CN111387959A - Non-contact physiological parameter detection method based on IPPG - Google Patents
Non-contact physiological parameter detection method based on IPPG Download PDFInfo
- Publication number
- CN111387959A CN111387959A CN202010216499.5A CN202010216499A CN111387959A CN 111387959 A CN111387959 A CN 111387959A CN 202010216499 A CN202010216499 A CN 202010216499A CN 111387959 A CN111387959 A CN 111387959A
- Authority
- CN
- China
- Prior art keywords
- ippg
- signal
- heart rate
- physiological parameter
- parameter detection
- 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.)
- Pending
Links
- 238000001514 detection method Methods 0.000 title claims abstract description 19
- 238000000034 method Methods 0.000 claims abstract description 26
- 230000011218 segmentation Effects 0.000 claims abstract description 8
- 238000001228 spectrum Methods 0.000 claims abstract description 7
- 230000003321 amplification Effects 0.000 claims description 19
- 238000003199 nucleic acid amplification method Methods 0.000 claims description 19
- 238000004364 calculation method Methods 0.000 claims description 14
- 230000003595 spectral effect Effects 0.000 claims description 7
- 238000001914 filtration Methods 0.000 claims description 6
- 206010003658 Atrial Fibrillation Diseases 0.000 claims description 5
- 230000008030 elimination Effects 0.000 claims description 5
- 238000003379 elimination reaction Methods 0.000 claims description 5
- 230000008569 process Effects 0.000 claims description 5
- 230000029058 respiratory gaseous exchange Effects 0.000 claims description 5
- 230000033764 rhythmic process Effects 0.000 claims description 5
- 230000000241 respiratory effect Effects 0.000 claims description 4
- 230000037384 skin absorption Effects 0.000 claims description 4
- 231100000274 skin absorption Toxicity 0.000 claims description 4
- 238000000513 principal component analysis Methods 0.000 claims description 3
- 230000002194 synthesizing effect Effects 0.000 claims description 3
- 230000004397 blinking Effects 0.000 abstract description 3
- 230000001815 facial effect Effects 0.000 abstract description 3
- 231100000075 skin burn Toxicity 0.000 abstract description 3
- 206010053652 Limb deformity Diseases 0.000 abstract description 2
- 239000000284 extract Substances 0.000 abstract description 2
- 230000036387 respiratory rate Effects 0.000 abstract 1
- 238000013186 photoplethysmography Methods 0.000 description 7
- 230000008859 change Effects 0.000 description 6
- 208000024172 Cardiovascular disease Diseases 0.000 description 3
- 238000003384 imaging method Methods 0.000 description 3
- 230000001766 physiological effect Effects 0.000 description 3
- 210000004204 blood vessel Anatomy 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 230000031700 light absorption Effects 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 238000012544 monitoring process Methods 0.000 description 2
- 238000003672 processing method Methods 0.000 description 2
- 238000011282 treatment Methods 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000002612 cardiopulmonary effect Effects 0.000 description 1
- 230000036996 cardiovascular health Effects 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 230000035876 healing Effects 0.000 description 1
- 230000001788 irregular Effects 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 230000010412 perfusion Effects 0.000 description 1
- 230000002265 prevention Effects 0.000 description 1
- 230000005180 public health Effects 0.000 description 1
- 230000000284 resting effect Effects 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/024—Detecting, measuring or recording pulse rate or heart rate
- A61B5/02416—Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/0205—Simultaneously evaluating both cardiovascular conditions and different types of body conditions, e.g. heart and respiratory condition
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/024—Detecting, measuring or recording pulse rate or heart rate
- A61B5/02405—Determining heart rate variability
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/0816—Measuring devices for examining respiratory frequency
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06V—IMAGE OR VIDEO RECOGNITION OR UNDERSTANDING
- G06V10/00—Arrangements for image or video recognition or understanding
- G06V10/20—Image preprocessing
- G06V10/25—Determination of region of interest [ROI] or a volume of interest [VOI]
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06V—IMAGE OR VIDEO RECOGNITION OR UNDERSTANDING
- G06V10/00—Arrangements for image or video recognition or understanding
- G06V10/20—Image preprocessing
- G06V10/26—Segmentation of patterns in the image field; Cutting or merging of image elements to establish the pattern region, e.g. clustering-based techniques; Detection of occlusion
- G06V10/267—Segmentation of patterns in the image field; Cutting or merging of image elements to establish the pattern region, e.g. clustering-based techniques; Detection of occlusion by performing operations on regions, e.g. growing, shrinking or watersheds
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06V—IMAGE OR VIDEO RECOGNITION OR UNDERSTANDING
- G06V40/00—Recognition of biometric, human-related or animal-related patterns in image or video data
- G06V40/10—Human or animal bodies, e.g. vehicle occupants or pedestrians; Body parts, e.g. hands
- G06V40/16—Human faces, e.g. facial parts, sketches or expressions
- G06V40/168—Feature extraction; Face representation
- G06V40/171—Local features and components; Facial parts ; Occluding parts, e.g. glasses; Geometrical relationships
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06V—IMAGE OR VIDEO RECOGNITION OR UNDERSTANDING
- G06V40/00—Recognition of biometric, human-related or animal-related patterns in image or video data
- G06V40/10—Human or animal bodies, e.g. vehicle occupants or pedestrians; Body parts, e.g. hands
- G06V40/18—Eye characteristics, e.g. of the iris
Abstract
The invention discloses a non-contact physiological parameter detection method based on IPPG. Belongs to the field of video image processing; the method comprises the following steps: recording a video, Euler amplifying, face recognition, eliminating motion artifacts, acquiring a heart rate and acquiring heart rate variability and a respiratory rate; the physiological parameter detection system is designed for non-contact physiological parameter detection; the method has the advantages of no contact with a tested part, simple and easy operation and the like, can solve the problem that patients with skin burn or limb deformity and infants are difficult to use contact instruments to measure physiological parameters, extracts the region of interest by facial segmentation, avoids the influence of blinking of eyes on signals, effectively removes motion errors by adopting a combined sparse spectrum reconstruction algorithm, improves the signals, and can be suitable for detecting various physiological parameters.
Description
Technical Field
The invention relates to the field of video image processing, in particular to a non-contact physiological parameter detection system method based on IPPG.
Background
The burden of cardiovascular diseases is gradually increased, which becomes a great public health problem and the prevention and treatment of cardiovascular diseases are not easy. Among them, heart rate is an important physiological parameter for measuring cardiovascular health status, and plays an important role in daily monitoring and diagnosis and treatment. The fast resting heart rate can be used as an independent risk index to predict the morbidity and mortality of cardiovascular diseases, and the fast exercise heart rate can reflect the cardio-pulmonary function and also help to keep the exercise intensity at a proper level.
Currently, although Photoplethysmography (PPG) has been widely used in the biomedical field, there are still inherent limitations. The ability to achieve only a single point of monitoring, the detection process requires the sensor to be in contact with the skin, etc., limiting its utility in situations such as perfusion imaging and healing assessment or where free motion is required. Therefore, Imaging Photoplethysmography (IPPG), a non-contact measurement technique, has been increasingly emphasized in recent years, has the advantages of no contact with a tested part, simple and easy operation, and the like, and can solve the problem that patients with skin burn or limb disability and infants are difficult to measure physiological parameters by using contact instruments.
Disclosure of Invention
Aiming at the problems, the invention provides a non-contact physiological parameter detection system method based on IPPG; thereby solving the problem that the application of the current IPPG technology is limited by imaging equipment.
The technical scheme of the invention is as follows: a non-contact physiological parameter detection method based on IPPG comprises the following steps:
(1.1), recording video: the tested object is seated in front of the computer, the face of the tested object is aligned to the camera, and the camera carried by the computer is used for recording a video of one minute;
(1.2), Euler amplification: performing Euler amplification processing on the recorded video;
(1.3), region of interest selection: the method comprises the following steps of firstly obtaining the position of an eye region through face recognition, and then carrying out face segmentation on a face, wherein the segmentation step comprises the following steps:
(1.3.1) setting the length of the eye region as a and the width as b;
(1.3.2) selecting a face area with the length of a and the width of 1.5b below the face area as an interested area, and avoiding errors caused by inevitable physiological activities such as winking and the like;
(1.4) obtaining three-channel signals of the IPPG signal; calculating the gray average value of R, G, B three channels of the interesting region of each frame, performing linear combination operation on the three channels to make the signal closer to the real IPPG signal,
(1.5) elimination of motion artifacts: eliminating the motion artifact of the IPPG signal by adopting a joint sparse spectrum reconstruction algorithm; separating spectral regions that affect skin absorption; removing the spectral range with small influence factors;
(1.6), acquisition of heart rate: setting a frequency range of heart rate, extracting effective peak values in the frequency range, and converting the effective peak values into time domains to obtain heart rate values;
(1.7), acquisition of heart rate variability and respiration rate: respectively extracting 100 continuous RR interval data, performing phase space reconstruction on the RR interval data, constructing a probability density function curve, and distinguishing atrial fibrillation from normal sinus rhythm through a skewness coefficient of the probability density function curve and an abscissa position corresponding to a curve peak value so as to detect heart rate variability;
the results show that the method can rapidly detect heart rate variability by using 100 continuous pulse interval data to distinguish atrial fibrillation from normal sinus rhythm, wherein the accuracy rate is 0.94.
Further, in the euler amplification in the step (1.2), the brightness value of the pixel point in each detection image in the time sequence is analyzed, the low-frequency part is selected for amplification, and then the low-frequency part and the original image are superposed to synthesize a final image, so that weak change information is amplified.
Further, the euler amplification processing is performed on the recorded video in the step (1.2), and the euler amplification processing method includes the following steps:
(1.2.1) decomposing each frame image of the video signal into different spatial resolutions;
(1.2.2) performing time domain band-pass filtering processing on the image with each spatial resolution to extract an interested frequency band;
(1.2.3) amplifying the filtering result, namely multiplying the signal of the interested frequency band by an amplification factor;
(1.2.4) adding the amplified images with different spatial resolutions and the corresponding original images, and synthesizing the images with different spatial resolutions to obtain a final image.
Further, the acquisition of the heart rate in step (1.6) includes calculation in the time domain and calculation in the frequency domain;
wherein, the calculation in the time domain: a method of calculating heart rate with reference to the PPG technique, since the IPPG technique is derived based on the PPG technique; designing a self-fitting quadratic curve which fits the variation trend between two peak values, so that the interference of the dicrotic wave can be avoided; repeating the above process to find all peak points;
calculation in the frequency domain: the frequency domain adopts a Fourier transform method to convert the IPPG signal into the frequency domain; according to medical knowledge, a frequency range of the heart rate is set, effective peak values in the frequency range are extracted and converted into a time domain, and a heart rate result is obtained.
Further, in step (1.2), a laplacian image sequence is generated during euler expansion, and the change of the pixel value of the edge part of the image sequence is stored in the laplacian image sequence, that is, the signal related to the breathing motion is stored in the edge of the expanded image sequence; and taking the time sequence signal corresponding to each edge point as a variable, and extracting a first principal component signal from all edge point signals by using principal component analysis, wherein the signal is a respiratory signal.
The invention has the beneficial effects that: the physiological parameter detection system is designed for non-contact physiological parameter detection; the method has the advantages of no contact with a tested part, simple and easy operation and the like, can solve the problem that patients with skin burn or limb deformity and infants are difficult to use contact instruments to measure physiological parameters, extracts the region of interest by facial segmentation, avoids the influence of blinking of eyes on signals, effectively removes motion errors by adopting a combined sparse spectrum reconstruction algorithm, improves the signals, and can be suitable for detecting various physiological parameters.
Drawings
FIG. 1 is a flow chart of the architecture of the present invention;
fig. 2 is a schematic diagram of region of interest selection in the present invention.
Detailed Description
In order to more clearly illustrate the technical solution of the present invention, the present invention will be further described below; obviously, the following description is only a part of the embodiments, and it is obvious for a person skilled in the art to apply the technical solutions of the present invention to other similar situations without creative efforts; in order to more clearly illustrate the technical solution of the present invention, the following detailed description is made with reference to the accompanying drawings:
as shown in the figure; a non-contact physiological parameter detection method based on IPPG comprises the following steps:
(1.1), recording video: the tested object is seated in front of the computer, the face of the tested object is aligned to the camera, and the camera carried by the computer is used for recording a video of one minute;
(1.2), Euler amplification: performing Euler amplification processing on the recorded video;
(1.3), region of interest selection: the method comprises the following steps of firstly obtaining the position of an eye region through face recognition, and then carrying out face segmentation on a face, wherein the segmentation step comprises the following steps:
(1.3.1) setting the length of the eye region as a and the width as b;
(1.3.2) selecting a face area with the length of a and the width of 1.5b below the face area as an interested area, and avoiding errors caused by inevitable physiological activities such as winking and the like;
(1.4) obtaining three-channel signals of the IPPG signal; calculating the gray average value of R, G, B three channels of the interesting region of each frame, performing linear combination operation on the three channels to make the signal closer to the real IPPG signal,
(1.5) elimination of motion artifacts: eliminating the motion artifact of the IPPG signal by adopting a joint sparse spectrum reconstruction algorithm; separating spectral regions that affect skin absorption; removing the spectral range with small influence factors;
(1.6), acquisition of heart rate: setting a frequency range of heart rate, extracting effective peak values in the frequency range, and converting the effective peak values into time domains to obtain heart rate values;
(1.7), acquisition of heart rate variability and respiration rate: respectively extracting 100 continuous RR interval data, performing phase space reconstruction on the RR interval data, constructing a probability density function curve, and distinguishing atrial fibrillation from normal sinus rhythm through a skewness coefficient of the probability density function curve and an abscissa position corresponding to a curve peak value so as to detect heart rate variability;
the results show that the method can rapidly detect heart rate variability by using 100 continuous pulse interval data to distinguish atrial fibrillation from normal sinus rhythm, wherein the accuracy rate is 0.94.
Further, in the euler amplification in the step (1.2), the brightness value of the pixel point in each detection image in the time sequence is analyzed, the low-frequency part is selected for amplification, and then the low-frequency part and the original image are superposed to synthesize a final image, so that weak change information is amplified.
Further, the euler amplification processing is performed on the recorded video in the step (1.2), and the euler amplification processing method includes the following steps:
(1.2.1) decomposing each frame image of the video signal into different spatial resolutions;
(1.2.2) performing time domain band-pass filtering processing on the image with each spatial resolution to extract an interested frequency band;
(1.2.3) amplifying the filtering result, namely multiplying the signal of the interested frequency band by an amplification factor;
(1.2.4) adding the amplified images with different spatial resolutions and the corresponding original images, and synthesizing the images with different spatial resolutions to obtain a final image.
Further, the acquisition of the heart rate in step (1.6) includes calculation in the time domain and calculation in the frequency domain;
wherein, the calculation in the time domain: a method of calculating heart rate with reference to the PPG technique, since the IPPG technique is derived based on the PPG technique; designing a self-fitting quadratic curve which fits the variation trend between two peak values, so that the interference of the dicrotic wave can be avoided; repeating the above process to find all peak points;
calculation in the frequency domain: the frequency domain adopts a Fourier transform method to convert the IPPG signal into the frequency domain; according to medical knowledge, a frequency range of the heart rate is set, effective peak values in the frequency range are extracted and converted into a time domain, and a heart rate result is obtained.
Further, in step (1.2), a laplacian image sequence is generated during euler expansion, and the change of the pixel value of the edge part of the image sequence is stored in the laplacian image sequence, that is, the signal related to the breathing motion is stored in the edge of the expanded image sequence; and taking the time sequence signal corresponding to each edge point as a variable, and extracting a first principal component signal from all edge point signals by using principal component analysis, wherein the signal is a respiratory signal.
The acquisition of the IPPG signal mainly comprises the steps of Euler amplification, region of interest selection, acquisition of an IPPG three-channel signal and the like.
Euler's amplification is to analyze the brightness value of the pixel point in each image in the time sequence, select the low frequency part to amplify, then superpose with the original image and synthesize the final image, thus amplify the weak change information.
The detected area can not completely cover the camera view, so that the shot video inevitably contains background objects irrelevant to calculation; the signal-to-noise ratio of the signal can be weakened due to the irregular change of the background objects, and the next calculation is influenced; therefore, the image should be segmented first, and only human tissue is reserved after the background environment is removed.
Because the volume of the blood vessel changes, the intensity of the reflected light on the skin surface of each part changes, so when the IPPG technology is used for measurement, the skin at any position can be selected theoretically; however, considering the amount of blood vessels, the convenience of measurement, the difficulty of identifying the measured part, and the like, all or part of the facial area of a person is generally selected to collect signals; the subject is to avoid errors caused by unavoidable physiological activities such as blinking by dividing a face region and selecting the face region below eyes as an interested region.
According to the light absorption curve and the three channel absorption curves of the CMOS camera, the light absorption overlapping part of the green channel and the skin is the largest, so that the signal with better signal-to-noise ratio compared with the blue channel and the red channel can be obtained by extracting the green channel IPPG signal; in order to enable the signal to be closer to the IPPG signal, linear operation is carried out on the three channels, the spectral interval influencing the skin absorption can be separated, and the spectral range with small influence factors is removed; the three channels are linearly combined to construct a new signal, so that other noise influences can be removed as far as possible.
The combined sparse spectrum reconstruction algorithm is applied to more strenuous physical exercise by a subject, the elimination effect of motion artifacts is better, and meanwhile, the algorithm can be better applied under the condition of lower sampling rate; therefore, the elimination of the motion artifact of the IPPG signal is carried out by adopting a joint sparse spectrum reconstruction algorithm.
Finally, it should be understood that the embodiments described herein are merely illustrative of the principles of embodiments of the present invention; other variations are possible within the scope of the invention; thus, by way of example, and not limitation, alternative configurations of embodiments of the invention may be considered consistent with the teachings of the present invention; accordingly, the embodiments of the invention are not limited to the embodiments explicitly described and depicted.
Claims (5)
1. A non-contact physiological parameter detection method based on IPPG is characterized by comprising the following steps:
(1.1), recording video: the tested object is seated in front of the computer, the face of the tested object is aligned to the camera, and the camera carried by the computer is used for recording a video of one minute;
(1.2), Euler amplification: performing Euler amplification processing on the recorded video;
(1.3), region of interest selection: the method comprises the following steps of firstly obtaining the position of an eye region through face recognition, and then carrying out face segmentation on a face, wherein the segmentation step comprises the following steps:
(1.3.1) setting the length of the eye region as a and the width as b;
(1.3.2) selecting a face area with the length a and the width 1.5b below the face area as an interested area;
(1.4) obtaining three-channel signals of the IPPG signal; calculating the gray average value of R, G, B three channels of the interesting region of each frame, performing linear combination operation on the three channels to make the signal closer to the real IPPG signal,
(1.5) elimination of motion artifacts: eliminating the motion artifact of the IPPG signal by adopting a joint sparse spectrum reconstruction algorithm; separating spectral regions that affect skin absorption;
(1.6), acquisition of heart rate: setting a frequency range of heart rate, extracting effective peak values in the frequency range, and converting the effective peak values into time domains to obtain heart rate values;
(1.7), acquisition of heart rate variability and respiration rate: and respectively extracting 100 continuous RR interval data, performing phase space reconstruction on the RR interval data, constructing a probability density function curve, and distinguishing atrial fibrillation from normal sinus rhythm through the skewness coefficient of the probability density function curve and the abscissa position corresponding to the peak value of the curve so as to detect the heart rate variability.
2. The IPPG-based non-contact physiological parameter detection method according to claim 1, wherein in the euler's expansion in step (1.2), the brightness value of the pixel point in each detected image in the time series is analyzed, the low frequency part is selected for expansion, and then the low frequency part is overlapped with the original image to synthesize the final image, so as to expand the weak variation information.
3. The IPPG-based non-contact physiological parameter detection method according to claims 1 and 2, wherein the euler expansion process is performed on the recorded video in step (1.2), which comprises the following steps:
(1.2.1) decomposing each frame image of the video signal into different spatial resolutions;
(1.2.2) performing time domain band-pass filtering processing on the image with each spatial resolution to extract an interested frequency band;
(1.2.3) amplifying the filtering result, namely multiplying the signal of the interested frequency band by an amplification factor;
(1.2.4) adding the amplified images with different spatial resolutions and the corresponding original images, and synthesizing the images with different spatial resolutions to obtain a final image.
4. The IPPG-based non-contact physiological parameter detection method according to claim 1, wherein the heart rate acquisition in step (1.6) comprises a calculation in the time domain and a calculation in the frequency domain;
wherein, the calculation in the time domain: designing a self-fitting quadratic curve, fitting the curve with the variation trend between two peak values, repeating the process, and finding all peak value points;
calculation in the frequency domain: the frequency domain adopts a Fourier transform method to convert the IPPG signal into the frequency domain; setting a frequency range of the heart rate, extracting effective peak values in the frequency range, and converting the effective peak values into a time domain to obtain a heart rate result.
5. The IPPG-based non-contact physiological parameter detection method according to claim 1, wherein in step (1.2), a laplacian image sequence is generated during euler expansion, and the changes of the pixel values of the edge portion of the image sequence are stored in the laplacian image sequence, i.e. the signals related to respiratory motion are stored in the edge of the expanded image sequence; and taking the time sequence signal corresponding to each edge point as a variable, and extracting a first principal component signal from all edge point signals by using principal component analysis, wherein the signal is a respiratory signal.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CN202010216499.5A CN111387959A (en) | 2020-03-25 | 2020-03-25 | Non-contact physiological parameter detection method based on IPPG |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CN202010216499.5A CN111387959A (en) | 2020-03-25 | 2020-03-25 | Non-contact physiological parameter detection method based on IPPG |
Publications (1)
Publication Number | Publication Date |
---|---|
CN111387959A true CN111387959A (en) | 2020-07-10 |
Family
ID=71411008
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CN202010216499.5A Pending CN111387959A (en) | 2020-03-25 | 2020-03-25 | Non-contact physiological parameter detection method based on IPPG |
Country Status (1)
Country | Link |
---|---|
CN (1) | CN111387959A (en) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN111839482A (en) * | 2020-07-30 | 2020-10-30 | 杭州艺兴科技有限公司 | Non-contact drug addict monitoring method and system based on IPPG |
CN111870235A (en) * | 2020-08-04 | 2020-11-03 | 杭州艺兴科技有限公司 | Drug addict screening method based on IPPG |
CN113499079A (en) * | 2021-06-18 | 2021-10-15 | 南京信息工程大学 | Atrial fibrillation detection method in electrocardiogram |
CN113628205A (en) * | 2021-08-25 | 2021-11-09 | 四川大学 | Non-contact respiratory frequency detection method based on depth image |
CN114764581A (en) * | 2022-06-16 | 2022-07-19 | 合肥心之声健康科技有限公司 | Atrial fibrillation classification method, device and system based on RR interphase space characteristics |
TWI795765B (en) * | 2021-04-28 | 2023-03-11 | 奧比森科技股份有限公司 | Non-contact physiological signal measurement apparatus, system and method |
CN116269285A (en) * | 2022-11-28 | 2023-06-23 | 电子科技大学 | Non-contact normalized heart rate variability estimation system |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN103340622A (en) * | 2013-07-01 | 2013-10-09 | 上海理工大学 | Atrial fibrillation automatic detection system based on smartphone |
CN104665803A (en) * | 2014-12-10 | 2015-06-03 | 上海理工大学 | Atrial fibrillation detecting system based on intelligent platform |
CN106686279A (en) * | 2016-12-28 | 2017-05-17 | 天津众阳科技有限公司 | Quasi-real-time color changing amplification system and method based on euler video amplification |
CN108272448A (en) * | 2018-03-29 | 2018-07-13 | 合肥工业大学 | A kind of contactless baby's physiological parameter monitoring method round the clock |
CN108433727A (en) * | 2018-03-15 | 2018-08-24 | 广东工业大学 | A kind of method and device of monitoring baby breathing |
CN109063763A (en) * | 2018-07-26 | 2018-12-21 | 合肥工业大学 | Video minor change amplification method based on PCA |
CN110236511A (en) * | 2019-05-30 | 2019-09-17 | 云南东巴文健康管理有限公司 | A kind of noninvasive method for measuring heart rate based on video |
CN110367950A (en) * | 2019-07-22 | 2019-10-25 | 西安爱特眼动信息科技有限公司 | Contactless physiologic information detection method and system |
-
2020
- 2020-03-25 CN CN202010216499.5A patent/CN111387959A/en active Pending
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN103340622A (en) * | 2013-07-01 | 2013-10-09 | 上海理工大学 | Atrial fibrillation automatic detection system based on smartphone |
CN104665803A (en) * | 2014-12-10 | 2015-06-03 | 上海理工大学 | Atrial fibrillation detecting system based on intelligent platform |
CN106686279A (en) * | 2016-12-28 | 2017-05-17 | 天津众阳科技有限公司 | Quasi-real-time color changing amplification system and method based on euler video amplification |
CN108433727A (en) * | 2018-03-15 | 2018-08-24 | 广东工业大学 | A kind of method and device of monitoring baby breathing |
CN108272448A (en) * | 2018-03-29 | 2018-07-13 | 合肥工业大学 | A kind of contactless baby's physiological parameter monitoring method round the clock |
CN109063763A (en) * | 2018-07-26 | 2018-12-21 | 合肥工业大学 | Video minor change amplification method based on PCA |
CN110236511A (en) * | 2019-05-30 | 2019-09-17 | 云南东巴文健康管理有限公司 | A kind of noninvasive method for measuring heart rate based on video |
CN110367950A (en) * | 2019-07-22 | 2019-10-25 | 西安爱特眼动信息科技有限公司 | Contactless physiologic information detection method and system |
Non-Patent Citations (1)
Title |
---|
马良: "基于普通摄像头的非接触式生理参数检测技术研究", 《中国优秀硕士学位论文全文数据库 医药卫生科技辑》 * |
Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN111839482A (en) * | 2020-07-30 | 2020-10-30 | 杭州艺兴科技有限公司 | Non-contact drug addict monitoring method and system based on IPPG |
CN111870235A (en) * | 2020-08-04 | 2020-11-03 | 杭州艺兴科技有限公司 | Drug addict screening method based on IPPG |
TWI795765B (en) * | 2021-04-28 | 2023-03-11 | 奧比森科技股份有限公司 | Non-contact physiological signal measurement apparatus, system and method |
CN113499079A (en) * | 2021-06-18 | 2021-10-15 | 南京信息工程大学 | Atrial fibrillation detection method in electrocardiogram |
CN113499079B (en) * | 2021-06-18 | 2023-12-08 | 南京信息工程大学 | Atrial fibrillation detection method in electrocardiogram |
CN113628205A (en) * | 2021-08-25 | 2021-11-09 | 四川大学 | Non-contact respiratory frequency detection method based on depth image |
CN114764581A (en) * | 2022-06-16 | 2022-07-19 | 合肥心之声健康科技有限公司 | Atrial fibrillation classification method, device and system based on RR interphase space characteristics |
CN116269285A (en) * | 2022-11-28 | 2023-06-23 | 电子科技大学 | Non-contact normalized heart rate variability estimation system |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CN111387959A (en) | Non-contact physiological parameter detection method based on IPPG | |
CN107529646B (en) | Non-contact heart rate measurement method and device based on Euler image amplification | |
Tasli et al. | Remote PPG based vital sign measurement using adaptive facial regions | |
CN110384491A (en) | A kind of heart rate detection method based on common camera | |
CN110662480A (en) | Device, system and method for measuring and processing physiological signals of a subject | |
Feng et al. | Motion artifacts suppression for remote imaging photoplethysmography | |
CA2934659A1 (en) | System and methods for measuring physiological parameters | |
CN111243739A (en) | Anti-interference physiological parameter telemetering method and system | |
CN112233813A (en) | Non-contact non-invasive heart rate and respiration measurement method and system based on PPG | |
Li et al. | An improvement for video-based heart rate variability measurement | |
JP2019097757A5 (en) | ||
CN112294282A (en) | Self-calibration method of emotion detection device based on RPPG | |
Chen et al. | Modulation model of the photoplethysmography signal for vital sign extraction | |
Qayyum et al. | Assessment of physiological states from contactless face video: a sparse representation approach | |
Zhang et al. | Using rear smartphone cameras as sensors for measuring heart rate variability | |
CN110584638A (en) | Non-contact heart rate measurement method based on CMOR wavelet | |
CN114246570B (en) | Near-infrared heart rate detection method by fusing peak signal-to-noise ratio and Peerson correlation coefficient | |
CN113693573B (en) | Video-based non-contact multi-physiological-parameter monitoring system and method | |
CN114331998A (en) | Non-contact cardiopulmonary coupling evaluation method | |
Wang et al. | KLT algorithm for non-contact heart rate detection based on image photoplethysmography | |
CN114387479A (en) | Non-contact heart rate measurement method and system based on face video | |
Pansare et al. | Heart Rate Measurement from Face and Wrist Video | |
Hu et al. | Study on Real-Time Heart Rate Detection Based on Multi-People. | |
CN113425282A (en) | Respiration rate monitoring method and device based on multispectral PPG blind source separation method | |
Gupta et al. | Denoising and Analysis of PPG Acquired From Different Body Sites Using Savitzky Golay Filter |
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 | ||
RJ01 | Rejection of invention patent application after publication |
Application publication date: 20200710 |