CN113397535A - Non-contact oxyhemoglobin saturation detection method - Google Patents
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- 108010064719 Oxyhemoglobins Proteins 0.000 title abstract description 6
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- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 claims abstract description 65
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7235—Details of waveform analysis
- A61B5/725—Details of waveform analysis using specific filters therefor, e.g. Kalman or adaptive filters
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Abstract
The invention discloses a non-contact blood oxygen saturation detection method, which comprises the following steps: acquiring an initial face middle iPG signal by a face diagnosis instrument; processing the initial middle iPG signal to obtain an empirical parameter required for calculating the blood oxygen saturation, and obtaining the ratio of the light intensity projection change of the dual-wavelength light source in the blood tissue; and obtaining a blood oxygen saturation value according to the empirical parameters. The invention provides a non-contact oxyhemoglobin saturation detection method, which obtains a stable iPP (imaging photo-plethysmography) signal by using a face diagnosis instrument device, and obtains experience parameters required by calculating oxyhemoglobin saturation by filtering an RB channel (red wavelength and blue wavelength) of the iPP signal.
Description
Technical Field
The invention relates to the field of physiological signal detection, in particular to a non-contact oxyhemoglobin saturation detection method.
Background
Cardiovascular disease has been a major cause of human death due to its high morbidity and various complications. The physiological parameter of blood oxygen saturation is the percentage of the volume of oxygenated hemoglobin to the volume of all hemoglobin, which reflects an important indicator of cardiovascular health, related to the cardiovascular condition of the cellular metabolism of human tissue.
The existing detection of blood oxygen saturation is generally divided into invasive and non-invasive techniques: 1. the traditional invasive technology is usually completed by adopting a blood oxygen analyzer, the blood oxygen analyzer detects the oxygen saturation in blood by the electrochemical principle, and the detection of the oxygen saturation is obtained by collecting the blood of a patient, so that the method has the advantages of quick measurement and accurate result; 2. the non-invasive detection technology can be divided into a reflection type and a projection type according to the positions of the photoelectric receiving device and the light source, and the two modes are distinguished mainly by judging whether the emergent light and the photoelectric receiving equipment are positioned on the same side. The existing non-invasive equipment is more common to adopt a projection type fingerstall type photoelectric acquisition device, an emission light source is arranged at the upper end in the fingerstall, a receiving device is arranged at the lower end, and the degree of blood oxygen saturation can be calculated through the absorption condition of hemoglobin at the finger part on the emission light source.
The existing detection method has the following problems:
the blood oxygen saturation detection is carried out by using the traditional invasive blood oxygen analyzer in a way of collecting blood by using a human body, blood is required to be collected every time, pain is brought to a patient, the preservation of collected blood also needs strict conditions, the operation process is complex, the requirement on medical conditions is high, the medical conditions cannot be continuously detected, and daily disease early warning cannot be carried out at home. The current predominant fingerstall detection method in the non-invasive technology has limitations, and such devices must be tightly attached to the skin and be shielded from light to obtain a physiological signal with good signal-to-noise ratio in order to obtain a better measurement result. The finger can not be used when the skin is not allowed to be directly contacted due to damage of the finger, discomfort is caused by overlarge sensitivity of the finger, and inaccuracy is caused by too little or too much blood microcirculation of the finger due to influence of the environment. And the finger cot type equipment needing to be attached to the skin is easily influenced by the motion artifact, and the motion artifact is more difficult to remove from the algorithm perspective by the single-point measurement mode.
Disclosure of Invention
In view of the above defects in the prior art, the technical problem to be solved by the present invention is to solve the problems that the existing non-invasive device has a strict acquisition environment, needs to be attached to the skin for a long time to increase discomfort, and has a limitation in applicability due to difficulty in reducing motion artifacts caused by single-point detection of physiological signals. The invention provides a non-contact oxyhemoglobin saturation detection method, which uses a face diagnosis instrument device, can effectively solve the problem of unstable detection environment, and the face diagnosis instrument device adopts a surrounding stable environment, so that objective and small-interference iPG (imaging photoplethysmography) signals can be conveniently obtained; the iPG technology can meet the requirement of multi-point blood volume change detection on human tissues, reduce the influence of artifacts on physiological signal extraction, and avoid discomfort caused by blood sampling or long-time skin attachment in a non-contact mode; according to the experiment provided by the invention, the RB channel (red wavelength and blue wavelength) filtering is carried out on the extracted iPG signal, so that the empirical parameters required for calculating the blood oxygen saturation are obtained, and finally, the real-time blood oxygen saturation value can be obtained.
In order to achieve the above object, the present invention provides a method for detecting blood oxygen saturation without contact, comprising the steps of:
acquiring an initial face middle iPG signal by a face diagnosis instrument;
processing the initial middle iPG signal to obtain an empirical parameter required for calculating the blood oxygen saturation, and obtaining the ratio of the light intensity projection change of the dual-wavelength light source in the blood tissue;
and obtaining a blood oxygen saturation value according to the empirical parameters.
Further, an initial midface iPPG signal is acquired by a face diagnosis instrument, and the method specifically comprises the following steps:
setting a surface diagnosis instrument to use a white light spectrum as an irradiation light source;
and acquiring continuous images of the middle area of the face of the person to obtain a blood perfusion signal.
Further, processing the initial central plane iPPG signal specifically includes:
and obtaining a blood perfusion signal according to the facial diagnosis instrument, obtaining an iPG signal, carrying out RGB three-channel extraction on the iPG signal, and reserving the iPG signal of a red light channel and a blue light channel.
Further, filtering the iPG signals of the reserved red light channel and the reserved blue light channel within the range of 0.7 to 4 hz; and processing the iPG signal by using a moving window with a repetition window of 10s to obtain experimental parameters.
Further, according to empirical parameters, the ratio of the light intensity projection change of the dual-wavelength light source in the blood tissue is obtained, so that the linear relation between the ratio of the light intensity projection change of the dual-wavelength light source in the blood tissue and the blood oxygen content is obtained, and finally the blood oxygen saturation is obtained.
Technical effects
The face diagnosis instrument used in the invention is provided with a multispectral light source, an interference-free environment, a high-resolution imaging system and a human-computer interaction interface, the equipment can use a face automatic segmentation algorithm, can overcome certain interference and intelligently identify a positioning area required by a human face, combines a light tissue effect and a hemodynamics principle, obtains a continuous image of the middle part of the face under the shooting of a high-resolution camera, performs image processing on a selected part in the continuous image, obtains the image pixel change of the selected part, and extracts a signal change curve of RGB (red, green and blue) three channels from the pixel change curve in the shooting time to obtain an initial face iPG (imaging photoplethysmography) signal.
The light source system is designed to be a 5500K white light environment, the light source is reflected by the inner wall material coated with high light reflection rate in the facial diagnosis instrument, and the illumination uniformity rate of over 95% is kept in a facial irradiation area through testing, so that the stability of the light source environment is ensured, an interference-free image acquisition environment is formed, and the high sensitivity and low noise of tongue and face image acquisition are ensured; the device designs light sources with different wavelengths, adjusts an imaging system to achieve optimal parameters, completes a fluctuation signal extraction algorithm of the iPG facial space blood volume based on multi-step frequency domain constraint, and obtains blood dynamic and chromatographic distribution information of different depths under facial skin.
The dual-light source wavelength and stable signal acquisition environment required by the invention can be met by the facial diagnosis instrument, and the required face middle iPG signal can be selected as the blood oxygen saturation calculation basis through the complete face iPG signal acquired by the facial diagnosis instrument.
The conception, the specific structure and the technical effects of the present invention will be further described with reference to the accompanying drawings to fully understand the objects, the features and the effects of the present invention.
Drawings
FIG. 1 is a flow chart of a method for contactless oximetry detection in accordance with a preferred embodiment of the present invention;
FIG. 2 is a schematic diagram of a face-center RGB three-channel iPG signal collected by the non-contact blood oxygen saturation detection method according to a preferred embodiment of the present invention;
FIG. 3 is a schematic diagram of the MATLAB fit determination of empirical parameters for a method of non-contact oximetry in accordance with a preferred embodiment of the present invention;
FIG. 4 is a graph illustrating a comparison between a non-contact blood oxygen estimation and a conventional blood oxygen estimation in a non-contact blood oxygen saturation detection method according to a preferred embodiment of the present invention;
FIG. 5 is a schematic diagram of a Bland-Altman method for non-contact blood oxygen saturation detection to measure the difference between two devices according to a preferred embodiment of the present invention.
Detailed Description
In order to make the technical problems, technical solutions and advantageous effects to be solved by the present invention more clearly apparent, the present invention is further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
In the following description, for purposes of explanation and not limitation, specific details are set forth, such as particular internal procedures, techniques, etc. in order to provide a thorough understanding of the embodiments of the invention. It will be apparent, however, to one skilled in the art that the present invention may be practiced in other embodiments that depart from these specific details. In other instances, detailed descriptions of well-known systems, devices, circuits, and methods are omitted so as not to obscure the description of the present invention with unnecessary detail.
The invention mainly relates to a method for detecting the blood oxygen saturation degree in a non-contact mode. By using a face diagnosis instrument device, a stable iPG (imaging photoplethysmography) signal is obtained, RB (red wavelength and blue wavelength) filtering is carried out on the extracted face iPG signal, an empirical parameter required by calculating the blood oxygen saturation can be obtained through a calculation formula of the blood oxygen content, and finally the method for detecting the blood oxygen content in a non-contact mode is realized.
1) Principle for calculating blood oxygen content
The blood oxygen content is the volume ratio of the oxygenated hemoglobin to the oxygenated hemoglobin plus the hemoglobin, and the iPG waveform signal under the white light environment can be obtained firstly through the facial blood perfusion signal collected by the facial diagnosis instrument, and the iPG signal of the red light channel and the blue light channel (namely the RB channel) is reserved as the data required for measuring the blood oxygen content by extracting the RGB three channels of the waveform signal.
The RB channel iPG signal extracted by the RGB channel reflects the blood perfusion condition of tiny blood vessels on the face of a human body, and the light intensity transmission change of red light and blue light in the facial tissue of the human body can be obtained, so that the relationship between the blood oxygen content and the light intensity projection change of light sources with different wavelengths in the blood tissue can be obtained:
wherein, SpO2Which represents the oxygen saturation level of blood,
representing the ratio of the intensity projection changes of the red light source and the blue light source in blood tissues,
in (1)
An alternating current component representing the change of red light in blood tissue,
is indicated by redThe direct current component of light change in blood tissue, wherein the alternating current component AC refers to the change part of the light absorption amount caused by the change of blood volume (mainly blood volume and hemoglobin as a component) caused by heart pulsation, and the direct current component DC refers to the direct current part formed by the light absorption amount of substances with unchanged light absorption amount, such as human subcutaneous tissue, bones and the like; in the same way, the method for preparing the composite material,
in (1)
An alternating current component representing the change of blue light in blood tissue,
representing the direct current component of the red light changing in the blood tissue. Finally, a and B are empirical parameters, which indicate that specific values can only be obtained by experiment or statistics, in the present invention, empirical parameters a and B are obtained by calibration experiments.
The ratio of the light intensity projection change in the blood tissue of the dual-wavelength light source can be calculated
The linear relation formula of the blood oxygen content and the blood oxygen content can be obtained: a x R + B, wherein
Empirical parameters A and B can be obtained in a calibration experiment, so that the predicted value of the blood oxygen content is finally calculated.
2) Detection process
The detection process mainly comprises a calibration experiment. In the detection process, an operator firstly obtains the blood oxygen content of a subject by using a traditional oximeter as a reference value, in a calibration experiment, the subject needs to hold a breath for 20 seconds, the ratio R of the light intensity projection change of the dual-wavelength light source in blood tissue is acquired, empirical parameters A and B are obtained according to the linear relation between R and the reference value of the blood oxygen content, and the specific process is shown below.
The detection method comprises the following specific steps and contents:
(a) facial blood perfusion collection
The testee sits in front of the face diagnosis instrument, the chin is placed on a support pad of the face diagnosis instrument, and a facial blood flow perfusion signal, namely an iPG waveform, is acquired. The detection in this embodiment requires calibration experiments with the subject in breath-hold status. In the calibration experiment of breath holding state, the traditional oximeter is used for measuring the blood oxygen saturation as an empirical parameter for subsequently fitting the blood oxygen saturation;
(b) iPG waveform signal processing
And extracting the acquired iPG waveform through an RGB channel to obtain an iPG initial waveform of the RB channel. After the waveform is filtered within the range of 0.7-4 Hz, the iPG signal is processed by using a moving window which is 10s and is a repeated window, and then the parameter R required in the formula test for calculating the blood oxygen content can be obtained, namely, the alternating current component of a red light channel is obtained
DC component of red light channel
AC component of blue channel
DC component of blue channel
Further calculate and know
(c) Empirical parameters required for calculating blood oxygen saturation
From the experimental data obtained in the operation (b), the parameter R in the calculation formula of the blood oxygen saturation can be obtained. And (3) extracting the values of 12 parameters R of different time periods according to the step (b) in a calibration experiment for each subject, and obtaining the relation between the values corresponding to the blood oxygen saturation value detected by the traditional oximeter. In the calibration experiment, 10 subjects are detected, and 12R values are obtained for each subject, so that the corresponding relation between 120R values and the reference value of the blood oxygen saturation can be obtained. Linear fitting of a linear function is carried out on the relation between the parameter R value and the blood oxygen saturation through the least square method curve fitting principle, so that the linear fitting condition shown in figure 3 can be obtained, the straight line of the linear function in the figure is a fitted linear equation, and empirical parameters A and B, namely parameters required for subsequent non-contact blood oxygen saturation measurement, can be obtained by calculating a fitting result.
3) Prediction result evaluation
The parameters required for calculating the blood oxygen saturation obtained in the calibration experiment can be used for predicting the blood oxygen saturation by using a diagnostic instrument, and the specific prediction steps and conditions are as follows:
(a) prediction step
The examinee firstly acquires facial blood perfusion data, namely iPG data, and in the detection process, the examinee only needs to keep a free breathing state, meanwhile, a traditional oximeter is used for comparing the blood oxygen saturation with a face diagnosis instrument, and at the stage, the operation flow of the face diagnosis instrument needs 30 seconds.
The three-channel iPG signal collected by the diagnosis instrument is subjected to signal processing operation which is the same as that of a calibration experiment, and the processed iPG data is subjected to parameter R calculation, namely
The procedure is the same as for the calibration experiment. According to empirical parameters A and B obtained in a calibration experiment, through a formula 1: SpO2The blood oxygen content was calculated as axr + B.
(b) Comparison of predicted results
Comparing the blood oxygen saturation predicted by the face diagnosis instrument with the blood oxygen saturation reference value detected by the traditional oximeter to obtain the comparison result shown in figure 4, wherein the difference of the detection results of the two instruments is not more than 3%; the difference of the two devices is measured by using a Bland-Altman method, the difference of the measurement results of the same individual is used as an ordinate, the average value of the two measurement results is used as an abscissa, and all the data of the testees are within a 95% confidence interval, so that the two devices have good consistency, and the non-contact blood oxygen estimation method using the facial diagnosis instrument device has application prospect.
Compared with the traditional contact type blood oxygen estimation method, the method has the beneficial effects that:
the oxygen saturation of blood can be detected without contact, and feasibility is provided for replacing the traditional oximeter;
the used detection environment comprises an RGB camera with a wide enough spectral range, the detection environment light source is stable, and the interference of the external environment can be eliminated to the maximum extent.
The foregoing detailed description of the preferred embodiments of the invention has been presented. It should be understood that numerous modifications and variations could be devised by those skilled in the art in light of the present teachings without departing from the inventive concepts. Therefore, the technical solutions available to those skilled in the art through logic analysis, reasoning and limited experiments based on the prior art according to the concept of the present invention should be within the scope of protection defined by the claims.
Claims (9)
1. A non-contact blood oxygen saturation detection method is characterized by comprising the following steps:
acquiring an initial face middle iPG signal by a face diagnosis instrument;
processing the initial mid-plane iPG signal to obtain an empirical parameter required for calculating the blood oxygen saturation, and obtaining the ratio of the light intensity projection change of the dual-wavelength light source in blood tissues;
and obtaining a blood oxygen saturation value according to the empirical parameters.
2. The method for detecting the degree of oxygen saturation in blood without contact as claimed in claim 1, wherein the acquisition of the initial mid-face iPPG signal by the facial diagnosis instrument specifically comprises:
setting a surface diagnosis instrument to use a white light spectrum as an irradiation light source;
and acquiring continuous images of the middle area of the face of the person to obtain a blood perfusion signal.
3. The method for detecting the degree of blood oxygen saturation without contact as claimed in claim 2, wherein the processing of the initial mid-plane iPPG signal specifically comprises:
and obtaining a blood perfusion signal according to the facial diagnosis instrument, obtaining an iPG signal, carrying out RGB three-channel extraction on the iPG signal, and reserving the iPG signal of a red light channel and a blue light channel.
4. The method for detecting the oxygen saturation level of blood without contact as recited in claim 3, wherein the iPG signal of the reserved red light channel and the reserved blue light channel is filtered within the range of 0.7 to 4 hz; and processing the iPG signal by using a moving window with a repetition window of 10s to obtain experimental parameters.
5. The method as claimed in claim 3, wherein the ratio of the light intensity projection variation of the dual-wavelength light source in the blood tissue is obtained according to the empirical parameters, so as to obtain the linear relationship between the ratio of the light intensity projection variation of the dual-wavelength light source in the blood tissue and the blood oxygen content, and finally obtain the blood oxygen saturation.
6. The method of claim 3, wherein the diagnostic device is configured as a semi-packaged device, further comprising a light source, a reflector, an imaging system and an image processing device; when the face diagnosis instrument is used, a face is attached to the face diagnosis instrument to form an interference-free environment, the light source is uniformly irradiated on the face through the reflector, the imaging system obtains continuous images in the middle of the face, and the continuous images are transmitted to the image processing device for image processing.
7. The method of claim 6, wherein the imaging system is configured as a high resolution camera.
8. The method as claimed in claim 6, wherein the image processing device receives the continuous image of the middle part of the face transmitted by the imaging system, processes the continuous image to obtain the variation curve of the image pixels, and extracts the signal variation curve of the RGB three channels from the variation curve of the image pixels.
9. The method as claimed in claim 6, wherein the light source is set to 5500K white light, and the reflector reflects the light source to uniformly irradiate the middle part of the face.
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