KR100650044B1 - Mobile radio terminal with blood pressure monitoring system PPG signal - Google Patents

Abstract

The present invention relates to a portable wireless terminal incorporating a blood pressure measurement system using a photoplethysmographic signal (hereinafter referred to as PPG).

The portable wireless terminal incorporating the blood pressure measuring system of the present invention detects a PPG (optical blood flow measurement signal) signal, generates blood pressure information, and transmits the blood pressure information to a designated manager computer via a wireless station and a network. A portable wireless terminal having a built-in, comprising: a PPG signal detection unit for detecting a PPG (optical blood flow measurement signal) signal having an LED (light emitting diode) unit and an optical sensor; A temperature signal detector having a temperature sensor to detect a temperature signal; A pressure signal detection unit having a pressure sensor to detect a pressure signal; A data acquisition system for receiving output signals of the PPG signal detector, the temperature signal detector, and the pressure signal detector and converting them into digital signals; An arithmetic processing unit for calculating a blood pressure value from the PPG signal, the pressure signal, and the temperature signal received from the data collection system when the pressure signal and the temperature signal received from the data collection system are respectively within predetermined reference ranges; And a key input unit for generating a blood pressure measurement start command.

In addition, when the detected pressure signal and the temperature signal are within the reference range, respectively, the systolic blood pressure BP _SYS , the systolic blood volume signal PPG _SYS , the pulse wave signal PR, and the systolic blood pressure correlation coefficients a _SYS and b. _SYS , c _SYS ) and obtained by BP _SYS = a _SYS PPG _SYS + b _SYS PR + c _SYS to obtain diastolic blood pressure (BP _DIA ), diastolic blood volume signal (PPG _DIA ), pulse wave signal (PR), diastolic blood pressure The correlation coefficients (a _DIA , b _DIA , c _DIA ) are obtained by BP _DIA = a _DIA PPG _DIA + b _DIA PR + c _DIA .

In addition, in the systolic blood pressure correlation coefficients a _SYS , b _SYS , and c _SYS , a _SYS , b _SYS has a negative value, c _SYS has a positive value, and the diastolic blood pressure correlation coefficients a _DIA , b _DIA , c _DIA In a _DIA , b _DIA has a negative value and c _DIA has a positive value.

Optical blood flow measurement signal, PPG, temperature, pressure, systolic blood pressure, diastolic blood pressure, pulse wave signal, systolic blood volume signal, diastolic blood volume signal

Description

Mobile radio terminal with integrated blood pressure measurement system using optical blood flow measurement signal PPG signal

1 is an absorption coefficient according to the wavelength of light of deoxyhemoglobin (Hb) and oxyhemoglobin (HbO ₂ ).

2 is an example of a PPG signal.

3 is a schematic block diagram illustrating a portable wireless terminal incorporating a blood pressure measuring system using a PPG signal according to an embodiment of the present invention.

4 is a block diagram illustrating a PPG signal detector of FIG. 3.

5 is an example of an attachment position on a finger of the PPG sensing unit of FIG. 4.

6 is an example of an attachment position on the finger of the PPG sensing unit, the pressure sensing unit, and the temperature sensing unit of FIG. 3.

FIG. 7 is a schematic block diagram for describing a configuration of the coefficient setting unit of FIG. 3.

FIG. 8 is a flowchart for explaining an operation of the coefficient setting unit of FIG. 7 in temperature and pressure control.

FIG. 9 is a flowchart for explaining an operation of a coefficient setting unit of FIG. 7 when temperature and pressure are not controlled.

FIG. 10 is a schematic flowchart of obtaining systolic blood pressure and diastolic blood pressure in the calculation processor of FIG. 3 during temperature and pressure control.

FIG. 11 is a schematic flowchart of calculating systolic blood pressure and diastolic blood pressure in the calculation processor of FIG. 3 when temperature and pressure are not controlled.

12A illustrates an embodiment of a portable wireless terminal incorporating a blood pressure measuring system using a PPG signal according to the present invention.

12b is another embodiment of a portable wireless terminal incorporating a blood pressure measuring system using the PPG signal of the present invention.

12c is another embodiment of a portable wireless terminal incorporating a blood pressure measuring system using the PPG signal of the present invention.

The present invention relates to a portable wireless terminal incorporating a blood pressure measurement system using a photoplethysmographic signal (hereinafter referred to as PPG).

In recent years, hypertension patients are rapidly increasing, and the most important thing in diagnosing and treating such hypertension is to periodically measure and manage blood pressure. In everyday life, however, people often forget when to measure blood pressure, and it is even more inconvenient to carry a blood pressure monitor to measure blood pressure on a regular basis. Therefore, if the blood pressure measuring system is embedded in a mobile phone, a personal digital assistant (PDA) which most people always carry, this inconvenience can be reduced. Recently, people often carry a portable wireless terminal such as a mobile phone or a PDA in their daily lives, and if such a mobile terminal such as a mobile phone or a PDA checks the blood pressure according to an alarm set for a blood pressure check time, a high blood pressure patient They will be able to manage their blood pressure more conveniently and regularly.

 The blood pressure measuring method of the blood pressure measuring system embedded in the portable wireless terminal should use a non-invasive blood pressure measuring method which is convenient for the patient to measure the blood pressure.

Non-invasive blood pressure measurement methods include auscultatory measurement, palpatory measurement, oscillometric measurement, finapres method, finger arterial pressure measurement, and phase shift of tactile sensors. There are various methods such as a method and a method using pulse wave propagation time.

Commonly used non-invasive blood pressure measurement methods include auscultation method and oscillometric method, both of which attach cuffs to the upper arm or wrist of the subject, pressurize them to a pressure higher than systolic blood pressure, occlude the artery, and then slowly depressurize Measure your blood pressure. The pinapress method uses a finger as the measurement position, provides pressure in the same manner as the oscillometric method, and then measures blood pressure by acquiring a change in blood flow through an optical method. However, the measurement method using the cuff cannot be re-measured until the occluded artery returns to its original state, which makes it unsuitable for continuous blood pressure measurement or observation of long-term changes in blood pressure. You may feel or have a skin trauma. In particular, this use of cuff is very inconvenient for patients who need to measure and manage blood pressure on a regular basis. In particular, if the blood pressure measuring method using the cuff is used in a portable wireless terminal having a blood pressure measuring system, the system becomes complicated, and in some cases, it is inconvenient to carry the cuff part separately in addition to the portable wireless terminal.

Another method is using pulse transit time (PTT), which is a method of estimating blood pressure using the inverse relationship between blood pressure and pulse wave transmission time. As a result, the pulse wave delivery time decreases, and conversely, when the blood pressure decreases, the extension of the blood vessel wall increases and the pulse wave delivery time increases. However, the method using pulse wave propagation time requires additional acquisition of ECG signal.

In addition, studies on blood pressure estimation using only a volume pulse using a reflected wave arrival time (ΔTDVP) without an ECG signal are being conducted.

Blood pressure estimation using pulse wave propagation time (PTT) and blood pressure estimation using only volume pulse wave using reflected wave arrival time (ΔTDVP) are both simple and simple because they only estimate blood pressure as a single component of the extension of the vessel wall. It offers an easy way, but there are a number of problems to solve.

Therefore, it is suitable for a portable wireless terminal incorporating a blood pressure measuring system, and a blood pressure measuring device capable of easily measuring blood pressure by a patient is desired.

The present invention provides a portable wireless terminal that does not use a cuff and has a blood pressure measurement system in which a patient can easily measure blood pressure. To this end, the present invention provides a portable wireless terminal incorporating a blood pressure measurement system using a PPG signal.

The present invention provides a portable wireless terminal incorporating a blood pressure measurement system using a more accurate PPG signal. That is, the blood pressure monitoring apparatus of the present invention defines a blood pressure according to temperature, pressure, and PPG signal to calculate a more accurate blood pressure in order to limit an error that may occur by estimating blood pressure as a single element of the extension of the blood vessel wall. Can be.

In addition, the blood pressure monitor of the present invention may not only measure blood pressure, but also analyze blood flow and pulse waves from the PPG signal to analyze information on each element to obtain information on cardiovascular function. PPG signals can provide more accurate cardiovascular function because they present cardiac output and cardiovascular resistance in the cardiovascular system.

In another aspect, the present invention provides a blood pressure monitor value that can be measured in any part of the body's arterial system that can obtain a PPG signal. Conventional blood pressure monitors can be measured only in limited areas such as wrists, upper arms, fingers and the like, but the blood pressure monitor of the present invention can be measured in any part of the human arterial system capable of obtaining PPG signals.

The theoretical background of the present invention will be described below.

Blood flow is caused by the pressure difference between each vessel, and blood flows from the high pressure to the low pressure. Factors that determine blood flow can be summarized by Equation 1, which is similar to Ohm's law.

In other words, blood flow V is equal to the ratio of ΔP (the difference in mean blood pressure between arteries and veins in the rm system) and resistance R of blood vessels.

The pressure in the vasculature (arterial and venous pressure) corresponds to the force per unit area that the blood exerts against the vessel wall, usually expressed in mmHg.

Resistance R can not be measured directly, but can be calculated from the pressure difference and blood flow between two points in the vascular system by Equation 1. Resistance to flow is caused by internal friction between the fluid layers and friction between the vessel wall and the fluid layer, which is determined by the size of the vessel, the viscosity of the liquid, and the type of flow. Blood flow can be represented by Equation 2 by the Hagen-Poiseuilles law (HPL).

은 관의 길이이며 상수 8은 속도 종단면도의 적분에서 얻어진다. Where ΔP is the pressure difference, r is the radius, η is the viscosity of the liquid,

Is the length of the tube and the constant 8 is obtained from the integral of the velocity profile.

According to Ohm's law, the resistance to flow is represented by equation (3).

It can be seen from Equation 3 that the resistance to blood flow and flow is directly proportional and inversely proportional to four squares of the radius, and these two variables are more affected by the diameter of the tube than by the length, pressure difference, or viscosity change. . In this relationship, it is clear that the change in the radius of the tube is the decisive mechanism for the effective regulation of blood flow and pressure, whether local or systemic adaptation is necessary.

Looking at the relationship between pressure and volume, the capacity of the aorta increases during human growth, and the extension (purity) is greatest in young adults (ages 16 to 39), and at older ages, the aorta dilates and purity is Decreases. As you age, your volume grows and pressure decreases. This is because, as a person ages, passive swelling occurs under constant pressure of blood and there is a decrease in elasticity in older tissues.

Because blood vessels are elastic, changes in pressure directly or indirectly change the lumen diameter and affect blood flow. Therefore, the blood flow in some blood vessels is affected by the pressure increase far greater than expected under the law of scabies in rigid tubes, resulting in a blood flow and pressure curve with a constantly increasing slope. However, in some other blood vessels, the increase in pressure causes a smaller increase in blood flow, so the slope of the curve of the blood flow-pressure of pressure continues to decrease. This effect is due to the autoregulated response of smooth muscle tissue to contraction to the kidneys (Bayliss effect). Autoregulated contractions are stronger when intravascular pressure increases, so blood pressure may increase slightly or not at all when pressure increases. This mechanism stabilizes blood supply to tissues.

The characteristics of blood vessels can be classified into six categories, such as elastic (Windkessel) vessels, resistance vessels, sphincter vessels, exchange vessels, dose vessels, and classification vessels. Double resistance vessels are terminal arteries and arterioles, and some capillaries and vasculature correspond to resistance vessels. The greatest resistance to flow occurs in all capillaries (terminal and arterioles), which have relatively small lumens and thick walls that are rich in muscle composition. Changes in the contractile state of the muscle tissue of these vessels cause a marked change in the diameter of the vessels, especially in numerous arterial stages, with a significant change in the total cross-sectional area. The effect of cross-sectional area on blood flow resistance suggests that smooth muscle activity in these vessels is a critical factor in regulating blood flow in each vessel as well as in distributing cardiac output to various organs.

In resistance in the vasculature, the aorta, arteries, and relatively long arterial branches account for about 19% of the total resistance to flow. The distal arteries and arterioles occupy nearly 50%. That is, almost half of the resistance is present in blood vessels only a few mm long. This large increase in resistance is due to relatively small diameter distal arteries and arterioles, and the reduction in cross-sectional area is not fully compensated for by increasing number of parallel tubes. Resistance in capillaries is also significant, accounting for 25% of the total. In the vein region, resistance is greatest in the varicose veins (4%), and the remaining veins occupy only 3%. Total Peripheral Resistance (TPR) is the overall resistance of the body circulation. That is the resistance of all the blood vessels connected in parallel. Total peripheral resistance and total blood flow (cardiac output) determine blood pressure at any moment. Blood pressure in the pauter system is blood volume x resistance.

Blood volume in the blood vessels is important in determining the heart's fullness during the diastolic phase and thus in determining the volume of blood ejected by the heart. Resistant vessels have high resistance and small doses. Dosage vessels have low resistance and large doses.

In arterial pressure, due to the inertia of the blood, the liquid column of blood entering the aorta during the ejector phase is prevented from simultaneously accelerating. This acceleration occurs only in the basal blood of the relative artery, causing a temporary increase in pressure, the so-called pressure pulse. At first, the pressure increases rapidly with the flow rate and then increases very slowly, after which the pressure pulse reaches its maximum after the blood flow pulse reaches its maximum. The pressure then drops.

In general, the maximum value of the pressure pulse curve during the systolic period is called the systolic blood pressure (PS), and the minimum value during the diastolic period is called the diastolic blood pressure (PD). The amplitude of blood pressure (PS-PD) is called pulse pressure. Mean blood pressure (PM), or arterial mean blood pressure, is the force that drives blood flow and represents the average of the pressure at one part of the blood vessel. This is obtained by integrating the pressure pulse curve over time. The mean blood pressure in the central artery can be represented fairly accurately by the arithmetic mean of PS and PD, the diastolic blood pressure plus half the amplitude of blood pressure (PM = PD + (PS-PD) / 2). The mean blood pressure in the peripheral artery is closer to the diastolic blood pressure plus one third of the blood pressure amplitude (PM = PD + (PS-PD) / 3).

In terms of pulse pressure, a 2001 Framingham study found that Franklin et al. Predicted that as age increases, the predictors of coronary risk shift from diastolic pressure to systolic pressure. In the 50s, diastolic blood pressure was the most powerful predictor, but in the fifties, all three components of blood pressure were equally important. After 60, diastolic blood pressure was negatively correlated with the risk of coronary artery. It is said to be a stronger risk predictor than systolic blood pressure. In physiological terms, pulse pressure is determined by three major hemodynamic factors: ventricular ejection, arterial stiffness, and wave reflection. However, ventricular rescue decreases with age, so after 50's this factor does not contribute to the increase in pulse pressure, which is mainly determined by arterial stiffness and pressure reflection.

Central large arteries not only act as conduits responsible for the transport and distribution of blood to the periphery, but also to buffer the pulsatility of the bloodstream. In other words, the large elastic arteries expand during the systolic phase and store some of the pulsatile blood flow and release them during the diastolic phase so that the blood flow continues during the deep cycle. When blood is ejected from the heart, the ascending aorta expands to produce a pulse wave that propagates peripherally along the artery, then hits the resistance of the rigid peripheral blood vessel and returns back to the heart.

As the ascending aorta moves to the peripheral artery, the size and shape of the pressure wave gradually change, but the average blood pressure is almost unchanged, but the pulse pressure gradually increases due to the increase in systolic pressure and the slight decrease in diastolic pressure. The main reason for the rise is that the distance from the peripheral reflection point is short, so that the reflected wave arrives at the systolic phase, not the diastolic. In addition, the vascular wall in the proximal aorta is rich in elastin, so the blood vessels have good extension, but as the peripheral arteries become more collagen and smooth muscle cells in the vessel wall, the blood vessels become stiff and the propagation speed of the pressure wave increases. As the body ages, the vascular wall becomes rigid due to arteriosclerosis. This change is prominent in the central elastic artery, causing systolic pressure to rise and pulse pressure to turn on, and the difference with the peripheral artery gradually disappears. As a result, the pulse pressure of the peripheral arteries is increased by about 50% in the younger than in the aorta, but is almost the same in the elderly.

In the measurement of PPG signals, Beer-Lambert's law describes the correlation of the projected light and the intensity of the transmitted light when light is projected at a given wavelength and passes through a homogeneous medium. do. This law uses the following equations (4) and (5) for the evaluation of the correlation for light transmitted from the vasoconstrictive circulation state at the fingertip at which the PPG signal is measured.

Equation 4 is an evaluation of blood and tissue, and Equation 5 is an evaluation of tissue. Where I ₀ , I, I _t are the intensity of the projected light, the light transmitted through blood and tissue, and the light transmitted through the tissue. ε _a , ε _v , ε _t are absorptions in arteries, veins, tissues, and the constants C _a , C _v , C _t are their concentrations, and V _a , V _v , V _t represent their volumes.

Dividing Equation 4 by Equation 5 yields Equation 6.

Where V is the total blood volume and ε is the mean absorption coefficient of the total blood. Thus V = V _a + V _v and ε = (ε _a V _a + ε _v V _v ) / V. C _a and C _v in Equation 4 represent the concentration of hemoglobin (hematocrit). The condition of C _v increases during mental stress, but the change is only a few percent. In conclusion, C _v and C _a can be thought of as being constant and equal to the average concentration of total blood C in normal circulation. Thus, C _a = C _v = C.

Arteries and veins of the hand are very sensitive to vasoconstrictive nerve stimulation, and there is no independent reflex and vasoconstriction. That means that changes in alpha-adrenergic activation can be thought of as appropriate for recognizing changes in the vascular state between arteries and veins at the fingertips. Therefore, when λ = V _v / V _a (ratio of arterial and venous blood volume), ε can be expressed as Equation 7 below.

In particular ε is not affected by changes correlated to blood volume. Therefore, the derivative of I / I _t corresponding to V in Equation 6 is expressed by the following Equation 8.

Equation 8 expresses the following equation 9.

The total blood volume consists of the mean and pulsating factors of the venous blood volume as well as the arterial blood volume. When the pulsation is observed only in the artery part, ΔI corresponding to ΔV is converted back to ΔV _a and ΔI _a in Equation (9). When the attenuation of transmitted light appears to lower the voltage in the actual PPG signal measurement, the values of ΔI _a and I have signs of (-) and (+), respectively. Therefore, -ΔI _a is already replaced by ΔI _a to have a positive value for ΔI _a in Equation (9).

1 is an absorption coefficient according to the wavelength of light of deoxyhemoglobin (Hb) and oxyhemoglobin (HbO ₂ ).

As shown in FIG. 1, when the red light passes through the oxyhemoglobin, the absorption rate is lower than that of the deoxyhemoglobin, and when the infrared light passes, the absorption rate is greater than that of the deoxyhemoglobin. This difference has been used as a basic theory to calculate oxygen saturation. Based on this theory, the absorbance is dependent on the transmission distance and the concentration of hemoglobin, and typically two red and infrared LEDs are selected to obtain oxygen saturation. It also undergoes a nonlinear calibration to calculate oxygen saturation through optical absorption. Absorption is dependent on hematocrit and blood volume. In addition, oxygen saturation depends on the anatomical differences of blood vessels and the difference in blood flow through the vessels. Absorption changes over time, with the highest values in the systole and the lowest in the diastolic. This is because blood fluctuations occur in blood vessels due to blood pressure. In other words, during the systolic period, red blood cells carry more oxygen hemoglobin to tissues. Therefore, in addition to the temporary volume increase of the absorbing tissue with the temporary increase in the amount of oxygen hemoglobin in the systolic phase, the voltage of the pulse wave pulse of the pulse oximeter transmitted through the absorbing dc component of the PPG signal and the arterial tissue is also temporarily Will increase. Thus, the output voltage of a typical pulse oximeter follows the waveform of blood pressure. Therefore, the pulse oximeter can basically calculate the heart rate. After correction, blood pressure can be calculated as well as oxygen saturation.

Looking at the characteristics of the PPG signal in the skin, it is absorbed by the arterial blood, venous blood, tissue, etc. in the light absorption of the skin, that is, when the light source is transmitted through the skin, the absorbed light is a waveform having a DC component and a pulsating component Is detected. As shown in FIG. 2, a waveform having a DC component and having a pulsation component having an amplitude AM is detected. The pulsating component is affected by the contraction and relaxation of the heart in the arterial vessels. This part reflects the maximum during the contraction of the heart and the minimum during relaxation. Therefore, in FIG. 2, the amplitude AM is referred to as a pulse wave signal (hereinafter referred to as PR), and the direct current component (DC) component is called a systolic blood volume signal (hereinafter referred to as PPG _SYS ). ) Can be referred to as the diastolic blood volume signal (hereinafter referred to as PPG _DIA ).

DC components, except pulsating components, reflect the absorption by arterial, venous, and tissue. Among these, the DC component caused by arterial blood vessels means blood remaining in blood vessels during cardiac relaxation and affects both light sources at the same ratio.

PPG signals measure the transmission of light through tissue as a function of time. Tissue blood volume increases during the systolic phase. The PPG signal therefore exhibits low light transmission, which also vibrates with the cardiac cycle. As shown in FIG. 2, the PPG signal has elements such as a baseline (hereinafter referred to as BL), an amplitude (hereinafter referred to as AM), and a period (hereinafter referred to as P). BL is inversely proportional to tissue blood volume, AM is proportional to tissue blood volume increase during systole, and P is the actual cardiovascular cycle. The baseline and amplitude of the PPG signal fluctuate mainly in the low frequency region, such as respiratory rate. This is because low-frequency fluctuations in the cardiac cycle are mainly controlled by the sympathetic nervous system. Fluctuations in finger blood volume (BL and AM) are caused by blood vessel contraction and relaxation in tissues significantly affected by the sympathetic nervous system. Low-frequency fluctuations in the BL and AM curves are due to automatic fluctuations in sympathetic nervous system activity. .

Looking at the relationship between temperature and pressure and PPG signal, Mendelson and Oaks, in 1988, tested the correlation between PPG signal and skin temperature and reported that the average pulsation amplitude decreased with increasing temperature. have. In addition, the pressure generated when a sensor attaches or measures a PPG signal on the sensor affects tissue perfusion. That is, when external pressure is generated on the finger or arm, the pressure constricts blood vessels. Because of this, blood volume is limited. Therefore, in order to obtain a meaningful PPG signal, the pressure at the measurement site must be applied with the least effect on the blood vessel.

Looking at the relationship between blood pressure and PPG signal, according to the hemodynamic law, pressure = resistance × cardiac output, the increase in blood pressure can be represented by increased peripheral blood vessel resistance and cardiac output. Takazawa suggested that the PPG signal is similar to the waveform of blood pressure and similar changes in the mechanism of blood vessel contraction and relaxation.

Based on the theoretical background described above, the blood pressure monitor of the present invention induces cardiac output and total peripheral resistance from the obtained PPG signal, from which the cardiovascular function and blood pressure are monitored from the PPG signal.

The technical problem to be achieved by the present invention is to provide a portable wireless terminal incorporating a blood pressure measurement system using a PPG signal.

Another technical problem to be achieved by the present invention is to provide a portable wireless terminal with a blood pressure measurement system that can be easily measured by the patient without using a cuff.

Another technical problem to be achieved by the present invention is to provide a portable wireless terminal incorporating a blood pressure measurement system using a more accurate PPG signal.

Another technical problem to be achieved by the present invention is to provide a portable wireless terminal having a blood pressure measurement system that can measure any part of the body's arterial system that can obtain a PPG signal.

Hereinafter, the configuration and operation of a portable wireless terminal incorporating a blood pressure measuring system using a PPG signal according to an embodiment of the present invention will be described in detail with reference to the accompanying drawings.

3 is a schematic block diagram illustrating a portable wireless terminal incorporating a blood pressure measuring system using a PPG signal according to an embodiment of the present invention. As shown in FIG. 3, the portable wireless terminal 100 having a blood pressure measurement system includes a PPG signal detector 1000, a temperature signal detector 2000, a pressure signal detector 3000, a data collection system 4200, and an operation processor 4400. ), Memory unit 4500, control unit 4600, key input unit 4700, display unit 4800, user I / F unit 4900, voice processor 5000, wireless unit 5100, coefficient setting unit 5200 ) That is, the portable wireless terminal 100 having a blood pressure measuring system detects a biological signal of a temperature, pressure, and optical blood flow measurement signal (hereinafter referred to as PPG), generates and outputs blood pressure information therefrom, and outputs the blood pressure information to the wireless station. It transmits to the designated manager computer 6300 via the 6000 and the network 6100. The manager computer 6300 may be a computer of a provider that provides a health care service, or may be a user's designated hospital computer.

The PPG signal detection unit 1000 includes a PPG sensing unit 1100 and a PPG detection control unit 1300, and detects the PPG and transmits the PPG to the data collection system 4200.

The PPG sensing unit 1100 includes a light emitting diode (hereinafter referred to as an LED) unit and an optical sensor, and detects light from which the light generated by the LED unit is transmitted or reflected from the tissue through the optical sensor.

The PPG detection control unit 1300 includes an LED driver and a PPG signal detection control unit, and drives the LED of the PPG sensing unit 1100 to detect the PPG signal from the output signal of the PPG sensing unit. This can be configured to pass the 0.05 ~ 20 Hz band of the PPG signal. In addition, a microcontroller may be used as the PPG detection controller 1300.

The temperature signal detector 2000 includes a temperature sensor 2100 and a temperature signal preprocessor 2300, and detects a temperature and transmits the temperature to the data collection system 4200.

The temperature sensing unit 2100 includes a temperature sensor and detects a temperature and converts it into an electrical signal.

The temperature signal preprocessor 2300 amplifies the signal output from the temperature sensor and removes noise.

The pressure signal detector 3000 includes a pressure sensor 3100 and a pressure signal preprocessor 3300, and detects a temperature and transmits the temperature to the data collection system 4200.

The pressure sensing unit 3100 includes a pressure sensor and detects a pressure and converts the pressure into an electrical signal.

The pressure signal preprocessor 3300 amplifies the signal output from the pressure sensing unit and removes noise.

The PPG sensing unit 1000, the temperature sensing unit 2100, and the pressure sensing unit 3100 constitute the living body signal detection unit 200.

The data collection system 4200 receives and outputs output signals of the PPG detection controller 1300, the temperature signal preprocessor 2300, and the pressure signal preprocessor 3300 into digital signals. A commercial data acquisition system can be used as the data acquisition system 4200.

When the pressure signal and the temperature signal received from the data collection system 4200 are respectively within the reference ranges, the arithmetic processing unit 4400 receives blood pressure values from the PPG signal, the pressure signal, and the temperature signal received from the data collection system 4200. Calculate The blood pressure information is stored in the memory unit 4500 and transmitted to the control unit 4600. The blood pressure value calculation process varies depending on whether the mode setting key (not shown) of the key input unit 4800 sets the temperature and pressure control mode, or sets the temperature and pressure non-control mode.

The memory unit 4500 stores a pressure reference signal, a temperature reference signal, a systolic blood volume reference signal, a diastolic blood volume reference signal, a blood pressure reference signal, a pulse wave reference signal, and correlation coefficients, and also stores blood pressure information received from the operation processor 4400. do.

The controller 4600 controls to display the blood pressure information received from the operation processor 4400 through the display unit 4700 or to output the blood pressure information to the speaker through the voice processor 5000, and also receives the blood pressure received from the operation processor 4400. Control to output information through the wireless unit 5100. The controller 4600 transmits a blood pressure measurement start command and a coefficient setting start command to the calculation processor 4400 through the key input unit 4700, and also sends the blood pressure measurement guide information to the speaker 5030 through the voice processor 500. Output or display on the display portion 4800.

The key input unit 4700 generates a blood pressure measurement start command and a coefficient setting start command according to the input key, and transmits the generated blood pressure measurement start command to the calculation processing unit 4400 through the control unit 4600. In addition, the key input unit 4700 is provided with a mode setting key (not shown) to select one of the temperature and pressure control mode, the temperature and pressure non-control mode. Here, the temperature and pressure control mode refers to a mode in which the temperature and pressure are controlled to be constant to a predetermined value, and the temperature and pressure non-control mode refers to a mode in which the temperature and pressure are not constant, that is, a variable mode.

The display unit 4800 receives and displays blood pressure information from the operation processor 4400 through the control unit. The display unit 4800 displays blood pressure measurement guide information and displays an error message when the temperature and pressure are not in the reference temperature and the reference pressure range.

The voice processing unit 5000 digitally processes the voice input by the microphone under the control of the control unit 4600 and transmits it to the wireless unit 5100 and demodulates the voice data received through the wireless unit 15 to output to the speaker 5030. do. In addition, the voice processor 5000 outputs blood pressure measurement guide information to the speaker 5030 under the control of the controller 4600.

The wireless unit 5100 modulates and converts the blood pressure information output from the control unit 4600 and transmits the frequency information as a wireless signal through an antenna, and separates a signal other than voice data from the wireless signal received through the antenna to convert the frequency into a frequency signal. And demodulate and transmit the demodulated data.

When the coefficient setting unit 5200 inputs a coefficient setting start command from the key input unit 4800 to the calculation processing unit 4400 through the control unit 4600, the coefficient setting unit 5200 may change the temperature and pressure from the user. Correlation coefficients are obtained through regression analysis by measuring the PPG signal and blood pressure, and storing them in the memory unit 4500 through the operation processor 4400. The correlation coefficients obtained by the coefficient setting unit 5200 include systolic blood pressure correlation coefficients (a _SYS , b _SYS , c _SYS ), which are correlation coefficients for blood pressure during systolic period, and diastolic blood pressure correlation coefficient, which is a correlation coefficient for blood pressure during diastolic period. (a _DIA , b _DIA , c _DIA ), systolic blood volume correlation coefficient (α _SYS , β _SYS , γ _SYS ), which is a correlation coefficient for blood volume signal during systolic period, and diastolic blood volume correlation coefficient, which is a correlation coefficient for blood volume signal during diastolic period (α _DIA , β _DIA , γ _DIA ), systolic pulse wave correlation coefficient (A _SYS , Β _SYS , Γ _SYS ), which is a correlation coefficient for pulse wave signals during systolic period, and diastolic pulse wave correlation coefficient, which is a correlation coefficient for pulse wave signals during diastolic phase (Α _DIA , Β _DIA , Γ _DIA ). The coefficient setting process of the coefficient setting unit 5200 depends on whether the mode setting key (not shown) of the key input unit 4700 sets the temperature and pressure control mode or sets the temperature and pressure non-control mode. In addition, the coefficient setting unit 5200 can be built-in or external, it can be detachable at the time of exterior.

Next, the operation processing of the operation processor 4400 will be described.

The calculation processing procedure of the calculation processing unit 4400 when the mode setting key of the key input unit 4700 is the temperature and pressure uncontrolled mode is as follows.

The operation processor 4400 determines whether the pressure signal and the temperature signal input from the data collection system 4200 are within a predetermined pressure reference range and temperature reference range, and when not within the pressure reference range and temperature reference range. The display unit 4600 notifies the blood pressure measurement to be repeated, that is, the PPG signal detection, the pressure signal detection, and the temperature signal detection again.

When the calculation processing unit is within the pressure reference range and the temperature reference range, the operation processing unit obtains the time intervals of the systolic and diastolic stages as shown in FIG. 2 from the PPG signal input from the data collection system 4200. From the temperature signal input from the data acquisition system 4200, the systolic temperature T _SYS and the diastolic temperature T _DIA , which are the temperatures of the systolic and diastolic time intervals, are obtained, and the data collection system 4200. The systolic pressure P _SYS and the diastolic pressure P _DIA , which are the pressures of the systolic and diastolic time intervals, are obtained from the pressure signal input from.

The calculation processor 4400 obtains the pulse wave signal PR by the equation (10).

PR = A _SYS T _SYS + Β _SYS P _SYS + Γ _SYS = Α _DIA T _DIA + Β _DIA P _DIA + Γ _DIA

In the systolic pulse wave correlation coefficients A _SYS , Β _SYS , and Γ _SYS , A _SYS and Β _SYS are positive real numbers and Γ _SYS is negative real numbers. In the diastolic pulse wave correlation coefficients A _DIA , Β _DIA and Γ _DIA , A _DIA and Β _DIA are positive real numbers and Γ _DIA is negative real numbers.

The calculation processing unit 4400 obtains the systolic blood volume signal PPG _SYS by Equation 11.

PPG _SYS = α _SYS T _SYS + β _SYS P _SYS + γ _SYS

Here, in the systolic blood volume correlation coefficients α _SYS , β _SYS , and γ _SYS , α _SYS is a negative real number, and β _SYS and γ _SYS are positive real numbers.

The calculation processor 4400 obtains the diastolic blood volume signal PPG _DIA by Equation 12.

PPG _DIA = α _DIA T _DIA + β _DIA P _DIA + γ _DIA

Here, in the diastolic blood volume correlation coefficients α _DIA , β _DIA , and γ _DIA , α _DIA is a negative real number, and β _DIA and γ _DIA are positive real numbers.

The calculation processing unit 4400 calculates the systolic blood pressure BP _SYS by the equation (13).

BP _SYS = a _SYS PPG _SYS + b _SYS PR + c _SYS

Here, for the systolic blood pressure correlation coefficients a _SYS , b _SYS and c _SYS , a _SYS and b _SYS are negative real numbers and c _SYS is a positive real number.

The calculation processor 4400 calculates the diastolic blood pressure BP _DIA by Equation 14.

BP _DIA = a _DIA PPG _DIA + b _DIA PR + c _DIA

Here, for diastolic blood pressure correlation coefficients a _DIA , b _DIA and c _DIA , a _DIA and b _DIA are negative real numbers and c _DIA is a positive real number.

That is, the systolic blood volume signal, the diastolic blood volume signal, and the pulse wave signal are calculated from Equations 10 to 14.

The systolic blood volume signal, the diastolic blood volume signal, and the pulse wave signal are detected from the PPG signal waveform input from the data collection system 4200. At this time, the systolic blood volume signal, the diastolic blood volume signal, and the pulse wave signal are detected in the PPG signal waveform as shown in FIG. 2, and the pulse wave signal is obtained from the amplitude (AM), and the systolic blood volume signal is obtained from the DC component (DC). Is obtained from the baseline BL.

The measured systolic blood volume signal, diastolic blood volume signal, and pulse wave signal values are determined to be equal to the systolic blood volume signal, diastolic blood volume signal, and pulse wave signal values calculated from Equations 10 to 14.

If the calculated values and the measured values are the same, the diastolic blood pressure and the systolic blood pressure obtained from Equations 10 to 14 are output as blood pressure values.

If the calculated values are different from the measured values, the normalized systolic blood volume signal, diastolic blood volume signal, pulse wave signal by normalizing the measured systolic blood volume signal, diastolic blood volume signal, and pulse wave signal by the preset temperature and pressure. Then, the diastolic and systolic blood pressures are recalculated using the obtained values and output as blood pressure values.

Next, the operation processing of the operation processing unit 4400 when the mode setting key of the key input unit 4700 is the temperature and pressure control mode is as follows.

The operation processor 4400 determines whether the pressure signal and the temperature signal input from the data collection system 4200 are within a predetermined pressure reference range and temperature reference range, and when not within the pressure reference range and temperature reference range. The display unit 4600 notifies the measurement of blood pressure by changing the measurement position, pressure, and the like.

The calculation processing unit detects the systolic blood volume signal, the diastolic blood volume signal, and the pulse wave signal from the PPG signal waveform input from the data collection system 4200 when it is within the pressure reference range and the temperature reference range. At this time, the systolic blood volume signal, the diastolic blood volume signal, and the pulse wave signal are detected in the PPG signal waveform as shown in FIG. 2, and the pulse wave signal is obtained from the amplitude (AM), and the systolic blood volume signal is obtained from the DC component (DC). Is obtained from the baseline BL.

Using the detected systolic blood volume signal, diastolic blood volume signal, and pulse wave signal, systolic blood pressure BP _SYS and diastolic blood pressure BP _DIA obtained by equations (13) and (14) are output as blood pressure values.

FIG. 4 is a block diagram illustrating the PPG signal detecting unit 1000 of FIG. 3. The PPG sensing unit 1100 including the LED unit 1150 and the optical sensor 1200, the LED driving unit 1400, and the PPG signal front are shown. A PPG detection control unit 1300 having a processing unit 1450 is included.

The PPG sensing unit 1100 includes an LED unit 1150 and an optical sensor 1200. The PPG sensing unit 1100 detects light from the LED unit 1150 transmitted or reflected from the tissue.

The LED unit 1150 is driven by the LED driving unit 1400 of the PPG detection control unit 1300 and consists of two light emitting diodes (LEDs) for outputting and irradiating two lights having different wavelengths. The LED unit 1150 may use each light emitting diode (LED) that outputs light having a red wavelength and a near infrared wavelength.

The optical sensor 1200 detects two light transmitted or reflected and converts the light into an electrical signal, that is, a current signal. The optical sensor 1200 may be configured as a photodiode. The optical sensor 1200 may be configured as a photodiode capable of detecting a red wavelength and a near infrared wavelength.

The PPG detection controller 1300 includes an LED driver 1400 and a PPG signal preprocessor 1450, and controls the PPG signal to apply a constant current to each wavelength band of two LEDs of the LED unit 1150. To detect.

The LED driver 1400 applies a constant current to each wavelength band of the two LEDs of the LED unit 1150. Current control is added during LED driving to make the DC value of the signal measured in two channels constant.

The PPG signal preprocessor 1450 includes a current-to-voltage converter 1500, a PPG preamplifier 1600, a demodulator 1700, and a filter unit 1750. The PPG signal preprocessor 1450 appropriately applies the electric signal input from the optical sensor 1200. Adjust to gain and amplify, then remove surrounding artifacts.

The current-voltage converter 1500 converts a current signal input from the optical sensor 1200 into a voltage signal.

The PPG preamplifier 1600 is configured as a differential amplifier to amplify the signal output from the current-voltage converter 1500 through the differential amplifier.

The demodulator 1700 separates a signal input from the PPG preamplifier 1600 into an ambient signal and a signal for each wavelength.

The filter unit 1750 includes a red light filter unit 1800 and an infrared filter unit 1900, and separates an ambient signal for each wavelength-specific signal output by being separated by the demodulator 1700 to generate an ambient artifact. The artifacts are removed, and an optical blood flow measurement signal (PPG) having only an AC component is obtained and transmitted to the data collection system 4200 through DC filtering and AC gain control.

The red light filter unit 1800 removes the peripheral artifacts by subtracting the peripheral signal from the red light signal separated from the demodulator 1700 and obtains the red light PPG signal having only an AC component through DC filtering and AC gain control.

The infrared filter unit 1900 removes the peripheral artifacts by subtracting the peripheral signal from the infrared signal output from the demodulator 1700 and obtains an infrared PPG signal having only an AC component through DC filtering and AC gain control.

FIG. 5 is an example of an attachment position of the PPG sensing unit of FIG. 4 in a finger. FIG.

When the PPG sensing unit 1100 is worn, a cross-sectional view of a finger is shown. The finger artery is located near the skin surface, horizontal to the length of the finger. There are two ways to locate the light sensor and LED in the PPG sensing unit. As shown in (a) of FIG. 5, both the optical sensor and the LED may be placed on the same surface to obtain a reflective PPG signal. As shown in (b) of FIG. A transparent PPG signal can be obtained.

6 is an example of an attachment position on the finger of the PPG sensing unit, the pressure sensing unit, and the temperature sensing unit of FIG. 3. In FIG. 6, the optical sensor and the LED are positioned opposite to each other as shown in FIG. 5 (b), and the temperature sensor is positioned so as to contact the bottom of the finger without overlapping the LED, and the pressure at the bottom as the finger is pressed. Position the pressure sensor so that the sensor is pressed. In the present invention, the mounting position of the PPG sensing unit, the pressure sensing unit, and the temperature sensing unit is not limited thereto, and various applications are possible without departing from the spirit of the present invention.

FIG. 7 is a schematic block diagram illustrating the coefficient setting unit of FIG. 3, including a pressure measuring unit 5300, a temperature measuring unit 5400, a blood pressure measuring unit 5500, a PPG measuring unit 5600, and a coefficient calculating unit 5700. It is provided.

The pressure measuring unit 5300 measures the pressure applied from the user measuring part.

The temperature measuring unit 5400 measures the temperature of the user measuring portion.

The blood pressure measuring unit 5500 includes a non-invasive blood pressure (NIBP) separate to measure blood pressure of the user separately. That is, the blood pressure measuring unit 5500 measures the temperature and pressure at the pressure measuring unit 5300 and the temperature measuring unit 5400 and simultaneously measures the blood pressure. As a result, blood pressure can be measured according to changes in temperature and pressure. At this time, the PPG measurement unit 5600 simultaneously measures the PPG signal. As an extracorporeal blood pressure monitor (NIBP), an oscillometric blood pressure monitor or a stethoscope can be used.

The PPG measuring unit 5600 measures the temperature and pressure at the pressure measuring unit 5300 and the temperature measuring unit 5400 and simultaneously measures the PPG signal. This allows the PPG signal to be measured as temperature and pressure changes. At the same time, blood pressure is also measured.

The coefficient calculating unit 5700 receives pressure, temperature, blood pressure, and PPG signals simultaneously measured from the pressure measuring unit 5300, the temperature measuring unit 5400, the blood pressure measuring unit 5500, and the PPG measuring unit 5600, and counting them. Obtain systolic blood pressure, diastolic blood pressure, and pulse wave according to temperature or pressure change from the PPG signal received by the calculation unit 5700, and together with the systolic and diastolic blood pressure values according to the temperature or pressure change inputted from the blood pressure measuring unit 5200. Through regression analysis (regression analysis), each correlation coefficient, namely systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ), diastolic blood pressure correlation coefficient (a _DIA , b _DIA , c _DIA ), systolic blood volume correlation coefficient ( α _SYS , β _SYS , γ _SYS ), diastolic blood volume correlation coefficient (α _DIA , β _DIA , γ _DIA ), systolic pulse wave correlation coefficient (Α _SYS , Β _SYS , Γ _SYS ), diastolic pulse wave correlation coefficient (Α _DIA , Β _DIA , Γ _DIA ).

FIG. 8 is a flowchart for explaining an operation of the coefficient setting unit of FIG. 7 in temperature and pressure control.

When the mode setting key of the key input unit 4800 is set to the temperature and pressure control mode, and the coefficient setting start command is input from the key input unit 4700, the coefficient setting unit 5200 starts an operation.

It is determined whether the pressure signal input from the pressure measuring unit 5300 is within a predetermined reference range (S3100). If the pressure signal is within the reference range, the predetermined temperature signal input from the temperature measuring unit 5400 is preset. It is determined whether it is within the standard range of (S3200).

If the temperature and pressure are within a predetermined reference range, it is determined whether to correct the coefficient setting (S3300), and when not correcting the coefficient setting, coefficient setting according to the existing regression equation is performed (S3400). That is, when the coefficient setting is not corrected, the systolic blood volume signal (PPG _SYS ), the diastolic blood volume signal (PPG _DIA ), and pulse wave defined by the user's height, finger circumference, weight, sex, and age inputted by the user interface By the signal PR, the coefficients used in Equations 13 and 14 are obtained through regression analysis and stored in the memory unit 4500 through the operation processor 4400.

When correcting the coefficient setting, the blood pressure (BP) measured by the blood pressure measuring unit 5500 is measured, and the PPG measuring unit 5600 measures the PPG signal, and the systolic blood volume signal ( PPG _SYS ), the diastolic blood volume signal PPG _DIA , and the pulse wave signal PR are detected (S3500). At this time, as shown in FIG. 2 in the PPG signal waveform, the pulse wave signal PR is obtained by the amplitude AM, the systolic blood volume signal PPG _SYS is obtained by the DC component, and the diastolic blood volume signal PPG _DIA is the baseline. Obtained by (BL).

Reference blood pressure, reference systolic blood volume signal PPG _SYS , reference diastolic blood volume signal PPG _DIA , and reference pulse wave signal PR are set (S3600). Here, the reference blood pressure refers to the reference systolic blood pressure and the reference diastolic blood pressure.

The reference blood pressure value BP, the reference systolic blood volume signal PPG _SYS , the reference diastolic blood volume signal PPG _DIA , and the reference pulse wave signal PR are stored in the memory unit 4500 (S3700).

Multiple regression analysis was performed on the coefficients used in Equations 13 and 14 from the blood pressure values (constrictor blood pressure, diastolic blood pressure), systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), and pulse wave signal (PR). Obtain through and store in the memory unit 4500 (S3800). That is, systolic blood pressure correlation coefficients (a _SYS , b _SYS , c _SYS ) and diastolic blood pressure correlation coefficients (a _DIA , b _DIA , c _DIA ) are obtained and stored in the memory unit 4500.

FIG. 9 is a flowchart for explaining an operation of a coefficient setting unit of FIG. 7 when temperature and pressure are not controlled.

When the mode setting key of the key input unit 4700 is set to the temperature and pressure uncontrolled mode, and the coefficient setting start command is input from the key input unit 4700, the coefficient setting unit 5200 starts operation.

It is determined whether the pressure signal input from the pressure measuring unit 5300 is within a predetermined reference range (S4100). If the pressure signal is within the reference range, the predetermined temperature signal input from the temperature measuring unit 5400 is preset. It is determined whether the reference range is within (S4200).

If the temperature and pressure are within a predetermined reference range, the temperature and pressure is measured for a predetermined time (S4300).

It is determined whether to correct the coefficient setting (S4400). If the coefficient setting is not corrected, the coefficient setting according to the existing regression equation is performed (S4500). That is, when the coefficient setting is not corrected, the systolic blood volume signal (PPG _SYS ), the diastolic blood volume signal (PPG _DIA ), and the pulse wave signal defined by the user's height, finger circumference, weight, gender, and age input by the user interface By (PR), each coefficient used in Equations 10 to 14 is obtained through regression analysis and stored in the memory unit 4500.

When correcting the coefficient setting, the blood pressure BP measured by the blood pressure measuring unit 5200, the temperature by the temperature measuring unit 5400, the pressure by the pressure measuring unit 5300, and the PPG by the PPG measuring unit 5300 are measured. The signal is measured and the systolic blood volume signal PPG _SYS , the diastolic blood volume signal PPG _DIA , and the pulse wave signal PR are detected from the measured PPG signal waveform (S4600). That is, in the PPG signal waveform, as shown in FIG. 2, the pulse wave signal PR is from amplitude AM, the systolic blood volume signal PPG _SYS is from the DC component, and the diastolic blood volume signal PPG _DIA is from the baseline BL. Obtain

Reference blood pressure, reference systolic blood volume signal (PPG _SYS ), reference diastolic blood volume signal (PPG _DIA ), and reference pulse wave signal (PR) are set (S4700). Here, the reference blood pressure refers to the reference systolic blood pressure and the reference diastolic blood pressure.

The reference blood pressure value BP, the reference systolic blood volume signal PPG _SYS , the reference diastolic blood volume signal PPG _DIA , and the reference pulse wave signal PR are stored in the memory unit 4500 (S4800).

From the blood pressure values (constrictor blood pressure, diastolic blood pressure), temperature, pressure, systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), pulse wave signal (PR), the respective coefficients used in Equations 10 to 14 Obtained through the regression analysis and stored in the memory unit (500) (S4900). That is, systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ), diastolic blood pressure correlation coefficient (a _DIA , b _DIA , c _DIA ), systolic blood volume correlation coefficient (α _SYS , β _SYS , γ _SYS ), diastolic blood volume correlation _Obtain coefficients (α _DIA , β _DIA , γ _DIA ), systolic pulse wave correlation coefficients (Α _SYS , Β _SYS , Γ _SYS ), and diastolic pulse wave correlation coefficients (Α _DIA , Β _DIA , Γ _DIA ) and store them in the memory unit 4500. do.

FIG. 10 is a schematic flowchart of obtaining systolic blood pressure and diastolic blood pressure in the calculation processor of FIG. 3 during temperature and pressure control. FIG. 10 shows a flowchart of the calculation processing unit 4400 when the mode setting key of the key input unit 4700 is set to the temperature and pressure control mode and a blood pressure measurement start command is input from the key input unit 4800.

It is determined whether the pressure signal input from the data collection system 4200 is within a predetermined reference range (S100). If the pressure signal is within the reference range, the predetermined temperature signal input from the data collection system 4200 is preset. It is determined whether the reference range is within (S130).

If the temperature signal is within a predetermined reference range, the calculation processing unit 4400 receives the PPG signal measured by the PPG signal detection unit 1000 through the data collection system 4200 (S200), and the systolic machine from the measured PPG signal waveform. The blood volume signal PPG _SYS , the diastolic blood volume signal PPG _DIA , and the pulse wave signal PR are detected (S300). That is, in the PPG signal waveform, as shown in FIG. 2, the pulse wave signal PR is from amplitude AM, the systolic blood volume signal PPG _SYS is from the DC component, and the diastolic blood volume signal PPG _DIA is from the baseline BL. Obtain

The operation processor 4400 reads correlation coefficients from the memory unit 4500 (S400). That is, the systolic blood pressure correlation coefficients (a _SYS , b _SYS , c _SYS ) and the diastolic blood pressure correlation coefficients (a _DIA , b _DIA , c _DIA ) are read from the memory unit 4500.

Systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), pulse wave signal (PR), and systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ) detected from the measured PPG signal waveform, diastolic blood pressure correlation Using the coefficients (a _DIA , b _DIA , c _DIA ), systolic and diastolic blood pressures are obtained by using Equations 13 and 14 (S500).

FIG. 11 is a schematic flowchart of calculating systolic blood pressure and diastolic blood pressure in the calculation processor of FIG. 3 when temperature and pressure are not controlled. FIG. 11 shows a flowchart of the calculation processing unit 4400 when the mode setting key of the key input unit 4700 is set to the temperature and pressure uncontrolled mode and a blood pressure measurement start command is input from the key input unit 4700.

It is determined whether the pressure signal input from the data collection system 4200 is within a predetermined reference range (S1100). If the pressure signal is within the reference range, the predetermined temperature signal input from the data collection system 4200 is preset. It is determined whether the reference range is within (S1130).

If the temperature signal is within a predetermined reference range, the calculation processing unit 4400 reads correlation coefficients from the memory unit 4500 (S1170). That is, the systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ), the diastolic blood pressure correlation coefficient (a _DIA , b _DIA , c _DIA ), and the systolic blood volume correlation coefficient (α _SYS , β _SYS , γ) from the memory unit 4500. _SYS ), diastolic blood volume correlation coefficient (α _DIA , β _DIA , γ _DIA ), systolic pulse wave correlation coefficient (Α _SYS , Β _SYS , Γ _SYS ), diastolic pulse wave correlation coefficient (Α _DIA , Β _DIA , Γ _DIA ) (S170).

The operation processor 4400 obtains a time interval between the systolic and diastolic phases from the PPG signal input from the data collection system 4200 (S1200).

The systolic temperature T _SYS and the diastolic temperature T _DIA , which are the temperatures of the systolic and diastolic time intervals, are obtained from the temperature signal input from the data collection system 4200 (S1250).

From the pressure signal input from the data acquisition system 4200, the systolic pressure P _SYS and the diastolic pressure P _DIA , which are the pressures of the systolic and diastolic time sections, are obtained (S1300).

With the systolic pulse wave correlation coefficient (Α _SYS , Β _SYS , Γ _SYS ), systolic temperature (T _SYS ), systolic pressure (P _SYS ), the pulse wave signal (PR) can be obtained by Equation 10, or the diastolic pulse wave correlation coefficient ( A _DIA , Β _DIA , Γ _DIA ), a diastolic temperature (T _DIA ), and a diastolic pressure (P _DIA ) are used to obtain a pulse wave signal PR by Equation 10 (S1350).

Systolic blood volume correlation coefficients (α _SYS , β _SYS , γ _SYS ), systolic temperature (T _SYS ), systolic pressure (P _SYS ), and the systolic blood volume signal (PPG _SYS ) is calculated by Equation 11 (S1400).

The diastolic blood volume correlation coefficient (α _DIA , β _DIA , γ _DIA ), the diastolic temperature (T _DIA ), and the diastolic pressure (P _DIA ) are obtained using Equation 12 to obtain a diastolic blood volume signal (PPG _DIA ) (S1450).

The systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ), the systolic blood volume signal (PPG _SYS ), and the pulse wave signal (PR) are used to calculate the systolic blood pressure (BP _SYS ) by Equation 13 (S1500).

The diastolic blood pressure correlation coefficient (a _DIA , b _DIA , c _DIA ), the diastolic blood volume signal (PPG _DIA ), and the pulse wave signal (PR) are calculated using Equation 14 to obtain a diastolic blood pressure (BP _DIA ).

The systolic blood volume signal PPG _SYS , the diastolic blood volume signal PPG _DIA , and the pulse wave signal PR are detected from the PPG signal waveform input from the data collection system 4200 (S1600). That is, in the PPG signal waveform, as shown in FIG. 2, the pulse wave signal PR is obtained by the amplitude AM, the systolic blood volume signal PPG _SYS is obtained by the DC component, and the diastolic blood volume signal PPG _DIA is the baseline ( BL).

Determine if the calculated values are the same as the measured values. That is, the calculated systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), pulse wave signals (PR) measured systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), pulse wave signals (PR) and It is determined whether or not the same (S1650). In other words, it is determined whether the values (calculated values) obtained in S1350 to S1550 and the values (measured values) obtained in S1600 are the same.

If the calculated values and the measured values are the same, the diastolic blood pressure and the systolic blood pressure calculated in S1500 to S1550 are output as blood pressure values (S1700). Alternatively, the previously set blood pressure value is output.

If the calculated values and the measured values are different from each other, the measured systolic blood volume signal (PPG _SYS ), the diastolic blood volume signal (PPG _DIA ), and the pulse wave signal (PR) are normalized by the preset temperature and pressure. The systolic blood volume signal (PPG _SYS ), the diastolic blood volume signal (PPG _DIA ), the pulse wave signal (PR) are obtained (S1800), and the diastolic blood pressure and the systolic blood pressure are again calculated using the obtained values (S1850).

12A, 12B and 12C illustrate an embodiment of a portable wireless terminal incorporating a blood pressure measuring system using a PPG signal according to the present invention. 12A illustrates that the biosignal detection unit 200 is located below the key input unit 4700 when the portable wireless terminal is a mobile phone. 12B illustrates a case in which the biosignal detection unit 200 is positioned on the top surface of the portable wireless terminal cover. 12C illustrates a case in which the biosignal detection unit 200 is located at the side of the main body of the portable wireless terminal. In addition, the portable wireless terminal incorporating the blood pressure measuring system of FIGS. 12A, 12B, and 12C includes a port 5230 for connecting the coefficient setting unit 5200.

12A, 12B, and 12C are exemplary embodiments of the portable wireless terminal incorporating the blood pressure measuring system according to the present invention. Thus, the position of the biosignal detection unit 200 in the portable wireless terminal is not limited, and the present invention is not limited thereto. It is possible to make changes within the scope of the subject matter. The biosignal detection unit 200 of the portable wireless terminal of the present invention may be inserted or positioned in an external or internal form in any part of the main body of the portable secondary terminal.

The present invention is not limited to the above described and illustrated in the drawings, and of course, more modifications and variations are possible to those skilled in the art within the scope of the following claims.

As described above, the present invention provides a portable wireless terminal incorporating a blood pressure measuring system using a PPG signal with higher accuracy, and a portable wireless terminal incorporating the blood pressure measuring system of the present invention does not use a cuff and the patient It is easy to measure blood pressure, and it can be measured at any part of the human arterial system that can obtain PPG signal.

In addition, the blood pressure monitor of the present invention can measure blood pressure more accurately by considering the influence of temperature and pressure when measuring blood pressure using a PPG signal, and can obtain information on cardiovascular function as well as blood pressure measurement.

In recent years, people often carry a portable wireless terminal such as a mobile phone or a PDA in everyday life, and the portable wireless terminal with the blood pressure measuring system of the present invention has a blood pressure check time in a portable wireless terminal such as a mobile phone or a PDA. If you check your blood pressure according to the alarm, you will be able to manage your blood pressure more conveniently and regularly.

Claims (35)

In a portable wireless terminal incorporating a blood pressure measurement system that detects a PPG (optical blood flow measurement signal) signal, generates blood pressure information, and transmits the blood pressure information to a designated administrator computer via a wireless station and a network. A PPG signal detection unit including an LED (light emitting diode) unit and an optical sensor to detect a PPG (optical blood flow measurement signal) signal; A temperature signal detector having a temperature sensor to detect a temperature signal; A pressure signal detection unit having a pressure sensor to detect a pressure signal; A data acquisition system for receiving output signals of the PPG signal detector, the temperature signal detector, and the pressure signal detector and converting them into digital signals; An arithmetic processing unit for calculating a blood pressure value from the PPG signal, the pressure signal, and the temperature signal received from the data collection system when the pressure signal and the temperature signal received from the data collection system are respectively within predetermined reference ranges; And a key input unit for generating a blood pressure measurement start command. In a portable wireless terminal incorporating a blood pressure measurement system that detects a PPG (optical blood flow measurement signal) signal, generates blood pressure information, and transmits the blood pressure information to a designated administrator computer via a wireless station and a network. LEDs (light emitting diodes); Optical sensor; A PPG detection control unit for detecting a PPG signal from the output signal of the optical sensor; A data acquisition system for receiving output signals of the PPG detection control unit and converting the output signals into digital signals; An arithmetic processing unit for calculating a blood pressure value from the PPG signal received from the data collection system; A control unit which controls to output the blood pressure value received from the calculation processing unit through a wireless unit; A display unit for receiving and displaying blood pressure information from the operation processor through the control unit; Modulation and frequency conversion of the blood pressure information output from the control unit is transmitted as a wireless signal through an antenna, and a radio frequency signal is separated from the radio signal received through the antenna other than the data and the frequency conversion and demodulation and transmitted to the control unit wireless Portable wireless terminal having a blood pressure measuring system, characterized in that it comprises at least. In a portable wireless terminal having a blood pressure measuring system for detecting a PPG (optical blood flow measurement signal) signal, a pressure signal, and a temperature signal to obtain a blood pressure value and transmit it to a designated administrator computer via a wireless station and a network. When the detected pressure signal and temperature signal are respectively within the standard ranges, Systolic blood pressure (BP _SYS ), systolic blood volume signal (PPG _SYS ), pulse wave signal (PR), systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ) BP _SYS = a _SYS PPG _SYS + b _SYS PR + c _SYS Obtained by Diastolic blood pressure (BP _DIA ), diastolic blood volume signal (PPG _DIA ), pulse wave signal (PR), diastolic blood pressure correlation coefficient (a _DIA , b _DIA , c _DIA ) BP _DIA = a _DIA PPG _DIA + b _DIA PR + c _DIA A portable wireless terminal incorporating a blood pressure measuring system, characterized in that it comprises at least a calculation processing unit obtained by. The method of claim 3, In the systolic blood pressure correlation coefficients a _SYS , b _SYS , and c _SYS , a _SYS and b _SYS have negative values and c _SYS has a positive value, The diastolic blood pressure correlation coefficient a _DIA , b _DIA , c _DIA , a _DIA , b _DIA has a negative value and c _DIA has a positive value, characterized in that a portable wireless terminal with a blood pressure measuring system. The method of claim 2, The portable wireless terminal incorporating the blood pressure measuring system And a temperature signal detector for detecting a temperature signal, and a pressure signal detector for detecting a pressure signal. And the calculation processing unit further includes pressure and temperature range determination means for determining whether the temperature signal and the pressure signal detected by the temperature signal detection unit and the pressure signal detection unit are within a predetermined pressure reference range and a temperature reference range. Portable wireless terminal with a built-in blood pressure measurement system. The method according to claim 1 or 3 or 5, The portable wireless terminal incorporating the blood pressure measuring system A portable wireless terminal having a blood pressure measurement system further comprising a coefficient setting unit for measuring the PPG signal and blood pressure according to temperature and pressure changes, and obtaining correlation coefficients through regression analysis. The method of claim 6, The coefficient setting unit has a systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ) which is a correlation coefficient for blood pressure during systolic period, and a diastolic blood pressure correlation coefficient (a _DIA , b _DIA , c _{DIA which} is a correlation coefficient for blood pressure during diastolic period). ), Systolic blood volume correlation coefficient (α _SYS , β _SYS , γ _SYS ), which is a correlation coefficient for blood volume signals during systolic period, and diastolic blood volume correlation coefficient (α _DIA , β _DIA , γ _DIA ), which is a correlation coefficient for blood volume signals during diastolic period ), Systolic pulse wave correlation coefficient (Α _SYS , Β _SYS , Γ _SYS ), which is the correlation coefficient for pulse wave signals during systolic period, and diastolic pulse wave correlation coefficient (Α _DIA , Β _DIA , Γ _DIA , which is the correlation coefficient for pulse wave signals during diastolic _phase Portable wireless terminal having a blood pressure measuring system, characterized in that obtaining at least one of. The method of claim 6, A portable wireless terminal incorporating a blood pressure measuring system, characterized in that the coefficient setting unit is built-in. The method of claim 6, The coefficient setting unit is a portable wireless terminal with a built-in blood pressure measuring system, characterized in that the external. The method of claim 1, The optical sensor, the temperature sensor, the pressure sensor is a portable wireless terminal incorporating a blood pressure measuring system, characterized in that the external portion is external to a predetermined portion of the portable wireless terminal. The method of claim 1, The optical sensor, the temperature sensor, the pressure sensor is a portable wireless terminal with a built-in blood pressure measuring system, characterized in that embedded in a predetermined portion of the portable wireless terminal. The method of claim 1, A portable wireless terminal incorporating a blood pressure measuring system, characterized in that the position of the optical sensor and the LED unit are both on the same side when viewed from the arterial position of the portion to be measured. The method of claim 1, And the optical sensor and the LED unit are opposite to each other when viewed from an artery position of a portion to be measured. The method of claim 13, The temperature sensor is positioned so as not to overlap with the LED part and in contact with the measurement part; The pressure sensor is a portable wireless terminal with a built-in blood pressure measuring system, characterized in that the position to measure the pressure applied as the measuring portion is pressed in contact with the temperature sensor. The method according to claim 1 or 3 or 5, The operation processing unit A systolic and diastolic time period setting means for obtaining a systolic and diastolic time interval from the PPG signal input from the data collection system if it is determined by the pressure and temperature range determining means that the pressure and temperature are within a reference range; Systolic and diastolic temperature setting means for obtaining a systolic temperature (T _SYS ) and a diastolic temperature (T _DIA ), which are temperatures in a time interval between the systolic and diastolic, from a temperature signal input from the data collection system; And a systolic and diastolic pressure setting means for obtaining systolic pressure (P _SYS ) and diastolic pressure (P _DIA ), which are pressures of the systolic and diastolic time sections, from the pressure signal input from the data collection system. Portable wireless terminal with a blood pressure measuring system. The method of claim 15, The calculation processing unit outputs a pulse wave signal PR PR = A _SYS T _SYS + Β _SYS P _SYS + Γ _SYS or PR = Α _DIA T _DIA + Β _DIA P _DIA + Γ _DIA Obtained by Wherein A _SYS , Β _SYS , and Γ _SYS are systolic pulse wave correlation coefficients, and A _DIA , Β _DIA and Γ _DIA are diastolic pulse wave correlation coefficients. The method of claim 16, In the systolic pulse wave correlation coefficients A _SYS , Β _SYS and Γ _SYS , A _SYS and Β _SYS have positive values and Γ _SYS has negative values, The diastolic pulse wave correlation coefficients Α _DIA , Β _DIA , Γ _DIA , Α _DIA , Β _DIA have a positive value, and Γ _DIA have a negative value. The method of claim 16, The calculation processing unit outputs a systolic blood volume signal (PPG _SYS ). PPG _SYS = α _SYS T _SYS + β _SYS P _SYS + γ _SYS Obtained by Diastolic blood volume signal (PPG _DIA ) PPG _DIA = α _DIA T _DIA + β _DIA P _DIA + γ _DIA Obtained by Wherein α _SYS , β _SYS , and γ _SYS are systolic blood volume correlation coefficients, and α _DIA , β _DIA and γ _DIA are diastolic blood volume correlation coefficients. The method of claim 18, In the systolic blood volume correlation coefficients α _SYS , β _SYS , and γ _SYS , α _SYS has a negative value and β _SYS , γ _SYS has a positive value, The diastolic blood volume correlation coefficients α _DIA , β _DIA , and γ _DIA have α _DIA , and β _DIA and γ _DIA have positive values. The method of claim 18, The calculation processing unit may be the systolic blood pressure (BP _SYS ) BP _SYS = a _SYS PPG _SYS + b _SYS PR + c _SYS Obtained by Diastolic blood pressure (BP _DIA ) BP _DIA = a _DIA PPG _DIA + b _DIA PR + c _DIA Obtained by Where a _SYS , b _SYS and c _SYS are systolic blood pressure correlation coefficients, a _DIA , b _DIA and c _DIA are diastolic blood pressure correlation coefficients, PPG _SYS is systolic blood volume signal, PPG _DIA is diastolic blood volume signal, and PR is pulse wave Portable wireless terminal with a blood pressure measuring system, characterized in that the signal. The method of claim 20, In the systolic blood pressure correlation coefficients a _SYS , b _SYS , and c _SYS , a _SYS and b _SYS have negative values and c _SYS has a positive value, The diastolic blood pressure correlation coefficient a _DIA , b _DIA , c _DIA , a _DIA , b _DIA has a negative value and c _DIA has a positive value, characterized in that a portable wireless terminal with a blood pressure measuring system. The method of claim 5, When it is determined in the pressure and temperature range determination means that the pressure or temperature is not within the pressure reference range or the temperature reference range, A portable wireless terminal incorporating a blood pressure measuring system, characterized in that for indicating the occurrence of an error when detecting the blood pressure in the display unit. In the blood pressure measuring method of a portable wireless terminal with a built-in blood pressure measuring system, Detecting a PPG (optical blood flow measurement signal) signal from an optical sensor, detecting a temperature signal from a temperature sensor, and detecting a pressure signal from a pressure sensor; A data collection step of receiving a temperature signal, a pressure signal, and a PPG signal, which are output signals of the biosignal detection step, respectively and converting the signal into a digital signal; Calculating a blood pressure value from the PPG signal, the pressure signal, and the temperature signal received from the data collection step, when the pressure signal and the temperature signal received from the data collection step are respectively within predetermined reference ranges; Blood pressure measurement method in a portable wireless terminal with a blood pressure measuring system, characterized in that it comprises at least. A PPG detection step of detecting a PPG signal from the optical sensor; A data collection step of receiving the output signals of the PPG detection step and converting the output signals into a digital signal; Calculating a blood pressure information from the PPG signal received from the data collecting step; A wireless transmission step of modulating and frequency converting the blood pressure information obtained in the operation processing step and transmitting the same as a wireless signal through an antenna; A display step of displaying blood pressure information obtained in the calculation processing step; And a step of transmitting the signal transmitted in the wireless transmission step to a manager for transmitting to a designated manager computer via a wireless station and a network. At least, the blood pressure measuring method in a portable wireless terminal incorporating a blood pressure measuring system. A PPG signal detection step of detecting a PPG (optical blood flow measurement signal); A data collection step of receiving the PPG signal detected in the PPG signal detection step and converting the signal into a digital signal; In the blood pressure measurement method in a portable wireless terminal with a blood pressure measurement system comprising; calculating a blood pressure value from the PPG signal received from the data collection step; The operation processing step, Systolic blood pressure signal (PPG _SYS ), pulse wave signal (PR), systolic blood pressure correlation coefficient (a _SYS , b _SYS , c _SYS ) output in the coefficient setting step is used to calculate the systolic blood pressure (BP _SYS ) BP _SYS = a _SYS PPG _SYS + b _SYS PR + c _SYS Obtained by The diastolic blood pressure (BP _DIA ) is obtained using the diastolic blood volume signal (PPG _DIA ), the pulse wave signal (PR), and the diastolic blood pressure correlation coefficient (a _DIA , b _DIA , c _DIA ) inputted from the memory. BP _DIA = a _DIA PPG _DIA + b _DIA PR + c _DIA Blood pressure measurement method in a portable wireless terminal, characterized in that it comprises a systolic and diastolic blood pressure detection step obtained by. The method of claim 25, The systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), pulse wave signal (PR) is Blood pressure measurement method in a portable wireless terminal, characterized in that for detecting the systolic blood volume signal, diastolic blood volume signal, pulse wave signal from the waveform of the PPG signal measured in the data collection step. The method according to claim 23 or 24 or 25, The blood pressure measurement method includes a temperature signal detection step for detecting a temperature signal, a pressure signal detection step for detecting a pressure signal, and a coefficient setting for obtaining correlation coefficients through regression analysis by measuring the PPG signal and blood pressure according to temperature and pressure change. More steps, The data collection step further includes a digital signal conversion step of receiving a temperature signal and a pressure signal detected in the pressure signal detection step and converting the pressure signal into a digital signal and a digital signal. Blood pressure measurement The method of claim 27, The operation processing step, A pressure reference range determination step of determining whether the pressure signal converted into the digital signal in the data collection step is within a predetermined reference range; A temperature reference range determination step of determining whether a temperature signal converted into a digital signal in the data collection step is within a predetermined reference range; Blood pressure measurement method in a portable wireless terminal, characterized in that it further comprises. The method of claim 28, The operation processing step A systolic and diastolic time interval setting step of obtaining a time interval between a systolic and diastolic phase from the PPG signal converted into a digital signal in the data collection step; A systolic and diastolic temperature detecting step of obtaining a systolic temperature (T _SYS ) and a diastolic temperature (T _DIA ), which are temperatures of a time interval between the systolic and diastolic phases, from a temperature signal converted into a digital signal in the data collection step; A systolic and diastolic pressure detecting step of obtaining systolic pressure (P _SYS ) and diastolic pressure (P _DIA ), which are pressures in the time intervals of the systolic and diastolic, from the pressure signal converted into a digital signal in the data collection step; Blood pressure measurement method in a portable wireless terminal, characterized in that it further comprises. The method of claim 29, The operation processing step The pulse wave signal PR is applied to the systolic temperature T _SYS , the systolic pressure P _SYS , and the systolic pulse wave correlation coefficients set in the coefficient setting step (A _SYS , Β _SYS , Γ _SYS ). PR = A _SYS T _SYS + Β _SYS P _SYS + Γ _SYS Obtained by Alternatively, the pulse wave signal PR may be obtained by using the diastolic temperature T _DIA , the diastolic pressure P _DIA , and the diastolic pulse wave correlation coefficients Α _DIA , Β _DIA and Γ _DIA set in the coefficient setting step. PR = Α _DIA T _DIA + Β _DIA P _DIA + Γ _DIA A blood pressure measurement method in a portable wireless terminal, characterized by further comprising a pulse wave detection step obtained by. The method of claim 30 The operation processing step The systolic blood volume signal (PPG _SYS ) is obtained with the systolic temperature (T _SYS ), the systolic pressure (P _SYS ), and the systolic blood volume correlation coefficients (α _SYS , β _SYS , and γ _SYS ) set in the coefficient setting step. PPG _SYS = α _SYS T _SYS + β _SYS P _SYS + γ _SYS Systolic blood volume detection step obtained by; The diastolic blood volume signal (PPG _DIA ) is obtained with the diastolic temperature (T _DIA ), the diastolic pressure (P _DIA ), and the diastolic blood volume correlation coefficient (α _DIA , β _DIA , γ _DIA ) set in the coefficient setting step. PPG _DIA = α _DIA T _DIA + β _DIA P _DIA + γ _DIA Diastolic blood volume detection step obtained by the; Blood pressure measurement method in a portable wireless terminal, characterized in that it further comprises. The method of claim 31, wherein The operation processing step From the waveform of the PPG signal received from the data collection step And a blood volume signal for detecting a systolic blood volume signal (PPG _SYS ), a diastolic blood volume signal (PPG _DIA ), a pulse wave signal (PR), and a pulse wave signal detecting step. 33. The method of claim 32, The calculated values, that is, the systolic blood volume signal PPG _SYS obtained in the systolic blood volume detection step, the diastolic blood volume signal PPG _DIA obtained in the diastolic blood volume detection step, and the pulse wave signal PR obtained in the pulse wave detection step, Compared to the measured value, that is, a calculated value for determining whether the systolic blood volume signal PPG _SYS , the diastolic blood volume signal PPG _DIA , and the pulse wave signal PR obtained in the blood volume signal and pulse wave signal detecting step are the same Blood pressure measurement method in a portable wireless terminal, characterized in that it further comprises a step. The method of claim 33, wherein If the calculated value and the measured value are the same in the calculated value and the measured value comparison step, The systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), pulse wave signal (PR) of the systolic and diastolic blood pressure detection step, The systolic blood volume signal PPG _SYS obtained in the systolic blood volume detection step, the diastolic blood volume signal PPG _DIA obtained in the diastolic blood volume detection step, and the pulse wave signal PR obtained in the pulse wave detection step. Blood pressure measurement method. The method of claim 34, wherein If the calculated value and the measured value are different in the calculated value and the measured value comparison step, The systolic blood volume signal (PPG _SYS ), diastolic blood volume signal (PPG _DIA ), pulse wave signal (PR) of the systolic and diastolic blood pressure detection step, Normalized value obtained by normalizing the systolic blood volume signal PPG _SYS , the diastolic blood volume signal PPG _DIA , and the pulse wave signal PR obtained in the blood volume signal and pulse wave signal detecting step by a predetermined temperature and pressure. A systolic blood volume signal (PPG _SYS ), a normalized diastolic blood volume signal (PPG _DIA ), and a normalized pulse wave signal (PR).

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