CN110823369B - Reflection-type photoelectric volume wave analog calibration method and device - Google Patents
Reflection-type photoelectric volume wave analog calibration method and device Download PDFInfo
- Publication number
- CN110823369B CN110823369B CN201910996221.1A CN201910996221A CN110823369B CN 110823369 B CN110823369 B CN 110823369B CN 201910996221 A CN201910996221 A CN 201910996221A CN 110823369 B CN110823369 B CN 110823369B
- Authority
- CN
- China
- Prior art keywords
- infrared light
- light
- volume wave
- photoelectric volume
- red light
- 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
- 238000000034 method Methods 0.000 title claims abstract description 30
- 238000012806 monitoring device Methods 0.000 claims abstract description 73
- 238000001514 detection method Methods 0.000 claims abstract description 66
- 230000029058 respiratory gaseous exchange Effects 0.000 claims abstract description 48
- 238000004088 simulation Methods 0.000 claims abstract description 48
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 claims abstract description 26
- 239000008280 blood Substances 0.000 claims abstract description 26
- 210000004369 blood Anatomy 0.000 claims abstract description 26
- 229910052760 oxygen Inorganic materials 0.000 claims abstract description 26
- 239000001301 oxygen Substances 0.000 claims abstract description 26
- 230000003287 optical effect Effects 0.000 claims abstract description 24
- 230000000241 respiratory effect Effects 0.000 claims description 43
- 230000005284 excitation Effects 0.000 claims description 39
- 230000000747 cardiac effect Effects 0.000 claims description 27
- 230000015572 biosynthetic process Effects 0.000 claims description 17
- 238000003786 synthesis reaction Methods 0.000 claims description 17
- 230000002194 synthesizing effect Effects 0.000 claims description 13
- 230000006698 induction Effects 0.000 claims description 9
- 108010064719 Oxyhemoglobins Proteins 0.000 claims description 8
- 238000001914 filtration Methods 0.000 claims description 3
- 230000003434 inspiratory effect Effects 0.000 claims description 3
- 238000012886 linear function Methods 0.000 claims description 3
- 238000013186 photoplethysmography Methods 0.000 claims description 3
- 230000009466 transformation Effects 0.000 claims description 3
- 238000009434 installation Methods 0.000 claims description 2
- 238000000926 separation method Methods 0.000 abstract description 3
- 230000002238 attenuated effect Effects 0.000 description 13
- 238000010586 diagram Methods 0.000 description 9
- 238000011160 research Methods 0.000 description 4
- 238000004519 manufacturing process Methods 0.000 description 3
- 230000000712 assembly Effects 0.000 description 2
- 238000000429 assembly Methods 0.000 description 2
- 230000005540 biological transmission Effects 0.000 description 2
- 238000011088 calibration curve Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000001575 pathological effect Effects 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 238000003759 clinical diagnosis Methods 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 238000012544 monitoring process Methods 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
Images
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J1/00—Photometry, e.g. photographic exposure meter
- G01J1/42—Photometry, e.g. photographic exposure meter using electric radiation detectors
- G01J1/44—Electric circuits
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J3/00—Spectrometry; Spectrophotometry; Monochromators; Measuring colours
- G01J3/28—Investigating the spectrum
- G01J3/42—Absorption spectrometry; Double beam spectrometry; Flicker spectrometry; Reflection spectrometry
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J1/00—Photometry, e.g. photographic exposure meter
- G01J1/42—Photometry, e.g. photographic exposure meter using electric radiation detectors
- G01J1/44—Electric circuits
- G01J2001/4446—Type of detector
- G01J2001/446—Photodiode
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J3/00—Spectrometry; Spectrophotometry; Monochromators; Measuring colours
- G01J3/28—Investigating the spectrum
- G01J3/42—Absorption spectrometry; Double beam spectrometry; Flicker spectrometry; Reflection spectrometry
- G01J2003/425—Reflectance
Abstract
The reflective photoelectric accumulated wave analog scaling method and the device have the advantages that the analog synthetic parameters are dynamically adjustable, the standard analog photoelectric accumulated waves containing multi-parameter physiological information such as pulse rate, respiration, pulse rate variability, blood oxygen saturation and the like are used as detection envelopes, and the problem of scaling the pulse rate, the respiration, the pulse rate variability and the blood oxygen saturation is solved; the problem of infrared light and red light identification is solved by adopting a pair of optical filters to perform optical path separation on the infrared light and the red light emitted by the reflective photoelectric volume wave monitoring device; the infrared light LED and the red light LED of the calibration device are closely arranged at the same position as the infrared light PD and the red light PD, so that the problem of alignment of the LED and the PD between the calibration device and the monitoring device is solved; the problem of different light emitting frequencies and driving time sequences of different monitoring devices is solved according to the pulse amplitude of red light and infrared light emitted by a light emitting device in the pulse waveform modulation calibration device driven by the red light and infrared light of the reflective photoelectric volume wave monitoring device to the standard simulation reflective photoelectric volume wave signal envelope.
Description
Technical Field
The invention belongs to the field of biomedical engineering, and relates to a reflective photoelectric volume wave simulation calibration method and device.
Background
The photoplethysmography contains abundant physiological signals including pulse rate, respiration, pulse rate variability, blood oxygen saturation and the like, is an important detection object of conventional medical monitoring, and the accuracy of the detection result of related physiological information directly relates to clinical diagnosis and treatment effects. Therefore, the research on the calibration method and apparatus of photoelectric volume wave has been continued.
The literature, "research on calibration curve of pulse oximeter", and "development of calibration device of pulse oximeter" disclose the main measurement indexes of the transmission type photoelectric volume wave, the calibration curve of pulse blood oxygen, and the calibration device, and solve the problems of the calibration method and device of the transmission type photoelectric volume wave. But the reflective type photoelectric volume wave monitoring device with wider application range and wider use part is still not effectively solved.
Referring to fig. 2, in the conventional reflective type photoelectric volume wave monitoring device in the prior art, a pair of infrared light emitting diode LED1 and red light emitting diode LED2 alternately emit infrared light and red light, respectively, and the infrared light and the red light are scattered by different tissue layers and then respectively incident on a photodiode PD. The monitoring device respectively detects the fluctuation information of the light intensity of the infrared light and the red light through the photodiode PD, and can obtain abundant physiological signals including pulse rate, respiration, pulse rate variability, blood oxygen saturation and the like in photoelectric volume waves.
The existing reflective type photoelectric volume wave simulation calibration device, as shown in fig. 3, includes a photodiode PDA and a pair of infrared LED LEDA and red LED LEDB, which are installed on the same plane parallel to the reflective type photoelectric volume wave monitoring device, wherein the photodiode PDA needs to be precisely aligned with the positions of the LEDs 1 and 2 of the monitoring device; the light emitting diodes LEDA, LEDB need to be precisely aligned with the position of the photodiode PD of the monitoring device; so that as much light as possible is emitted by the light emitting diode into the photodiode. Meanwhile, the PDA needs to detect the received light intensity information respectively strictly according to the light emitting frequency and the excitation timing sequence of the alternate lighting of the LED1 and the LED2 so as to distinguish the light intensity of the emitted infrared light and the red light, and after the attenuation coefficient is simply calculated, the attenuated infrared light and red light are emitted by the LEDA and the LEDB to simulate the absorption of the infrared light and the red light by the tissue. Further realize the calibration of pulse rate and blood oxygen saturation. Scaling of respiratory and pulse rate (heart rate) variability is currently not possible, subject to the limitations of scaling methods. Meanwhile, the positions of the light emitting diode and the photodiode in the reflective type photoelectric capacitance accumulated wave monitoring devices with different models produced by various manufacturers are different, the distances are different, the shapes are different, and the sizes are different, so that the LED and the PD between the calibration device and the monitoring device are difficult to align. The light emitting frequency and the driving time sequence of the light emitting diodes are different, so that the light paths of infrared light and red light are difficult to separate and the identification is difficult. Finally, the reflective type photoelectric volume wave analog calibration device which is difficult to produce and manufacture and has uniform specification and is compatible with products of various manufacturers can only be customized according to the specification and the requirement of different monitoring devices. This situation has greatly limited the application of reflective type optical capacitance integrated wave monitoring devices, especially reflective oximeters.
Disclosure of Invention
Aiming at the problems in the prior art, the invention provides a reflective type photoelectric volume wave analog calibration method which is easy to realize and is compatible with reflective type photoelectric volume wave monitoring devices of various manufacturers and can simultaneously calibrate pulse rate, respiration, pulse rate variability and blood oxygen saturation, and a calibration device which has a simple structure and is easy to operate.
The invention is realized by the following technical scheme:
a reflective photoelectric volume wave simulation calibration method comprises the following steps:
step 1, synthesizing a standard simulation reflection type photoelectric volume wave; through parameter setting, simulating a standard simulation reflection type photoelectric volume wave of multi-parameter physiological information with dynamically adjustable synthesis parameters as a detection envelope;
step 2, filtering red light and infrared light pulses emitted by the reflective photoelectric volume wave monitoring device as incident light to obtain detection light pulses;
step 3, according to the detection of the detection light pulse, red light and infrared light excitation pulses emitted by the reflective photoelectric volume wave monitoring device are obtained;
step 4, according to the red light and infrared light excitation pulse, modulating with the detection envelope obtained in the step 1; at the time corresponding to the red light excitation pulse and the infrared light excitation pulse, modulating the amplitude of the red light excitation pulse and the infrared light excitation pulse to be equal to the amplitude of the detection envelope to be used as a driving light pulse for calibrating the red light excitation pulse and the infrared light excitation pulse;
and 5, generating red light and infrared light with the same intensity as the standard simulation photoelectric volume wave detection envelope amplitude according to the driving light pulse of the calibration red light and the infrared light, and using the red light and the infrared light as emergent light for the reflective photoelectric volume wave monitoring device to detect and calibrate.
Preferably, in step 1, the standard simulated reflection type photoelectric volume wave includes a red light signal and an infrared light signal.
Preferably, in step 1, the multi-parameter physiological information includes pulse rate, respiration, pulse rate variability and blood oxygen saturation.
Further, the pulse rate is the reciprocal of the waveform period of the single cardiac cycle photoelectric volume wave infrared light;
when pulse rate parameters are synthesized, the actual single cardiac cycle photoelectric volume wave infrared light waveform is fitted through superposition of three Gaussian signals, and is described by a formula (1):
wherein t is the time independent variable of the function p (t), p (t) is the single cardiac cycle photoelectric volume wave infrared light waveform obtained by superposing three Gaussian signals, ViIs the amplitude of the ith Gaussian function, TiIs the central position of the ith Gaussian function, UiThe width of the ith Gaussian function is shown, i is the serial number of the Gaussian function, and i is a positive integer between 1 and 3;
extending the single cardiac cycle photoelectric volume wave infrared light waveform to a plurality of cardiac cycles and at least extending to a complete respiratory cycle to form the single respiratory cycle fixed parameter photoelectric volume wave infrared light waveform.
Still further, the method for synthesizing the breathing parameters comprises the following steps,
first, the actual single respiratory cycle respiratory waveform is fitted by superposition of two half-sinusoidal signals, described by equation (2):
wherein T is the time independent variable of a function r (T), r (T) is a single respiratory cycle respiratory waveform obtained by superposing two half-sine signals, TupThe inspiratory time for a breath, also called the rise time, TdnThe expiration time of a breath, also called the fall time.
Secondly, according to the set proportional coefficient and phase difference of the respiratory induction amplitude change, the respiratory induction frequency change and the respiratory induction intensity change, the simulated single respiratory cycle respiration modulation parameter photoelectric product infrared optical waveform synthesized by the simulated single respiratory cycle fixed parameter photoelectric product infrared optical waveform and the simulated single respiratory cycle respiratory waveform is described by a formula (3):
y(t)＝kar(t+pa)p((1+kfr(t+pf))t)+kir(t+pi) (3)
wherein t is the time independent variable of the function y (t), y (t) is a single-breath-period photoelectric volume wave infrared light waveform obtained by superposing three Gaussian signals and two half-sine signals, and k isa、paProportional coefficients and phase differences, respectively, of respiration-induced amplitude variations (RIAV); k is a radical off、pfProportional coefficient and phase difference of Respiration Induced Frequency Variation (RIFV), respectively; k is a radical ofi、piRespectively, the proportionality coefficient and the phase difference of the Respiration Induced Intensity Variation (RIIV).
Furthermore, when synthesizing the pulse rate variability parameters,
extending the synthesized simulation single-respiration-cycle respiration modulation parameter photoelectric volume wave infrared light waveform to a multiple respiration cycle; synthesizing pulse rate variability information in the multi-respiratory cycle photoelectric volume wave infrared light waveform by adjusting the PP interval of each cardiac cycle in the obtained multi-respiratory cycle to obtain a multi-parameter dynamically-adjusted photoelectric volume wave infrared light waveform IR (t) containing pulse rate variability;
the synthesis of the pulse rate variability parameter is described by equation (4):
PPi＝ξ1(1+ξ2×r(t)) (4)
wherein, PPiDuration of the ith PP interval; xi1Random numbers in a Gaussian distribution with a mean equal to the expectation of all PP intervals; xi2Random numbers which are more than 0 and are distributed in a semi-Gaussian way; t is the sum of the durations of the first i-1 PP intervals.
When synthesizing oxyhemoglobin saturation parameters, synthesizing oxyhemoglobin saturation information in the multi-parameter dynamically-adjusted photoplethysmographic red light waveform by performing linear function transformation on the multi-parameter dynamically-adjusted photoplethysmographic infrared light waveform IR (t) to obtain a multi-parameter dynamically-adjusted photoplethysmographic red light waveform Red (t) containing oxyhemoglobin saturation information;
the synthesis of the blood oxygen saturation information is described by equation (5):
where t is the time argument of the functions Red (t), IR (t), RedAC(t)、IRAC(t) the AC components of red waveform Red (t) and infrared waveform IR (t) in the photoplethysmography respectively; redDC、IRDCThe amplitudes of the direct current components of the red light waveform Red (t) and the infrared light waveform IR (t) are constant in a cardiac cycle; alpha and beta are respectively empirical values and are determined by calibration; spO2Is also constant over one cardiac cycle.
A reflection-type photoelectric volume wave analog calibration device comprises a processor and calibration transceiving units of red light and infrared light which are adjacently arranged on the same installation surface, wherein each of the two calibration transceiving units comprises a photosensitive detection part and a light emitting part; a precise optical filter for red light and infrared light is correspondingly arranged above the photosensitive detection component for red light and infrared light;
the red light and infrared light photosensitive detection part is used for detecting through the corresponding precision optical filter and emitting red light excitation pulses and infrared light excitation pulses by the reflective photoelectric volume wave monitoring device;
the processor comprises a parameter setting unit and two signal generators; the input end of the processor is respectively connected with the photosensitive detection parts of red light and infrared light, and the output end of the processor is respectively connected with the luminous parts of red light and infrared light;
the parameter setting unit synthesizes a standard simulation reflection-type photoelectric volume wave as a detection envelope through the step 1 in the method;
the two signal generators respectively obtain the driving pulses of the calibration red light and the infrared light through the steps 3-4 in the method;
the light emitting components of the red light and the infrared light generate the red light and the infrared light with the same intensity as the standard simulation photoelectric volume wave detection envelope amplitude according to the driving pulse of the calibration red light and the infrared light, and the red light and the infrared light are used for the detection and calibration of the reflection type photoelectric volume wave monitoring device.
Preferably, the precision optical filter of the photosensitive detection component corresponding to the red light and the infrared light adopts a red light filter with the bandwidth of 1nm and the central wavelength of 660nm and an infrared light filter with the central wavelength of 940 nm.
Preferably, the photosensitive detection part is a photodiode, and the light emitting part is a light emitting diode.
Compared with the prior art, the invention has the following beneficial technical effects:
the invention solves the problem of calibrating pulse rate, respiration, pulse rate variability and oxyhemoglobin saturation at the same time by using the standard simulation photoelectric volume wave of multi-parameter physiological information such as pulse rate, respiration, pulse rate variability and oxyhemoglobin saturation as a detection envelope through dynamically adjustable simulation synthesis parameters; the problem of infrared light and red light identification is solved by adopting a pair of optical filters to perform optical path separation on the infrared light and the red light emitted by the reflective photoelectric volume wave monitoring device; the infrared light LED and the red light LED of the calibration device are closely arranged at the same position as the infrared light PD and the red light PD, so that the problem of alignment of the LED and the PD between the calibration device and the monitoring device is solved; according to the reflective photoelectric volume wave monitoring device, the pulse amplitudes of red light and infrared light emitted by red light and infrared light emitting devices in the pulse waveform modulation calibration device are simulated to reach the standard according to the own red light and infrared light driving pulse waveform modulation calibration device, so that the problem that different monitoring devices are different in light emitting frequency and driving time sequence is solved; finally, a simple, convenient and feasible reflective photoelectric volume wave analog calibration method and device are realized, and the reflective photoelectric volume wave monitoring device is used for carrying out calibration evaluation on the detection result of the physiological signal.
Drawings
FIG. 1 is a schematic flow chart of the steps of the reflective type photoelectric volume wave simulation calibration method of the present invention.
Fig. 2 is a schematic diagram of a conventional reflective photoelectric volume wave monitoring device in the prior art.
Fig. 3 is a schematic diagram illustrating a reflective type optical capacitance accumulated wave simulation calibration apparatus in the prior art.
FIG. 4 is a schematic diagram of the reflective photoelectric volume wave analog calibration device of the present invention.
FIG. 5 is a waveform diagram of the reflective type photoelectric volume wave simulation calibration method of the present invention.
FIG. 6 is a schematic structural diagram of a reflective photoelectric volume wave analog calibration device according to the present invention.
Detailed Description
The present invention will now be described in further detail with reference to specific examples, which are intended to be illustrative, but not limiting, of the invention.
The invention provides a reflective photoelectric accumulated wave simulation calibration method and device, which solve the problems of difficult production, uniform manufacture and compatibility with reflective photoelectric accumulated wave simulation calibration devices of various manufacturers and products in the prior reflective photoelectric accumulated wave monitoring device due to different positions, different distances, different shapes, different sizes, different light emitting frequencies, different light source driving time sequences and the like between a light source and a detector in the monitoring devices of various manufacturers and models by using a simulation synthesis parameter dynamic adjustable simulation photoelectric accumulated wave technology containing multi-parameter physiological information such as pulse rate, respiration, pulse rate variability, blood oxygen saturation and the like.
As shown in fig. 4, the reflective type photoelectric volume wave analog calibration device of the present invention has two sets of photodiode and led combinations, which are the combination of photodiode PDA and led LEDA, and the combination of photodiode PDB and led LEDB, closely installed at the same position. Wherein, a group of precise optical filters are respectively arranged above each group of photodiodes, an infrared light filter FLTA is correspondingly arranged above the photodiode PDA, and a red light filter FLTB is correspondingly arranged above the photodiode PDB. The center wavelength of the infrared light filter is 940nm, and the center wavelength of the red light filter is 660 nm. In the preferred embodiment, as shown in fig. 4, after the infrared light excitation pulse and the red light excitation pulse emitted by a group of light emitting diodes LED1 and LED2 of the reflective type photoelectric volume wave monitoring device are filtered by the light filter of the calibration device and then detected by the corresponding photodiodes, the infrared light emitted by the monitoring device LED1 is filtered by the FLTA corresponding to the calibration device and detected by the PDA, and then is calculated to drive the LEDA to emit standard infrared light to be emitted to the monitoring device PD for calibration, and after the red light emitted by the monitoring device LED2 is filtered by the FLTB corresponding to the calibration device and detected by the PDB, the red light emitted by the LEDB is calculated to emit standard red light to be emitted to the monitoring device PD for calibration. The excitation light intensity of the monitoring device detected by the calibration device PDA and the PDB is sent to the calibration device processor, the intensity of the excitation light intensity is converted into attenuated light intensity after tissue attenuation according to the setting of the calibration requirement, and then the attenuated light intensity is transmitted to the light emitting diodes LEDA and LEDB of the calibration device to emit attenuated infrared light and attenuated red light which correspond to the attenuated infrared light and the attenuated red light after tissue attenuation. The emitted attenuated infrared light and the attenuated red light impinge on the photodiode PD of the monitoring device and are detected by it as if reflected light scattered by the multilayer tissue were detected. At this moment, the attenuated light intensity after tissue attenuation is a group of standard signals, namely the calibration device sends standard photoelectric volume wave signals to the monitoring device, and the monitoring device detects the standard signals so as to complete the calibration process of the monitoring device.
Because the infrared light, the red light LED, the infrared light and the red light PD of the calibration device have small areas and are closely arranged at the same position, and can be regarded as the same point physically, according to the reversible principle of the light path, the infrared light and the red light which are detected by the photodiode of the monitoring device and are emitted by the point are equivalent to the photoelectric volume wave signal which is reflected back by the point and is attenuated by the tissue, and the position of the LED and the PD of the monitoring device and the position of the PD and the LED of the calibration device are not required to be accurately aligned. Meanwhile, a pair of precise optical filters and a photodiode in the calibration device are introduced, so that the PDA and the PDB respectively detect infrared light and red light emitted by the monitoring device, the problem of identification of the infrared light and the red light is solved, the problem of identification of the light emitting frequency and the driving time sequence of the monitoring device is solved, the calibration device can generate standard light pulses with corresponding light intensity as long as excitation light of the monitoring device is emitted, and the light emitting frequency and the driving time sequence of the monitoring device do not need to be known in advance. The infrared light and the red light pulse amplitude emitted by the infrared light and red light emitting diodes in the calibration device are modulated to the standard simulated reflection type photoelectric capacitance accumulated wave signal envelope, so that the calibration device can generate the reflection type photoelectric capacitance accumulated wave signal in any physiological and pathological states, and the application scene does not need to be customized in advance. Therefore, no matter the manufacturer and the model of the reflective type photoelectric volume wave monitoring device, no matter whether the position, the distance, the shape and the size between the light emitting diode and the photoelectric diode in the monitoring device are different, no matter whether the light emitting frequency and the driving time sequence of the light source are different, and no matter whether the application scenes are different, the calibration method and the device can complete the calibration process of the reflective type photoelectric volume wave monitoring device.
The invention is characterized in that: the simulation synthesis parameters are dynamically adjustable, standard simulation reflection type photoelectric volume waves containing multi-parameter physiological information of pulse rate, respiration, pulse rate variability and blood oxygen saturation are used as detection envelopes, and a pair of optical filters are adopted to perform optical path separation on red light and infrared light emitted by a reflection type photoelectric volume wave monitoring device; according to the self red light and infrared light excitation pulse waveform of the reflective photoelectric volume wave monitoring device, the amplitude of the attenuated red light and the attenuated infrared light pulse emitted by the red light and infrared light luminous devices in the calibration device is modulated to a standard simulated reflective photoelectric volume wave signal envelope and is irradiated to the photosensitive device of the reflective photoelectric volume wave monitoring device, so that a photoelectric volume wave synthesis signal containing standard pulse rate, respiration, pulse rate variability and blood oxygen saturation is generated in the reflective photoelectric volume wave monitoring device, and the simple, convenient and feasible reflective photoelectric volume wave simulation calibration method and device are realized, and the reflective photoelectric volume wave monitoring device can calibrate and evaluate the detection result of the physiological signal.
Referring to fig. 1, the reflective type photoelectric volume wave simulation calibration method of the present invention comprises the following steps:
and step 1, synthesizing a standard photoplethysmographic signal. Through parameter setting, simulation synthesis parameters are dynamically adjustable, and standard simulation reflection type photoelectric volume waves containing multi-parameter physiological information of pulse rate, respiration, pulse rate variability and blood oxygen saturation are used as detection envelopes. For use in step 4.
And 2, filtering. Infrared light and red light pulses emitted by the reflective photoelectric volume wave monitoring device are used as incident light and are filtered by a precision optical filter with the bandwidth of 1nm and the central wavelengths of 940nm and 660nm respectively, and then the infrared light and the red light pulses are sent to corresponding photosensitive detection parts of the calibration device for detection respectively.
And 3, photosensitive detection. And (3) transmitting the filtered detection light pulse obtained in the step (2) to a corresponding photosensitive detection component of the calibration device for detection, and obtaining the red light and infrared light excitation pulse emitted by the reflective photoelectric volume wave monitoring device.
And 4, driving light modulation. Modulating the red light and infrared light excitation pulses emitted by the reflective photoelectric volume wave monitoring device obtained in the step 3 with the standard simulated photoelectric volume wave detection envelope obtained in the step 1; and at the corresponding time of the red light excitation pulse and the infrared light excitation pulse, modulating the amplitude of the red light excitation pulse and the infrared light excitation pulse to be equal to the amplitude of a standard simulation reflection type photoelectric volume wave detection envelope, and taking the amplitude as the red light and infrared light driving light pulse of the calibration device.
And 5, emitting light. And (4) transmitting the red light and infrared light driving light pulses of the calibration device obtained in the step (4) to a light emitting part, generating red light and infrared light with the same intensity as the envelope amplitude of the standard simulation photoelectric volume wave detection at the same time, and using the red light and the infrared light as emergent light for the detection of a reflective photoelectric volume wave monitoring device, wherein the detection of the reflective photoelectric volume wave monitoring device is that the received standard simulation photoelectric volume wave is dynamically adjustable in parameter and contains multi-parameter physiological information of pulse rate, respiration, pulse rate variability and blood oxygen saturation.
Referring to fig. 5, the top diagram shows the synthesis of the standard photoelectric volume signal in step 1, so that the simulation synthesis parameters are dynamically adjustable by parameter setting, and the standard simulation photoelectric volume containing multi-parameter physiological information such as pulse rate, respiration, pulse rate variability and blood oxygen saturation is used as the detection envelope. The lowest diagram shows the red light and infrared light excitation pulse information emitted by the reflective photoelectric volume wave monitoring device obtained by photosensitive detection in the step 3. The middle diagram shows step 4, driving the light modulation. And (3) according to the position information of the red light and infrared light excitation pulse emitted by the reflection-type photoelectric volume wave monitoring device obtained in the step (3), modulating the position information with the standard simulation photoelectric volume wave detection envelope obtained in the step (1), and at the time corresponding to the red light and infrared light excitation pulse of the reflection-type photoelectric volume wave monitoring device, calibrating the amplitude of the red light and infrared light driving pulse of the device to be equal to the amplitude of the standard simulation photoelectric volume wave detection envelope. The driving pulse is respectively sent to the light-emitting component, and red light and infrared light with the same intensity as the standard simulation photoelectric volume wave detection envelope amplitude are generated at the same time for detection of the reflective photoelectric volume wave monitoring device.
In step 1, the standard photoelectric volume signal includes a red light signal and an infrared light signal. Wherein, the wavelength of the red light is 660nm, and the wavelength of the infrared light is 940 nm.
Preferably, in step 1, the standard simulated photoplethysmographic signal containing the multi-parameter physiological information of pulse rate, respiration, pulse rate variability and blood oxygen saturation is described in equations (1) to (5):
the pulse rate is the reciprocal of the waveform period of the single cardiac cycle photoelectric volume wave infrared light. Fitting an actual single-cardiac-cycle photoplethysmographic infrared light waveform by superposition of three gaussian signals is described by equation (1):
wherein t is the time independent variable of the function p (t), p (t) is the single cardiac cycle photoelectric volume wave infrared light waveform obtained by superposing three Gaussian signals, ViIs the amplitude of the ith Gaussian function, TiIs the central position of the ith Gaussian function, UiIs the width of the ith gaussian function. i is the serial number of the Gaussian function, and i is a positive integer between 1 and 3. Extending the single cardiac cycle photoelectric volume wave infrared light waveform to a plurality of cardiac cycles and at least extending to a complete respiratory cycle to form the single respiratory cycle fixed parameter photoelectric volume wave infrared light waveform. Each heart of the infrared light of the photoelectric volume waveThe periodic waveforms are completely the same, and the cardiac cycle, amplitude and intensity are completely consistent.
The superposition fitting of the two half-sinusoidal signals to the actual single respiratory cycle respiratory waveform is described by equation (2):
wherein T is the time independent variable of a function r (T), r (T) is a single respiratory cycle respiratory waveform obtained by superposing two half-sine signals, TupThe inspiratory time for a breath, also called the rise time, TdnThe expiration time of a breath, also called the fall time.
The simulation single breathing cycle fixed parameter photoelectric volume wave infrared light waveform and the simulation single breathing cycle respiration waveform are superposed to fit the actual single breathing cycle respiration modulation parameter photoelectric volume wave infrared light waveform, so that the proportionality coefficients and the phase difference of the respiration-induced amplitude change, the respiration-induced frequency change and the respiration-induced intensity change in the simulation single breathing cycle respiration modulation parameter photoelectric volume wave infrared light waveform are obtained.
According to the obtained proportional coefficient and phase difference which can be set for the respiratory induction amplitude change, the respiratory induction frequency change and the respiratory induction intensity change, the simulated single respiratory cycle respiratory modulation parameter photoelectric volume infrared optical waveform synthesized by the simulated single respiratory cycle fixed parameter photoelectric volume infrared optical waveform and the simulated single respiratory cycle respiratory waveform is described by a formula (3):
y(t)＝kar(t+pa)p((1+kfr(t+pf))t)+kir(t+pi) (3)
wherein t is the time independent variable of the function y (t), y (t) is a single-breath-period photoelectric volume wave infrared light waveform obtained by superposing three Gaussian signals and two half-sine signals, and k isa、paProportional coefficients and phase differences, respectively, of respiration-induced amplitude variations (RIAV); k is a radical off、pfProportional coefficient and phase difference of Respiration Induced Frequency Variation (RIFV), respectively; k is a radical ofi、piAre respectively provided withThe proportionality coefficient and phase difference of Respiration Induced Intensity Variation (RIIV).
Extending the synthesized simulation single-respiration-cycle respiration modulation parameter photoelectric volume wave infrared light waveform to a multiple respiration cycle; synthesizing heart rate (pulse rate) variability information in the multi-respiratory cycle photoelectric volume wave infrared light waveform by adjusting the PP interval of each cardiac cycle in the obtained multi-respiratory cycle to obtain a multi-parameter dynamic adjustment photoelectric volume wave infrared light waveform IR (t) containing the heart rate (pulse rate) variability. Ir (t) is the respiratory cycle extension function of the multi-respiratory cycle respiration modulation parameter photoelectric volume wave infrared light waveform of the synthesized heart rate variability information, i.e. the single-respiratory cycle respiration modulation parameter photoelectric volume wave infrared light waveform y (t).
The synthesis of the pulse rate variability information is described by equation (4):
PPi＝ξ1(1+ξ2×r(t)) (4)
wherein, PPiIs the duration of the ith PP interval, i.e. the duration of the ith pulse rate (heart rate) interval ξ1Is a random number with a Gaussian distribution, the mean of which is equal to the expectation, ξ, of all PP intervals1The value of (a) affects the position of the central point of the poincare graph, ξ1The larger the variance of (A), the straight line PP with the center pointi+1＝PPiThe greater the range of up-shift, so ξ1Mainly affecting the poincare diagram SD1 parameter. Xi2A random number greater than 0 and distributed in a semi-Gaussian distribution, the value of which determines the point (PP)i，PPi+1) With the current central point (xi)1，ξ1) The distance between them, mainly affects the SD2 parameter. t is the sum of the durations of the first i-1 PP intervals.
By performing linear function transformation on the multi-parameter dynamic adjustment photoelectric volume wave infrared light waveform IR (t), the blood oxygen saturation information can be synthesized in the multi-parameter dynamic adjustment photoelectric volume wave red light waveform, and the multi-parameter dynamic adjustment photoelectric volume wave red light waveform Red (t) containing the blood oxygen saturation information is obtained.
The synthesis of the blood oxygen saturation information is described by equation (5):
where t is the time argument of the functions Red (t), IR (t), RedAC(t)、IRAC(t) are the AC components of the red waveform Red (t) and the infrared waveform IR (t) in the photoplethysmogram, respectively. RedDC、IRDCThe amplitudes of the dc components of the red waveform red (t) and the infrared waveform ir (t) are constant within one cardiac cycle. α and β are empirical values, respectively, and are determined by scaling. SpO2Is also constant over one cardiac cycle. Thus, the blood oxygen saturation S is given in one cardiac cyclepO2AC component IR of infrared light waveform of sum-photoplethysmographic waveAC(t), then obtaining the photoelectric volume wave red light waveform alternating current component
RedAC(t) of (d). Given a blood oxygen saturation dynamics function S in a sequence of multiple cardiac cycles of a multi-respiratory cyclepO2(t) and a photo-capacitance accumulated wave infrared light waveform IR (t), so as to obtain a photo-capacitance accumulated wave red light waveform Red (t). That is, in the cardiac cycle sequences of multiple respiratory cycles obtained in this step, the photoplethysmogram IR (t) and Red (t) waveforms include the function S of the dynamic variation of blood oxygen saturationpO2(t)。
The reflective photoelectric volume wave analog calibration device, as shown in fig. 4 and fig. 6, includes the following components:
assemblies 1, 2, filter components. Namely a red light and infrared light filter with the bandwidth of 1nm, the central wavelength of 660nm and 940 nm. The device is used for separating the red light and the infrared light emitted by the reflective photoelectric volume wave monitoring device. Respectively sent to the components 3 and 4, and detected by the corresponding photosensitive detection part of the calibration device.
Assemblies 3, 4, photosensitive detection means. The intensity of the detection light pulse obtained by the components 1 and 2 and filtered is detected to obtain the red light and infrared light excitation pulse information emitted by the reflective photoelectric volume wave monitoring device. Preferably, the photosensitive detection component is a photodiode.
Assembly 5, processor means. The device consists of a parameter setting unit and a pair of photoelectric volume wave signal generators. And completing the synthesis of the standard photoelectric volume wave signal. Through the parameter setting unit, the simulation synthesis parameters are dynamically adjustable, and standard simulation photoelectric volume waves containing multi-parameter physiological information such as pulse rate, respiration, pulse rate variability, blood oxygen saturation and the like are used as detection envelopes. The position information of red light and infrared light excitation pulse emitted by the reflective photoelectric volume wave monitoring device obtained by the two signal generators through the components 3 and 4 is modulated with a standard simulated photoelectric volume wave detection envelope, so that the amplitude of red light and infrared light driving pulse of the calibration device at the time corresponding to the red light and infrared light excitation pulse of the reflective photoelectric volume wave monitoring device is equal to the amplitude of the standard simulated photoelectric volume wave detection envelope at the time.
Components 6, 7, light emitting components. According to the red light and infrared light driving pulse of the calibration device obtained by the component 5, the red light and infrared light with the intensity related to the standard simulation photoelectric volume wave detection envelope amplitude at the moment are generated for the detection of the reflective photoelectric volume wave monitoring device. At the moment, the reflective photoelectric volume wave monitoring device detects and receives the standard simulated photoelectric volume wave which has dynamically adjustable parameters and contains multi-parameter physiological information such as pulse rate, respiration, pulse rate variability, blood oxygen saturation and the like. Preferably, the light emitting part is a light emitting diode.
The reflection-type photoelectric volume wave analog calibration method can realize a reflection-type photoelectric volume wave analog calibration device with simple structure, easy realization, small volume and low power consumption. The device can conveniently generate standard photoelectric volume wave signals for the calibration of a photoelectric volume wave monitoring device, and can also generate various photoelectric volume wave waveforms in physiological or pathological states for scientific research and clinical photoelectric volume wave detection and research.
Claims (8)
1. A reflection-type photoelectric volume wave simulation calibration method is characterized by comprising the following steps:
step 1, synthesizing a standard simulation reflection type photoelectric volume wave; through parameter setting, simulating a standard simulation reflection type photoelectric volume wave of multi-parameter physiological information with dynamically adjustable synthesis parameters as a detection envelope;
step 2, filtering red light and infrared light pulses emitted by the reflective photoelectric volume wave monitoring device as incident light to obtain detection light pulses;
step 3, according to the detection of the detection light pulse, red light and infrared light excitation pulses emitted by the reflective photoelectric volume wave monitoring device are obtained;
step 4, according to the red light and infrared light excitation pulse, modulating with the detection envelope obtained in the step 1; at the time corresponding to the red light excitation pulse and the infrared light excitation pulse, modulating the amplitude of the red light excitation pulse and the infrared light excitation pulse to be equal to the amplitude of the detection envelope to be used as a driving light pulse for calibrating the red light excitation pulse and the infrared light excitation pulse;
step 5, according to the driving light pulse of the calibration red light and the infrared light, the red light and the infrared light with the intensity same as the standard simulation photoelectric volume wave detection envelope amplitude are generated and serve as emergent light for the reflective photoelectric volume wave monitoring device to detect and calibrate;
in step 1, the multi-parameter physiological information comprises pulse rate, respiration, pulse rate variability and blood oxygen saturation;
the pulse rate is the reciprocal of the waveform period of the single cardiac cycle photoelectric volume wave infrared light;
when pulse rate parameters are synthesized, the actual single cardiac cycle photoelectric volume wave infrared light waveform is fitted through superposition of three Gaussian signals, and is described by a formula (1):
wherein t is the time independent variable of the function p (t), p (t) is the single cardiac cycle photoelectric volume wave infrared light waveform obtained by superposing three Gaussian signals, ViIs the amplitude of the ith Gaussian function, TiIs the central position of the ith Gaussian function, UiThe width of the ith Gaussian function is shown, i is the serial number of the Gaussian function, and i is a positive integer between 1 and 3;
extending the single cardiac cycle photoelectric volume wave infrared light waveform to a plurality of cardiac cycles and at least extending to a complete respiratory cycle to form the single respiratory cycle fixed parameter photoelectric volume wave infrared light waveform.
2. The reflective type photoelectric capacitance accumulated wave simulation calibration method according to claim 1, wherein in step 1, the standard simulated reflective type photoelectric capacitance accumulated wave comprises a red light signal and an infrared light signal.
3. A reflective type photoelectric volume wave analog calibration method according to claim 1, wherein the method for synthesizing the breathing parameter comprises the following steps,
first, the actual single respiratory cycle respiratory waveform is fitted by superposition of two half-sinusoidal signals, described by equation (2):
wherein T is the time independent variable of a function r (T), r (T) is a single respiratory cycle respiratory waveform obtained by superposing two half-sine signals, TupThe inspiratory time for a breath, also called the rise time, TdnThe expiration time for a breath, also known as the fall time;
secondly, according to the set proportional coefficient and phase difference of the respiratory induction amplitude change, the respiratory induction frequency change and the respiratory induction intensity change, the simulated single respiratory cycle respiration modulation parameter photoelectric product infrared optical waveform synthesized by the simulated single respiratory cycle fixed parameter photoelectric product infrared optical waveform and the simulated single respiratory cycle respiratory waveform is described by a formula (3):
y(t)＝kar(t+pa)p((1+kfr(t+pf))t)+kir(t+pi) (3)
wherein t is the time independent variable of the function y (t), y (t) is a single-breath-period photoelectric volume wave infrared light waveform obtained by superposing three Gaussian signals and two half-sine signals, and k isa、paAre respectively breathingA scale factor and a phase difference that induce a change in amplitude (RIAV); k is a radical off、pfProportional coefficient and phase difference of Respiration Induced Frequency Variation (RIFV), respectively; k is a radical ofi、piRespectively, the proportionality coefficient and the phase difference of the Respiration Induced Intensity Variation (RIIV).
4. A reflective optical capacitance volume wave analog calibration method according to claim 3, characterized in that, when synthesizing pulse rate variability parameters,
extending the synthesized simulation single-respiration-cycle respiration modulation parameter photoelectric volume wave infrared light waveform to a multiple respiration cycle; synthesizing pulse rate variability information in the multi-respiratory cycle photoelectric volume wave infrared light waveform by adjusting the PP interval of each cardiac cycle in the obtained multi-respiratory cycle to obtain a multi-parameter dynamically-adjusted photoelectric volume wave infrared light waveform IR (t) containing pulse rate variability;
the synthesis of the pulse rate variability parameter is described by equation (4):
PPi＝ξ1(1+ξ2×r(t)) (4)
wherein, PPiDuration of the ith PP interval; xi1Random numbers in a Gaussian distribution with a mean equal to the expectation of all PP intervals; xi2Random numbers which are more than 0 and are distributed in a semi-Gaussian way; t is the sum of the durations of the first i-1 PP intervals.
5. A reflective photoelectric volume wave simulation calibration method according to claim 4, wherein when synthesizing the oxyhemoglobin saturation parameter, the oxyhemoglobin saturation information can be synthesized in the multi-parameter dynamically adjusted photoelectric volume wave red light waveform by performing linear function transformation on the multi-parameter dynamically adjusted photoelectric volume wave infrared light waveform IR (t), so as to obtain a multi-parameter dynamically adjusted photoelectric volume wave red light waveform Red (t) containing oxyhemoglobin saturation information;
the synthesis of the blood oxygen saturation information is described by equation (5):
where t is the time argument of the functions Red (t), IR (t), RedAC(t)、IRAC(t) the AC components of red waveform Red (t) and infrared waveform IR (t) in the photoplethysmography respectively; redDC、IRDCThe amplitudes of the direct current components of the red light waveform Red (t) and the infrared light waveform IR (t) are constant in a cardiac cycle; alpha and beta are respectively empirical values and are determined by calibration; spO2Is also constant over one cardiac cycle.
6. A reflection-type photoelectric volume wave analog calibration device is characterized by comprising a processor and calibration transceiving units of red light and infrared light which are adjacently arranged on the same installation surface, wherein the two calibration transceiving units respectively comprise a photosensitive detection part and a light emitting part; a precise optical filter for red light and infrared light is correspondingly arranged above the photosensitive detection component for red light and infrared light;
the red light and infrared light photosensitive detection part is used for detecting through the corresponding precision optical filter and emitting red light excitation pulses and infrared light excitation pulses by the reflective photoelectric volume wave monitoring device;
the processor comprises a parameter setting unit and two signal generators; the input end of the processor is respectively connected with the photosensitive detection parts of red light and infrared light, and the output end of the processor is respectively connected with the luminous parts of red light and infrared light;
the parameter setting unit synthesizes a standard simulated reflection-type photoelectric volume wave as a detection envelope through the step 1 in the method according to any one of claims 1 to 5;
two signal generators obtaining drive pulses for the scaled red and infrared light, respectively, by steps 3-4 of the method according to any of claims 1-5;
the light emitting components of the red light and the infrared light generate the red light and the infrared light with the same intensity as the standard simulation photoelectric volume wave detection envelope amplitude according to the driving pulse of the calibration red light and the infrared light, and the red light and the infrared light are used for the detection and calibration of the reflection type photoelectric volume wave monitoring device.
7. A reflective photoelectric volume wave analog scaling device according to claim 6, wherein the precision filters of the photosensitive detecting elements corresponding to red light and infrared light use red light with a bandwidth of 1nm and a center wavelength of 660nm and infrared light filters with a center wavelength of 940 nm.
8. A reflective optical capacitance volume wave analog scaling device according to claim 6, wherein the photosensitive detection element is a photodiode and the light emitting element is a light emitting diode.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910996221.1A CN110823369B (en) | 2019-10-18 | 2019-10-18 | Reflection-type photoelectric volume wave analog calibration method and device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910996221.1A CN110823369B (en) | 2019-10-18 | 2019-10-18 | Reflection-type photoelectric volume wave analog calibration method and device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN110823369A CN110823369A (en) | 2020-02-21 |
| CN110823369B true CN110823369B (en) | 2020-11-10 |
Family
ID=69549751
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201910996221.1A Active CN110823369B (en) | 2019-10-18 | 2019-10-18 | Reflection-type photoelectric volume wave analog calibration method and device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN110823369B (en) |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111466922B (en) * | 2020-05-14 | 2023-11-24 | 中科搏锐（北京）科技有限公司 | Self-adaptive blood oxygen signal acquisition probe, device and method based on near infrared blood oxygen detection |
| CN113706984B (en) * | 2021-08-06 | 2022-07-12 | 西安交通大学 | Synchronous analog calibration device and method for blood pressure and reflective photoelectric accumulated wave |
| CN113855013B (en) * | 2021-09-28 | 2022-06-10 | 杭州大牧医疗科技有限公司 | Probe conversion device of blood oxygen simulator |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2007097702A1 (en) * | 2006-02-21 | 2007-08-30 | Lindberg Lars-Goeran | Non-invasive monitoring of blood flow in deep tissue |
| CN103271745A (en) * | 2013-06-07 | 2013-09-04 | 秦皇岛市康泰医学系统有限公司 | Pulse blood oxygen simulation system and implementation method |
| CN104414626A (en) * | 2013-08-23 | 2015-03-18 | 同方健康科技(北京)有限公司 | Electronic magnetic induction blood pressure monitor and method of parameter calibration on same |
| CN107847166A (en) * | 2015-06-30 | 2018-03-27 | 皇家飞利浦有限公司 | Utilize the sensing system and method for multiple PPG sensors |
| EP3395236A1 (en) * | 2017-04-25 | 2018-10-31 | Tata Consultancy Services Limited | Systems and methods for adaptive sensors calibration |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2015102589A1 (en) * | 2013-12-30 | 2015-07-09 | Apple Inc. | Motion artifact cancelation |
| TW201838584A (en) * | 2017-04-18 | 2018-11-01 | 原相科技股份有限公司 | Electronic apparatus and method capable of reducing or avoiding offset interference and accurately measuring physiological characteristics of user |
-
2019
- 2019-10-18 CN CN201910996221.1A patent/CN110823369B/en active Active
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2007097702A1 (en) * | 2006-02-21 | 2007-08-30 | Lindberg Lars-Goeran | Non-invasive monitoring of blood flow in deep tissue |
| CN103271745A (en) * | 2013-06-07 | 2013-09-04 | 秦皇岛市康泰医学系统有限公司 | Pulse blood oxygen simulation system and implementation method |
| CN104414626A (en) * | 2013-08-23 | 2015-03-18 | 同方健康科技(北京)有限公司 | Electronic magnetic induction blood pressure monitor and method of parameter calibration on same |
| CN107847166A (en) * | 2015-06-30 | 2018-03-27 | 皇家飞利浦有限公司 | Utilize the sensing system and method for multiple PPG sensors |
| EP3395236A1 (en) * | 2017-04-25 | 2018-10-31 | Tata Consultancy Services Limited | Systems and methods for adaptive sensors calibration |
Also Published As
| Publication number | Publication date |
|---|---|
| CN110823369A (en) | 2020-02-21 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN110823369B (en) | Reflection-type photoelectric volume wave analog calibration method and device | |
| USRE39268E1 (en) | Simulation for pulse oximeter | |
| US11147456B2 (en) | Marker with light emitting area for use in determining vital sign information | |
| US6997879B1 (en) | Methods and devices for reduction of motion-induced noise in optical vascular plethysmography | |
| US20100185068A1 (en) | Non-contact photoplethysmographic pulse measurement device and oxygen saturation and blood pressure measurement devices using the same | |
| AU2009298937B2 (en) | System and method for photon density wave pulse oximetry and pulse hemometry | |
| JPH03500614A (en) | Equipment and methods used in pulse oximetry | |
| CN105960264B (en) | The monitoring based on camera to the vital sign during phototherapy disposition | |
| EP2953529A1 (en) | System and method for determining vital sign information of a subject | |
| JP2004135854A (en) | Reflection type photoelectric pulse wave detector and reflection type oxymeter | |
| CN104224144A (en) | Photoelectric plethysmography photoelectric detection sensor | |
| JP4909904B2 (en) | Dental pulp blood measuring method, device, and dental pulp blood measuring adapter | |
| US20080081966A1 (en) | Symmetric LED array for pulse oximetry | |
| CN103876747A (en) | Calibration device for oxyhemoglobin saturation analog meter | |
| Hu et al. | Development of effective photoplethysmographic measurement techniques: From contact to non-contact and from point to imaging | |
| CN110811572B (en) | Simulation synthesis method and device for photoelectric volume wave signal | |
| CN109106376A (en) | The detection method and device of total hemoglobin concentration in a kind of blood | |
| CN211484538U (en) | Controllable array reflection type photoelectric sensor module | |
| CN201481422U (en) | Light-frequency converting pulse oximeter | |
| WO2015066876A1 (en) | Heart rate detection method and device | |
| Fortin et al. | The importance of VERIFI (“Vasomotoric Elimination and Reconstructed Identification of the Initial set-point”) for the performance of the CNAP technology | |
| RU2770266C2 (en) | Sensor for an optical cerebral oximeter, apparatus for securing the sensor to the head of the patient and method for operation of the sensor | |
| Nomoni et al. | A pulsatile optical tissue phantom for the investigation of light-tissue interaction in reflectance photoplethysmography | |
| AvakhKisomi et al. | A novel wireless ring-shaped multi-site pulse oximeter | |
| US20070129617A1 (en) | Light source drive algorithm |
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 | ||
| TR01 | Transfer of patent right | ||
| TR01 | Transfer of patent right |
Effective date of registration: 20231110 Address after: West side of the second floor of Building 3, No. 8-3 Chunwang Road, Panyang Industrial Park, Huangdai Town, Xiangcheng District, Suzhou City, Jiangsu Province, 215000 Patentee after: Suzhou Sanlang Medical Technology Co.,Ltd. Address before: 710000 workshop 2 in yard 5, West Qinling Third Road, Caotang science and technology industry base, high tech Zone, Xi'an, Shaanxi Province Patentee before: SHAANXI HUACHEN PETROLEUM TECHNOLOGY CO.,LTD. Effective date of registration: 20231110 Address after: 710000 workshop 2 in yard 5, West Qinling Third Road, Caotang science and technology industry base, high tech Zone, Xi'an, Shaanxi Province Patentee after: SHAANXI HUACHEN PETROLEUM TECHNOLOGY CO.,LTD. Address before: 710049 No. 28 West Xianning Road, Shaanxi, Xi'an Patentee before: XI'AN JIAOTONG University |