TW201511735A - A PPG-based physiological sensing system with a spatio-temporal sampling approach towards identifying and removing motion artifacts from optical signals - Google Patents

Abstract

The present invention pertains mainly to the fields of fitness and/or sport performance by enabling robust and accurate determination of physiological parameters, including, but not limited to, heart rate and breathing rate as indicator of physical exertion or intensity during exercise. In one embodiment, the present invention is a PPG-based physiological sensing system employing a spatio-temporal sampling approach towards identifying and removing motion artifacts from optical signals received from a wearable optical sensing device in real-time and during various states of physical activity. The invention comprises a wearable optical sensing device capable of sensing and transmitting optical signals representative of physiological parameters to a remote electronic device. The wearable optical sensing device comprises an optical sensing unit with a light-emitting and light-detecting module for measuring blood volume changes caused by expansion and contraction of the small blood vessels in the skin and underlying tissue during the cardiac cycle. The spatial arrangement and temporal sampling configuration (sequence) of the system subsequently allows for a common absorption point to be determined mathematically for each multi-channel sampling period, thereby obtaining an instantaneous optical measurement at different positions on the propagating pulse wave.

Description

PPG-based physiological sensing system with space-time sampling path for optical signal recognition and removal of moving artifacts

Cross-reference to related applications

The present application claims priority to U.S. Provisional Application No. 61/862,767, filed on Aug. 6, 2013, and U.S. Provisional Application No. 61/870,266, filed on Aug. 27, 2013. The title of the US Provisional Application is "A Ppg-Based Physiological Sensing System With A Spatio-Temporal Sampling Approach Towards Identifying And Removing Motion Artifacts From Optical Signals", and the specification thereof is incorporated herein by reference in its entirety.

The present invention relates primarily to (particularly) by achieving physiological parameters (including but not limited to) as an indicator of physical exertion or intensity during exercise and for subsequent determination (but not limited to) excessive oxygen consumption after exercise ( The field of fitness and/or athletic performance of EPOC, informally known as afterburn rate and respiratory rate, is robust and accurate.

The pulse rate (usually and interchangeably referred to as the heart rate) is the rate at which the heart beats in units measured in beats per minute (bpm). The heart rate measured during physical activity (eg, exercise) is usually higher than the heart rate measured at rest and used as a cardiac response A measure of the efficiency of increasing the demand for blood supply during physical activity. Thus, the heart rate is typically used to monitor and adjust the intensity or level of effort during exercise.

Recently, with the advancement of self-monitoring of physiological parameters, it has attracted increasing attention and needs to be able to accurately and accurately measure physical activity in various states (i.e., during quiet, during moderate activities, and during intense exercise). Non-invasive, interference-free, wearable physiological sensing device for heart rate and other physiological parameters.

For this purpose, optical plethysmography (PPG) is widely used in the well-known optical sensing technology for measuring blood analytes and hemodynamic properties. In most basic forms, PPG technology only requires illumination of a light source (eg, a light-emitting diode, LED) of a tissue sample (eg, skin) and small changes in the intensity of the measured light (ie, the physiological properties of the sample being measured) Associated absorption light detectors (eg, photodiodes). The light absorption of the sample to be measured may be by absorption of skin (melanin content), tissue, blood (water/fluid and different hemoglobin species), and blood volume (ie, due to expansion and contraction of small blood vessels during the heart cycle). The result of the level of tissue perfusion). A PPG signal indicating a change in blood volume during a heart cycle can be used to determine the heart rate by studying the time interval between successive peaks (or valleys) in the PPG signal or volume pulse. In addition, information about hemodynamic properties (such as blood pressure per pulse and pulse wave velocity (as an indicator of arterial stiffness)) can be extracted from the waveform characteristics of the PPG signal, while different hemoglobin (Hb) species at different wavelengths The unique light absorption property can be used to determine the blood oxygen level condition (i.e., oxygen saturation).

Physiological sensing devices based on PPG technology are well known in the art and exist in two configurations: i) a reflective sensing device, and ii) a transmissive sensing device. The PPG-based reflective sensing device includes a light source and a photodetector on the same side of the sample to be measured, and the PPG-based transmissive sensing device includes a light source and a photodetector on the opposite side of the sample to be measured. The main advantage of the PPG-based reflective sensing device is its adaptability to various positions on the human body (for example, the user's arms, legs, torso, etc.), while the PPG-based transmissive sensing device is limited to the body. a position that allows light to be easily transmitted (for example, The user's fingertips, earlobe, or another relatively thin, well-perfused tissue or body part).

Although LED and photodiode technology have played a central role in reducing the cost and size of modern physiological sensing devices based on PPG, the common defects of existing physiological sensing devices based on optics are inherent sensitivity to interference. And the subsequent inaccuracy caused by moving artifacts. Various methods, sampling paths, and signal processing techniques have been developed and illustrated to reduce the effects of optical signals. For this purpose, many existing devices use a combination of optical-based solutions and accelerometer-based solutions; however, there is currently no method suitable for solving problems related to physical activity in all states, including violent activities such as during exercise. Or device.

Thus, there is a need for a solution that overcomes many of the problems and shortcomings associated with optical based existing physiological sensing devices that address sensitivity to interference and inaccuracies caused by moving artifacts during physical activity of various states.

Although the present invention has been described in detail in the following detailed description of the embodiments of the invention, it is understood that the invention is not to be construed as limited Make changes in the case.

In one embodiment, the present invention discloses a PPG-based reflective physiological sensing system having optical signal recognition and removal of moving artifacts received from a wearable optical sensing device to achieve physical activity for various states. Space-time sampling path for accurate and robust determination of physiological parameters (including but not limited to heart rate) during the period. The PPG-based physiological sensing system includes a remote electronic device (such as a smart phone (eg, iPhone) that is preferably worn on, but not limited to, the user's upper arm and with a specially developed software application. ^TM )) A wearable optical sensing device for communication. The wearable optical sensing device includes optical sensing and light sensing module optical measurement for measuring blood volume changes caused by expansion and contraction of small blood vessels in the skin and underlying tissue during a heart cycle unit. The physical design of the optical sensing unit allows for rapid (i.e., almost instantaneous) sequential sampling at different locations on the propagation volume pulse. The spatial configuration and time sampling configuration (sequence) of the system then allows mathematically determining common absorption points for each multi-channel sampling period, thereby obtaining instantaneous optical measurements at different locations on the propagation pulse. The original optical signal representing the change in blood volume is transmitted to the remote electronic device executing the professionally developed software application, the specially developed software application configured to: i) receive and process the raw optical signal; and ii Obtain, store, and store an accurate and robust physiological output (including, but not limited to, heart rate and respiratory rate) and display it to the user via the user interface. In addition, the processed optical signal is used to determine the instantaneous oxygen consumption (VO ₂ ) (but not limited to the determination) and to measure the severity of the exercise (such as, but not limited to, excessive oxygen consumption after exercise (EPOC, informally called After burning)). Naturally, several additional physiologically relevant metrics can be determined (with or without accelerometers or other activity sensing techniques) such as, but not limited to: (i) exercise rhythm; (ii) optimal exercise rhythm (iii) Total oxygen consumption normalized by activity; (iv) EPOC standardized by activity; (v) VO ₂ max; (vi) orthostatic heart rate test for over-training; (vii) heart rate change Rate; (viii) calorie utilization; and (ix) blood lactate concentration.

1‧‧‧ Physiological sensing system based on optical plethysmography

2‧‧‧Dressable optical sensing device

3‧‧‧User upper arm

4‧‧‧ Remote electronic device

5‧‧‧Sensor unit

6‧‧‧Signal Amplifier

7‧‧‧Low-pass filter

8‧‧‧ Analog to digital converter

9‧‧‧Microprocessor

10‧‧‧ transceiver

11‧‧‧Antenna

12‧‧‧Rechargeable battery

13‧‧‧Memory components

14‧‧‧ transceiver

15‧‧‧Professional development of software applications

16‧‧‧ Processor

17‧‧‧Rechargeable battery

18‧‧‧ memory components

19‧‧‧User interface

20‧‧‧Light-emitting diodes/light-emitting diodes of the same wavelength

21‧‧‧Photodiode/shared photodiode

22‧‧‧Antenna

BL‧‧‧Bottom left

Blc1‧‧‧Starting blank cycle/start

Blc2‧‧‧ Blank Cycle/End

BR‧‧‧Bottom right

TL‧‧‧ upper left

TR‧‧‧top right

The drawings are used to further illustrate the various embodiments of the present invention, and are in accordance with the principles of the invention Together, they are incorporated in the specification and form part of this specification.

The invention is illustrated by reference to the exemplary embodiments of the accompanying drawings, which are not drawn to any scale, wherein: FIG. 1 is a PPG-based physiological sensing system including a wearable optical sensing device in communication with a remote electronic device A conceptual illustration of an exemplary embodiment includes the remote electronic device containing and executing a specially developed software application configured to process optical signals and display physiological output to a user via a user interface.

2 is a conceptual illustration of an electronic component including a wearable optical sensing device that is preferably worn on, but not limited to, the upper arm of a user.

3 is a conceptual illustration of an electronic component including a remote electronic device, such as a smart phone (eg, ^iPhoneTM ).

4 is a conceptual illustration of an optical sensing unit including a light emitting and light detecting module and its configuration within the scope of the illustrative embodiment.

5 is a conceptual illustration of a series of spatiotemporal sampling paths for optical signal recognition and removal of moving artifacts, illustrated by an exemplary spatial configuration and time sampling configuration (sequence), wherein: FIG. 5A illustrates multi-channel sampling. Pathway and accompanying nomenclature; Figure 5B summarizes the spatial configuration and time sampling configuration (sequence) used as an example throughout the present invention; Figure 5C illustrates a sampling period and a non-sampling period consisting of multiple sampling steps Complete sample sequence; Figure 5D illustrates mathematically determining the common absorption point for each multi-channel sampling period.

The detailed description and the accompanying drawings set forth and illustrate the various aspects of the invention. The description, examples and figures are not intended to limit the scope of the invention in any way.

1 is a conceptual illustration of an illustrative embodiment of a PPG-based physiological sensing system 1 including a wearable optical sensing device 2 preferably worn on, but not limited to, a user's upper arm 3 . The wearable optical sensing device 2 is coupled to a remote electronic device 4 (eg, a smart phone (eg, a smart phone) capable of receiving and processing optical signals transmitted from the wearable optical sensing device 2 and displaying the output to the user via a user interface (eg, , iPhone ^TM ) or equivalent device) communication. Although, other agreements may also be used, exemplary methods of data transmission and then to Bluetooth ^TM. The remote electronic device 4 contains and executes a specially developed software application configured to perform the following steps: i) receiving and processing raw optical signals from the wearable optical sensing device 2 ; and ii) obtaining and storing robustness And accurate physiological output (including but not limited to heart rate) and displayed to the user via the user interface. Optical signals received from the wearable optical sensing device 2 can also be used to obtain other physiological parameters including, but not limited to, respiratory rate.

In an alternative embodiment of the present invention, processing of the original optical signal may occur on the wearable optical sensing device 2 , and the final physiological output may be transmitted to the remote electronic device 4 containing the appropriate software application via the user interface. The physiological output is displayed to the user. In another alternative embodiment of the present invention, partial processing of the original optical signal may occur on the wearable optical sensing device 2 , and the partially processed signal may be transmitted to the remote electronic device 4 containing the appropriate software application. For final processing of physiological output and display to the user via the user interface. In still another alternative embodiment of the present invention, processing of the original signal and display of the physiological output to the user may occur on the wearable optical sensing device 2 , in this processing configuration, wearable Optical sensing device 2 includes a suitable user interface.

FIG 2 conceptually illustrates a system comprising an electronic component of a wearable optical sensing device 2, the wearable optical sensing means 2 include (but are not limited to) coupled to the sensing unit 5 of the microprocessor 9, the signal amplifier 6 , low pass filter 7 , analog to digital converter (ADC) 8 , memory component 13 and transceiver 10 . The antenna 11 coupled to the transceiver 10 supports communication (i.e., data transfer between the optical sensing device 2 and the remote electronic device 4 ). The antenna 11 can be connected wirelessly (e.g., Bluetooth ^(TM) or the like) or can represent a wired connection to the remote electronic device 4 . Electronic components coupled to the rechargeable battery 12 may be recharged by a battery power supply 12, and all of these electronic components housed in the waterproof case (not shown) in the. The optical sensing unit 5 under the control of the microprocessor 9 generates an analog signal through the signal amplifier 6 and the low pass filter 7 indicating the intensity of the light measured by the light detecting module (illustrated in FIG. 4). The adjusted analog signal is converted to a digital signal by the ADC 8 and is ready to be transmitted by the microprocessor 9 . The raw optical signals are transmitted via transceiver 10 and antenna 11 to a suitable remote electronic device (e.g., ^iPhoneTM ) for processing and outputting the display.

Other functions of the microprocessor 9 may include determining whether the PPG signal peak is too large (i.e., saturated) or too weak (i.e., causes a bad signal to noise ratio). This gain control level is achieved by providing a microprocessor 9 that feeds back to the optical sensing unit 5 via a digital to analog converter (DAC) (not shown). If the detected pulse peak is too weak, the microprocessor 9 provides feedback to the optical sensing unit 5 via the DAC to increase the intensity of the LED by increasing the current, or to reduce the current if the signal is saturated. It is especially important to adjust the brightness of the LED to obtain a suitable signal system, since the standard values between users can be based on skin color (melanin content), blood pressure, pulse strength and/or other changes that can occur during the variable exercise mode. Significantly different (for example, changes in ambient temperature or body temperature). In addition, gain control valuablely helps to conserve battery power within the system.

Another function of the microprocessor 9 can include: capturing the battery power of the wearable optical sensing device 2 , and transmitting the information to the remote end if not displayed locally (eg, via voice prompts, vibration alerts, and the like) The electronic device 4 is for display to the user via the user interface.

The requirements for the memory component 13 depend on the preferred processing configuration of the system, i.e., whether the raw optical signal is fully processed, partially processed, or not processed at all on the wearable optical sensing device 2 . In the exemplary embodiment, all signal processing occurs on the remote electronic device 4 and thus the memory component 13 is not a limitation of the design of the wearable optical sensing device 2 . However, in an alternative embodiment having a processing configuration in which any level of signal processing occurs on the wearable optical sensing device 2 , the memory component 13 must not be designed for the wearable optical sensing device 2 Less.

Figure 3 conceptually illustrates a system comprising an electronic component of the distal end 4 of the electronic device, the electronic device 4 comprises a distal end (but not limited to) a processor coupled to the memory 18 of the assembly 16, user interface 19 and the transceiver 14. The antenna 22 coupled to the transceiver 14 supports communication (i.e., data transfer between the remote electronic device 4 and the wearable optical sensing device 2 ). The antenna system 22 may be a wireless (e.g., Bluetooth ^TM or a grade thereof), or may represent a connection to a wired wearable sensing device 2 of the optical connector. Electronic components coupled to the rechargeable battery 17 may be recharged by a battery-powered 17, and all such as electronic components housed in the housing for the decision by the manufacturer. The distal end of the electronic device 4 may be (for example) 15 comprises a receiver capable of execution by the software developed by the specialized application (the App) from a wearable optical sensing means of the second optical signal smart phone (such as, iPhone ^TM ) or an equivalent device. In an exemplary embodiment, remote electronic device 4 executes a heartbeat rate monitoring application configured to perform the following steps: i) receiving and processing an original optical signal indicative of a change in blood volume (ie, from a wearable optical sensation) The pulse of the measuring device 2 ; and ii) obtain and store an accurate and robust heart rate and output it to the user via the user interface 19 .

The heartbeat rate output displayed to the user via the user interface 19 of the remote electronic device 4 can, for example, be used to form an exercise schedule based on a particular ability and/or fitness goal of the individual. For example, the maximum estimated heart rate that will begin can be calculated based on the age and fitness level of the user or empirically determined. This concept determines the range of ideal heart rate for a particular fitness or performance goal. The maximum estimated heart rate may correspond to an extreme play level, and the different exercise intensity levels may correspond to different heart rate ranges spanning from a maximum estimated heart rate down to a range corresponding to a quiet heart rate. In this way, a range of heart rate rates for different exercise intensities can be formed to allow the user to more effectively control and/or monitor their activity levels, track their progress, and reach their fitness goals. Importantly, the heart rate and other physiological output decisions determined in this manner are intended only as a guide and are susceptible to appropriate modification and/or interpretation.

The wearable optical sensing device 2 includes optical sensing and light detecting modules for measuring light volume changes caused by expansion and contraction of small blood vessels in the skin and underlying tissue during a heart cycle Unit 5 . FIG. 4 illustrates an exemplary configuration of a light emitting and light detecting module including an optical sensing unit 5 . In an exemplary embodiment, the light emitting module is configured by a group of four identically surrounding a light detecting module that includes a single photodiode 21 having spectral sensitivity across the spectral sensitivity of the light emitting module. The wavelength LED 20 is composed. In an alternative embodiment of the invention, the light emitting module can include two or more distinct wavelengths and/or a higher plurality of light sources. Similarly, in an alternative embodiment of the invention, the light detecting module can include a higher plurality of light sensors having spectral sensitivity across the spectral sensitivity of the light emitting module. The light emitting module and the light detecting module are positioned in close proximity to one another and positioned to the skin surface of the user to allow for accurate measurement of changes in blood volume at a single location on the user's body. The spatial configuration and time sampling configuration (sequence) of the optical sensing unit 5 under the control of the microprocessor 9 allows mathematically determining the common absorption point for each multi-channel sampling step (described below in Figure 5).

For the purposes of the present invention, an illustrative embodiment having a light emitting module comprising four identical LEDs having wavelengths in the visible green spectrum (eg, 525 nm) is illustrated, but is not intended to limit the invention in any way. category. Depending on the specific requirements of the system, a higher number of LEDs and/or the incorporation of two or more distinct wavelengths in the measurement may provide additional information for subsequent analysis.

A spatiotemporal sampling approach using optical signal recognition and removal of moving artifacts is described below with reference to Figures 5A-5D . Multi-channel sampling by the optical sensing unit 5 comprising a plurality of LEDs 20 and a single common photodiode 21 is achieved by alternating sequential sampling of the LEDs under the control of the microprocessor 9 . An exemplary six channel sampling configuration is illustrated in Figure 5A . The sampling period includes a blank period at the beginning ( Blc1 ) and end ( Blc2 ) of the sampling. By measuring the light level without LED illumination, it is possible to determine and compensate for ambient light effects over the entire sampling period. After the initial blanking period ( Blc1 ), the exemplary time sampling configuration (sequence) follows the "diagonally spanning" pattern, starting at the upper left ( TL ) position and continuing to the lower right ( BR ), lower left ( BL ) and the upper right ( TR ) position. The sampling period ends with a blank period ( Blc2 ). This exemplary time sampling configuration (sequence) used as an example of the present invention is summarized in Figure 5B . Seven additional (eight total) sampling configurations (resolving their common absorption points (see Figure 5D)) by rotating only the "diagonally spanning" sampling sequence to different starting positions are present in the exemplary embodiment and sampling Within the scope of the sequence. Similarly, numerous sampling configurations (sequences) having a higher plurality of light sources (having two or more distinct wavelengths) to achieve spatiotemporal sampling are applicable to alternative embodiments of the present invention. Figure 5C is used to illustrate a complete sample sequence of an exemplary sampling configuration consisting of a sampling period comprising a plurality of sampling steps and a non-sampling step designated for data preparation and transmission.

The physical design of the optical sensing unit 5 allows for near instantaneous absorption measurements at different locations on the propagated pulse wave via rapid sequential sampling. The spatial configuration and time sampling configuration (sequence) of the system allows mathematically determining the common absorption point for each multi-channel sampling period, as illustrated in Figure 5D . The goal of the spatiotemporal sampling approach is to simultaneously (ie, instantaneously) obtain optical measurements at different locations of the propagation pulse. For example, an alternative approach to achieving the same goal would include a photodiode for each LED in the system, thereby allowing for instantaneous illumination and measurement of all LEDs. In doing so, it is easier to identify and remove unexpected behavior (ie, accidents based on known and/or inferred physiological limitations (such as pulse wave velocity, heart rate acceleration and deceleration, etc.), such as making optical signals Deteriorating moving artifacts.

Spatiotemporal sampling is achieved by first specifying a common absorption point of the optical measurement to be obtained around each of the sampling positions on the propagation pulse. To fall in pairs of sampling points (for example, TL-BL (top-bottom); TL-TR (left-right); BR-BL (right-left); BR-TR (bottom-top); Blc1-Blc2 ( Background)) Specify the common absorption point in a way that spans the range. In the illustrated example, the common absorption point is assigned to the middle of the sampling period including a plurality of sampling steps, however, this need not always be the case.

The known sampling time ( t ) and sampling point ( 0.5t ) are further assigned to each sampling step. In the illustrated example, the sampling point is assigned to the middle of the sampling step, however, this need not always be the case. Given the known sampling time t , the selected time sampling configuration (sequence) allows time-aligned absorbance values that are sequentially measured at different locations on the propagation pulse to be time aligned at the common absorption point. In this way, time dependent estimates of the measured values of the absorbance at different locations on the pulse wave and measurements obtained during the blank period can be estimated at the same point in time.

For the interpretation, take the time alignment of the measured absorbance values obtained at the upper left ( TL ) position and the upper right ( TR ) position: TL and TR are time aligned with respect to the common absorption point, so that the common absorption point is before The sampling time and the sampling time after the common absorption point are the same and are equal to 1.5t respectively. It is inferred that the "top" time-pair can be obtained by averaging the absorption values obtained for the TL position and the TR position, respectively, that is, the time coefficient for the time-aligned "top" absorption rate estimation 0.5). Quasi-absorption estimate ( a ): a = 0.5 ( TL + TR )

The time coefficient is calculated by dividing the sampling time from the first correlation measurement location to the sampling time taken by the specified common absorption point by the total sampling time taken between the selected paired points. For example, for the time alignment of the measured absorbance values obtained at the TL position and the TR position, the time coefficient is calculated as follows:

Similarly, it can be obtained by separately averaging (time coefficient 0.5) at the lower right ( BR ) position and the lower left ( BL ) position and at the blank period at the beginning ( Bcl1 ) and end ( Blc2 ) of the sampling. Absorbance values to obtain a "bottom" time-aligned absorbance estimate ( b ) and a "blank" time-aligned absorbance estimate ( c ): b = 0.5 ( BR + BL )

c = 0.5 ( Blc 1+ Blc 2)

While the same principle applies to the time alignment of the absorbance values measured at the upper left ( TL ) position and the lower left ( BL ) position, the alignment is asymmetrical in this case. To illustrate, TL and BL are temporally aligned with respect to the common absorption point such that the sampling time before the absorption of the estimated point is 1.5t and 0.5t , respectively, after the absorption of the estimated point. It is inferred that the time-dependent absorption rate estimate ( d ) of the "left side" can be obtained by means of a time coefficient of 0.75: d = 0.75 ( BL - TL ) + TL

Similarly, the "right" time-aligned absorbance estimate ( e ) can be obtained from the absorbance measured at the lower right ( BR ) position and the upper right ( TR ) position with a time factor of 0.25: e = 0.25 ( TR - BR )+ BR

In the entire calculation of the time-aligned absorption estimate, the designated sampling point ( 0.5t ) for each sampling step is used as the measurement point. Moreover, the accuracy of this linear approximation of the absorbance values at the common absorption point is susceptible to a sampling time t that is approximately zero.

The time-aligned absorption estimate can then be incorporated into digital signal processing techniques that identify and remove moving artifacts from optical signals to obtain robust and accurate physiological parameter determination (eg, Kalman filtering, Fourier analysis, peak identification, independent components) One of the analysis and others, or a combination thereof. For this purpose, the time-aligned "top" ( a ), "bottom" ( b ), "left" ( d ) and "right" ( e ) absorbance estimates can be applied separately or averaged to obtain spatial pairs. Quasi-absorption rate estimation. The time-aligned "blank" ( c ) absorbance estimate is applied to compensate for ambient light effects during individual sampling steps or throughout the sampling period.

In addition, the processed optical signal can be used to determine the instantaneous oxygen consumption (VO ₂ ) (but not limited to this determination) and to measure the intensity of the exercise (such as (but not limited to), after the exercise, the oxygen consumption (EPOC, informally Known as post-combustion. Naturally, several additional physiologically relevant metrics can be determined (with or without accelerometers or other activity sensing techniques), such as (but not limited to): (i) exercise rhythm; Ii) optimal exercise rhythm; (iii) total oxygen consumption normalized by activity; (iv) EPOC standardized by activity; (v) VO ₂ max; (vi) orthostatic heart rate test for over-training; (vii) rate of change in heart rate; (viii) calorie utilization; and (ix) blood lactate concentration. The information obtained is intended to be used as a guide to a particular fitness and/or athletic performance goal of the user.

Having thus described the exemplary embodiments of the present invention, it will be understood by those skilled in the art that the disclosures of the exemplary embodiments are merely illustrative and that various alternatives and modifications can be made within the scope of the present invention. And modify. Therefore, the invention is not limited to the specific embodiments as illustrated herein, but only by the scope of the following claims.

1‧‧‧ Physiological sensing system based on optical plethysmography

2‧‧‧Dressable optical sensing device

3‧‧‧User upper arm

4‧‧‧ Remote electronic device

Claims (24)

An optical sensing device capable of performing percutaneous measurement on a user, comprising: a light emitting module that is close to a skin of the user, the light emitting module comprising a plurality of light sources having different wavelengths, the plurality At least one of the light sources has a wavelength in the green spectrum, and at least a second one of the plurality of light sources has a second wavelength greater than 740 nm; and a light detecting module that is proximate to the skin of the user and The light emitting module is configured to detect light from the light emitting module and reflected off the skin of the user. The optical sensing device of claim 1, wherein the second wavelength is greater than 740 nm. The optical sensing device of claim 1, wherein the second wavelength is at an absorption point such as oxyhemoglobin and deoxyhemoglobin. The optical sensing device of claim 1, wherein the light detecting module measures light absorption associated with physiological parameters of the user. The optical sensing device of claim 1, wherein the light emitting module is configured such that at least a portion of the emitted light penetrates the skin of the user. The optical sensing device of claim 1, further comprising a processor coupled to the light emitting module to: disable the plurality of light sources during a first time period; sequentially enabling the plurality of lights one at a time Each of the light sources; and deactivating the plurality of light sources during the last time period. The optical sensing device of claim 6, further comprising a processor configured to calculate physiological parameters using information from the light detecting module obtained during the first time period and the last time period To compensate for information obtained from the photodetection module during the time periods. An optical sensing device according to claim 1, configured to detect emission from the light The module penetrates at least a portion of the backscattering of the light of the user's skin, wherein at least one of the plurality of light sensors has a spectral sensitivity across a spectral sensitivity of the light emitting module. The optical sensing device of claim 1, further comprising a processor coupled to the light detecting module, wherein the processor recognizes and removes the moving fake from the detected light indicating physiological parameters related to light absorption a time-space sampling path, the processor performing the steps of: receiving optical signals from the light detecting module; processing the optical signals to obtain time aligned values; time aligned values and/or no time pairs The quasi value is incorporated into at least one digital signal processing technique; and the at least one associated physiological parameter is calculated based on the at least one digital signal processing technique. An optical sensing device capable of performing percutaneous measurement on a user, comprising: a light emitting module that is close to a skin of the user, the light emitting module comprising a plurality of light sources having different wavelengths, the plurality At least one of the plurality of light sources has a first wavelength, and at least a second one of the plurality of light sources has a second wavelength; and a light detecting module that is adjacent to the skin of the user and the light emitting module, For detecting light originating from the light emitting module and reflecting off the skin of the user. A method for percutaneous measurement of a user, comprising the steps of: providing a light emitting module proximate to a skin of the user, the light emitting module comprising a plurality of light sources having different wavelengths, the plurality At least one of the light sources has a wavelength in the green spectrum, and at least a second one of the plurality of light sources has a second wavelength greater than 740 nm; and provides access to the skin of the user and the light emitting module a light detecting module for detecting a light source from the light emitting module and reflecting off the skin of the user Light. The method of claim 11, further comprising the step of estimating the oxygen uptake amount (VO ₂ ) by calculating the oxygen uptake amount (VO ₂ ) based on the optically determined heart rate and/or the respiratory rate value. The method of claim 11, further comprising the step of estimating the oxygen uptake amount (VO ₂ ) by calculating an oxygen uptake amount (VO ₂ ) based on the optically determined heart rate and/or the respiratory rate value and the movement sensing data. The method of claim 11, further comprising the step of estimating post-exercise oxygen consumption (EPOC) by calculating an oxygen uptake (VO ₂ ) based on an optically determined heart rate and/or a respiratory rate value; The oxygen consumption after exercise was calculated based on the oxygen uptake (VO ₂ ). The method of claim 11, further comprising the step of estimating post-exercise oxygen consumption (EPOC) by calculating an oxygen uptake based on the optically determined heart rate and/or respiratory rate value and the motion sensing data ( VO ₂ ); and calculate the oxygen consumption after exercise according to the oxygen uptake (VO ₂ ). The method of claim 11, further comprising the step of estimating the post-exercise oxygen consumption by calculating the post-exercise oxygen consumption (EPOC) based on the oxygen uptake (VO ₂ ). The method of claim 11, further comprising the step of estimating energy consumption by calculating an oxygen uptake amount (VO ₂ ) based on an optically determined heart rate and/or a respiratory rate value; and depending on an oxygen uptake amount (VO _{2 )} ) Calculate energy consumption. The method of claim 11, further comprising the step of estimating energy consumption by: calculating an oxygen uptake amount (VO ₂ ) based on an optically determined heart rate and/or a respiratory rate value and/or moving sensing data; Energy consumption is calculated based on oxygen uptake (VO ₂ ) and/or motion sensing data. The method of claim 11, further comprising the step of estimating energy consumption by calculating energy consumption based on oxygen uptake (VO ₂ ). The method of claim 11, further comprising the step of estimating energy expenditure by calculating an energy consumption based on the optically determined heart rate and/or the breathing rate value. The method of claim 11, further comprising the step of estimating energy expenditure by calculating energy consumption based on the optically determined heart rate and/or respiratory rate value and/or the motion sensing data. The method of claim 11, further comprising the step of estimating the blood lactate concentration by calculating the oxygen uptake amount (VO ₂ ) based on the optically determined heart rate and/or the respiratory rate value; and depending on the oxygen uptake amount (VO _{2 )} Calculate the oxygen consumption after exercise; and estimate the blood lactate concentration based on the predicted oxygen consumption after exercise. The method of claim 11, further comprising the step of identifying and removing moving artifacts indicative of physiological parameters associated with light absorption by: generating optical from the light detecting module configured to enable spatiotemporal sampling Processing the optical signal to obtain a time alignment value; incorporating the time alignment value and/or the non-time alignment value into at least one digital signal processing technique; and processing according to the at least one digital signal Technical calculations related physiological parameters. The method of claim 11, further comprising the step of identifying a tempo by: generating an optical signal from the light detecting unit configured to enable spatiotemporal sampling; processing the optical signal to obtain a time aligned value and not Time aligned values; the time aligned values are incorporated into at least one digital signal processing technique; and the tempo is calculated in accordance with the at least one digital signal processing technique.