted optical sensor |
| US9538922B2 (en) * | 2009-10-30 | 2017-01-10 | Medtronic, Inc. | Monitoring an interval within the cardiac cycle |
-
2017
- 2017-09-29 CN CN201710906597.XA patent/CN107582040B/en active Active
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1317293A (en) * | 2000-03-22 | 2001-10-17 | Ge医疗系统环球技术有限公司 | Image forming method and device thereof and supersonic imaging device |
| CN101485565A (en) * | 2009-02-13 | 2009-07-22 | 华中科技大学 | Laser speckle blood current imaging and analyzing method |
| TW201038253A (en) * | 2009-04-28 | 2010-11-01 | Univ Chung Yuan Christian | Measuring device of heart rate variability |
| CN104068841A (en) * | 2014-07-07 | 2014-10-01 | 成都康拓邦科技有限公司 | Measuring method and device for measuring systole time parameter |
| CN105249951A (en) * | 2015-09-17 | 2016-01-20 | 深圳市和虎科技有限公司 | Ultra-low power consumption exercise heart rate detection wireless module |
| CN105212915A (en) * | 2015-11-06 | 2016-01-06 | 重庆医科大学 | Personalized at the real-time non-invasive detection methods of body blood pressure |
| CN106691410A (en) * | 2016-12-13 | 2017-05-24 | 佛山科学技术学院 | Pulse and red blood cell concentration monitoring instrument and method |
| CN106890008A (en) * | 2017-02-15 | 2017-06-27 | 北京大学第三医院 | A kind of cerebrovascular analysis system |
Also Published As
| Publication number | Publication date |
|---|---|
| CN107582040A (en) | 2018-01-16 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN109157202B (en) | Cardiovascular disease early warning system based on multi-physiological signal deep fusion | |
| WO2019161609A1 (en) | Method for analyzing multi-parameter monitoring data and multi-parameter monitor | |
| CN101357062B (en) | Vital signs parameter evaluation device based on volume pulsation wave detection | |
| CN108577830B (en) | User-oriented physical sign information dynamic monitoring method and system | |
| CN107582040B (en) | Method and device for monitoring heart rhythm | |
| WO2019161608A1 (en) | Multi-parameter monitoring data analysis method and multi-parameter monitoring system | |
| US20060287605A1 (en) | Heart rate variability analyzing device | |
| CN106901705A (en) | A kind of unaware human Body Physiology Multi-parameter harvester and acquisition method and application | |
| CN109691994A (en) | A kind of rhythm of the heart analysis method based on electrocardiogram | |
| CN103445767B (en) | The full-automatic autonomic nervous function detector of sensor monitoring interactive controlling | |
| CN111714088B (en) | Human body characteristic index detection method and system based on traditional Chinese medicine principle | |
| CN110897631B (en) | Real-time pregnancy monitoring device and method | |
| Polanía et al. | Method for classifying cardiac arrhythmias using photoplethysmography | |
| CN110236508A (en) | A kind of non-invasive blood pressure continuous monitoring method | |
| van Gent et al. | Heart rate analysis for human factors: Development and validation of an open source toolkit for noisy naturalistic heart rate data | |
| Kuzmin et al. | Mobile ECG monitoring system prototype and wavelet-based arrhythmia detection | |
| CN110881967A (en) | Non-invasive multi-segment peripheral arterial vessel elastic function detection method and instrument thereof | |
| Han et al. | Smartwatch PPG peak detection method for sinus rhythm and cardiac arrhythmia | |
| Ozturk et al. | Single-arm diagnostic electrocardiography with printed graphene on wearable textiles | |
| Ahmad et al. | A prototype of an integrated blood pressure and electrocardiogram device for multi-parameter physiologic monitoring | |
| CN210408412U (en) | Portable dynamic cardiovascular parameter acquisition equipment | |
| Ryan et al. | When is it good to use wristband devices to measure HRV?: Introducing a new method for evaluating the quality of data from photophlethysmography-based HRV devices | |
| Metshein et al. | Study of electrode locations for joint acquisition of impedance-and electro-cardiography signals | |
| Kew et al. | Wearable patch-type ECG using ubiquitous wireless sensor network for healthcare monitoring application | |
| Ahmed et al. | Heart rate and inter-beat interval computation to diagnose stress using ECG sensor signal |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |