JP2019208617A - Organism analyzer, organism analysis method and program - Google Patents

Abstract

To calculate highly accurately a systolic blood pressure and a diastolic blood pressure.SOLUTION: In an organism analyzer including a pulse pressure calculation part for calculating a pulse pressure index relative to a pulse pressure of an organism, an average blood pressure calculation part for calculating an average blood pressure index relative to an average blood pressure of the organism, and a blood pressure calculation part for calculating a systolic blood pressure and a diastolic blood pressure corresponding to the pulse pressure index and the average blood pressure index, at least either of the pulse pressure index and the average blood pressure index is calculated corresponding to a blood flow rate index relative to a blood flow rate of the organism calculated from an intensity spectrum relative to a frequency of light reflected and received by the inside of the organism by irradiation of a laser beam.SELECTED DRAWING: Figure 3

Description

  The present invention relates to a technique for analyzing a living body.

  Various measurement techniques for analyzing biological information such as blood pressure have been proposed. For example, Patent Document 1 discloses a blood pressure measurement device that measures blood pressure using a blood flow velocity sensor that irradiates a living body with ultrasonic waves. Specifically, the blood pressure measurement device calculates systolic blood pressure from the maximum value of the artery diameter and the maximum value of the blood flow velocity, and calculates the diastolic blood pressure from the minimum value of the artery diameter and the minimum value of the blood flow velocity. To do.

JP 2004-154231 A

  However, since the calculated value of the arterial diameter may include noise, the maximum value suitable for the calculation of the systolic blood pressure and the minimum value suitable for the calculation of the diastolic blood pressure may not always be appropriately specified. The same applies to the blood flow velocity. Therefore, the technique of Patent Document 1 cannot always calculate systolic blood pressure and diastolic blood pressure with high accuracy.

In order to solve the above problems, a living body analysis device according to a preferred embodiment of the present invention calculates a pulse pressure calculation unit that calculates a pulse pressure index related to the pulse pressure of a living body, and calculates an average blood pressure index related to the average blood pressure of the living body. An average blood pressure calculation unit and a blood pressure calculation unit for calculating systolic blood pressure and diastolic blood pressure according to the pulse pressure index and the average blood pressure index are reflected and received inside the living body by laser light irradiation. At least one of the pulse pressure index and the average blood pressure index is calculated according to the blood flow index related to the blood flow of the living body calculated from the intensity spectrum related to the frequency of the light.
The biological analysis method according to a preferred aspect of the present invention calculates a pulse pressure index related to the pulse pressure of the living body, calculates an average blood pressure index related to the average blood pressure of the living body, and contracts according to the pulse pressure index and the average blood pressure index. Is a biological analysis method for calculating diastolic blood pressure and diastolic blood pressure, from an intensity spectrum related to the frequency of light reflected and received inside the living body by laser light irradiation, according to a blood flow index related to the blood flow volume of the living body At least one of the pulse pressure index and the average blood pressure index is calculated.
A program according to a preferred aspect of the present invention includes a pulse pressure calculation unit that calculates a pulse pressure index related to the pulse pressure of a living body, an average blood pressure calculation unit that calculates an average blood pressure index related to the average blood pressure of the living body, a pulse pressure index and an average A program that causes a computer to function as a blood pressure calculation unit that calculates systolic blood pressure and diastolic blood pressure according to a blood pressure index, and the intensity related to the frequency of light reflected and received inside the living body by laser light irradiation At least one of the pulse pressure index and the average blood pressure index is calculated according to the blood flow index related to the blood flow of the living body calculated from the spectrum.

It is a side view of the living body analysis device concerning a 1st embodiment of the present invention. It is a graph which shows the time change of blood pressure. It is a block diagram which paid its attention to the function of a biological analysis apparatus. It is a block diagram which paid its attention to the element for calculating a pulse pressure. It is a graph which shows the time change of a blood volume parameter | index. It is a graph which shows the time change of a blood flow rate parameter | index. It is a graph which shows the relationship between the blood flow velocity amplitude measured about a test subject, and the amplitude of the time change of the calculated blood volume parameter | index about the case where the test subject's skin thickness was changed. It is a graph which shows the relationship between the blood flow velocity amplitude measured about a test subject, and the amplitude of the time change of the calculated blood flow volume index about the case where the test subject's skin thickness was changed. A graph showing the relationship between the blood flow velocity amplitude actually measured for a subject and the ratio of the time change amplitude of the blood volume index and the time change amplitude of the blood flow index for a plurality of cases where the skin thickness of the subject is changed It is. It is a graph which shows the time change of the normalized blood volume parameter | index, and the time change of the normalized blood flow parameter | index respectively. It is the graph which showed the relationship between the pulse-wave propagation speed measured about the test subject, and the ratio of the blood volume integrated value and the blood flow integrated value about several test subjects. It is a graph which shows the relationship between the pulse pressure measured about a test subject, and the product of an amplitude parameter | index and a resistance parameter | index about several test subjects. It is a schematic diagram of the blood vessel of an arm part. It is a graph which shows the relationship between the distance from the heart to the specific site | part on the blood vessel, and the average blood pressure in the said site | part. It is a block diagram which paid its attention to the element for calculating average blood pressure. It is a flowchart of the biological analysis process which a control apparatus performs. It is a flowchart which shows the specific content of the process which calculates a pulse pressure. It is a flowchart which shows the specific content of the process which calculates a resistance parameter | index. It is a flowchart which shows the specific content of the process which calculates average blood pressure. It is a flowchart which shows the specific content of the process which calculates average blood pressure. It is the graph which showed the relationship between the kind of blood vessel in a systemic circulation, and blood pressure. It is a block diagram which paid its attention to the element for calculating the pulse pressure which concerns on the modification of 1st Embodiment. It is a block diagram which paid its attention to the element for calculating the pulse pressure which concerns on the modification of 1st Embodiment. It is a graph which shows the time change of a blood flow rate parameter | index. It is a block diagram which paid its attention to the element for calculating the pulse pressure which concerns on the modification of 1st Embodiment. It is a block diagram which paid its attention to the element for calculating the pulse pressure which concerns on the modification of 1st Embodiment. It is a block diagram which paid its attention to the element for calculating the average blood pressure which concerns on the modification of 1st Embodiment. Among the detection signals, the SN ratio in the frequency band used for the calculation of the blood flow index and the SN ratio in the frequency band used for the calculation of the absorbance index in the detection signal are determined by the light emitting unit and the light receiving unit. It is a table | surface shown about the case where several distance is changed. It is a block diagram which paid its attention to the function of the bioanalytical apparatus in 2nd Embodiment. It is a block diagram which paid its attention to the function of the bioanalytical apparatus in 3rd Embodiment. It is a graph which shows the variation coefficient of the average value of the blood flow volume index over a plurality of analysis periods, and the variation coefficient of the average value of the blood flow volume index over a plurality of analysis periods. It is a schematic diagram which shows the usage example of the bioanalytical apparatus which concerns on 4th Embodiment. It is a schematic diagram which shows the other usage example of the bioanalytical apparatus which concerns on 4th Embodiment. It is a graph which shows the relationship between the actual value of the blood volume parameter | index which concerns on 5th Embodiment, and the cube of the blood vessel diameter. It is a graph which shows the relationship between the average blood pressure (calculated value) and average blood pressure (actually measured value) which concern on 5th Embodiment. It is a graph which shows the frequency weighting intensity spectrum which concerns on each of 7th Embodiment and contrast. It is a graph which shows the relationship between the average blood pressure (calculated value) and average blood pressure (actually measured value) which are related to proportionality. It is a graph which shows the relationship between the average blood pressure (calculated value) and average blood pressure (actually measured value) which concern on 7th Embodiment. It is a block diagram of the bioanalytical apparatus in a modification. It is a block diagram of the bioanalytical apparatus in a modification. It is a block diagram of the bioanalytical apparatus in a modification.

<First Embodiment>
FIG. 1 is a side view of a biological analysis apparatus 100 according to the first embodiment of the present invention. The biological analysis apparatus 100 is a measuring device that non-invasively measures biological information of a subject. The biological analysis apparatus 100 according to the first embodiment measures the systolic blood pressure Pmax and the diastolic blood pressure Pmin of a specific part (hereinafter referred to as “measurement part”) H in the body of the subject (user) as biological information. In the following description, the wrist or upper arm of the subject is exemplified as the measurement site H.

  FIG. 2 is a graph showing the temporal change PT of the blood pressure P. In the first embodiment, the systolic blood pressure (maximum blood pressure) Pmax and the diastolic blood pressure (minimum blood pressure) Pmin in the analysis period (about 0.5 to 1 second) T corresponding to one beat of pulsation are calculated. The symbol ΔP in FIG. 2 is the pulse pressure in the analysis period T, and the symbol Pave is the average blood pressure in the analysis period T. The pulse pressure ΔP is the difference between the systolic blood pressure Pmax and the diastolic blood pressure Pmin. The time length of the analysis period T is not limited to one beat. For example, a period longer than the time length corresponding to one beat may be set as the analysis period T.

Here, the knowledge that the relationship of the following formulas (1) and (2) is approximately established among the average blood pressure Pave, the pulse pressure ΔP, the systolic blood pressure Pmax, and the diastolic blood pressure Pmin is obtained. It was. Therefore, the biological analysis apparatus 100 according to the first embodiment calculates the pulse pressure ΔP and the average blood pressure Pave, and calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin from the pulse pressure ΔP and the average blood pressure Pave.

  1 is attached to a measurement site H (upper arm or wrist). The bioanalytical apparatus 100 of the first embodiment is a wristwatch-type portable device that includes a housing unit 12 and a belt 14. The biological analyzer 100 is attached to the body of the subject by winding the belt 14 around the measurement site H.

  FIG. 3 is a configuration diagram focusing on the function of the biological analysis apparatus 100. The biological analysis apparatus 100 according to the first embodiment includes a control device 21, a storage device 22, a display device 23, a detection unit 30A, and a detection unit 30B. The control device 21 and the storage device 22 are installed inside the housing unit 12.

  As illustrated in FIG. 1, the display device 23 (for example, a liquid crystal display panel) is installed, for example, on the surface of the housing 12 opposite to the measurement site H. The display device 23 displays various images including the measurement results under the control of the control device 21.

  Each detection unit 30 (30A, 30B) is a detection device that generates a detection signal Z corresponding to the state of the measurement site H. The detection signal ZA generated by the detection unit 30A is used for calculating the pulse pressure ΔP. On the other hand, the detection signal ZB generated by the detection unit 30B is used for calculating the average blood pressure Pave.

  The control device 21 in FIG. 3 is an arithmetic processing device such as a CPU (Central Processing Unit) or an FPGA (Field-Programmable Gate Array), and controls the entire biological analysis device 100. The storage device 22 is configured by, for example, a nonvolatile semiconductor memory, and stores a program executed by the control device 21 and various data used by the control device 21. A configuration in which the functions of the control device 21 are distributed over a plurality of integrated circuits, or a configuration in which some or all of the functions of the control device 21 are realized with dedicated electronic circuits may be employed. In FIG. 3, the control device 21 and the storage device 22 are illustrated as separate elements. However, the control device 21 that includes the storage device 22 may be realized by, for example, an ASIC (Application Specific Integrated Circuit).

  The control device 21 according to the first embodiment executes a program stored in the storage device 22 to thereby execute a plurality of functions (calculation unit 51A, calculation unit 51B, calculation unit) for calculating the systolic blood pressure Pmax and the diastolic blood pressure Pmin. A pulse pressure calculation unit 53, an average blood pressure calculation unit 55, and a blood pressure calculation unit 57) are realized. Note that some functions of the control device 21 may be realized by a dedicated electronic circuit.

  Schematically, the pulse pressure calculation unit 53 calculates the pulse pressure ΔP using a predetermined index calculated by the calculation unit 51A from the detection signal ZA. On the other hand, the average blood pressure calculation unit 55 calculates the average blood pressure Pave using a predetermined index calculated by the calculation unit 51B from the detection signal ZB. The blood pressure calculator 57 calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin from the pulse pressure ΔP calculated by the pulse pressure calculator 53 and the average blood pressure Pave calculated by the average blood pressure calculator 55. As understood from the above description, the detection unit 30A, the calculation unit 51A, and the pulse pressure calculation unit 53 are elements for calculating the pulse pressure ΔP, and the detection unit 30B, the calculation unit 51B, the average blood pressure calculation unit 55, Is an element for calculating the mean blood pressure Pave.

<Pulse pressure ΔP>
Hereinafter, the process for calculating the pulse pressure ΔP will be described. Here, it is known that the blood pressure P can be expressed by the following expression (3) representing the water-hammer. As understood from Equation (3), the blood pressure P is expressed as a product of the blood density ρ, the pulse wave velocity PWV, and the blood flow velocity V of the blood vessel.

Since the blood density ρ and the pulse wave velocity PWV have little temporal variation, the amount of change in the blood density ρ and the amount of change in the pulse wave velocity PWV in the analysis period T can be regarded as constant. Therefore, as shown in Equation (4), the pulse pressure (that is, the amount of change in pressure during the analysis period T) ΔP is the blood density ρ, the pulse wave velocity PWV, and the amount of change in blood flow velocity V during the analysis period T. (In other words, it is expressed as a product of ΔV, ie, the amplitude of the change in blood flow velocity over time) The blood density ρ can be set to a predetermined value (for example, 1070 kg / m ³ ) because individual differences are small. That is, the pulse pressure ΔP can be calculated by calculating the pulse wave propagation velocity PWV and the amplitude of the blood flow velocity V over time (hereinafter referred to as “blood flow velocity amplitude”) ΔV. .

  FIG. 4 is a configuration diagram focusing on elements (detection unit 30A, calculation unit 51A, and pulse pressure calculation unit 53) for calculating pulse pressure ΔP. The detection unit 30A of the first embodiment includes a detection device 30A1 (an example of the first detection device). The detection device 30A1 is an optical sensor module that generates a detection signal ZA1 corresponding to the state of the measurement site H. Specifically, the detection device 30A1 includes a light emitting unit E and a light receiving unit R. The light emitting unit E and the light receiving unit R are installed, for example, at a position facing the measurement site H in the housing unit 12 (typically, a surface that contacts the measurement site H).

  The light emitting unit E is a light source that irradiates the measurement site H with light. The light emitting unit E of the first embodiment irradiates the measurement site H (living body) with a narrow band coherent laser beam. For example, a light emitting element such as a VCSEL (Vertical Cavity Surface Emitting LASER) that emits laser light by resonance in the resonator is preferably used as the light emitting unit E. The light emitting unit E of the first embodiment irradiates the measurement site H with light having a predetermined wavelength (for example, 800 nm to 1300 nm) in the near infrared region, for example. The light emitting unit E emits light under the control of the control device 21. In addition, the light which the light emission part E radiate | emits is not limited to near-infrared light.

  The light that has entered the measurement site H from the light emitting unit E repeats diffuse reflection while passing through the inside of the measurement site H, and then exits to the housing unit 12 side. Specifically, light that has passed through the blood vessel existing inside the measurement site H and the blood in the blood vessel is emitted from the measurement site H to the housing 12 side.

  The light receiving unit R receives the laser light reflected inside the measurement site H. Specifically, the light receiving unit R generates a detection signal ZA1 indicating the light reception level of the light that has passed through the measurement site H. For example, a light receiving element such as a photodiode (PD: Photo Diode) that generates an electric charge according to the received light intensity is used as the light receiving unit R. Specifically, a light receiving element in which a photoelectric conversion layer is formed of InGaAs (indium gallium arsenide) exhibiting high sensitivity in the near infrared region is suitable as the light receiving portion R. As understood from the above description, the detection device 30A1 of the first embodiment is a reflective optical sensor in which the light emitting unit E and the light receiving unit R are located on one side with respect to the measurement site H. However, a transmission type optical sensor in which the light emitting unit E and the light receiving unit R are located on opposite sides of the measurement site H may be used as the detection device 30A1. The detection device 30A1 includes, for example, a drive circuit that drives the light emitting unit E by supplying a drive current, and an output circuit that amplifies and A / D converts the output signal of the light receiving unit R (for example, an amplifier circuit and an A / D converter) In FIG. 4, the illustration of each circuit is omitted.

  The light reaching the light receiving part R is a component diffusely reflected by a tissue (stationary tissue) that is stationary inside the measurement site H and an object (typically a red blood cell) that moves inside the blood vessel inside the measurement site H. And diffusely reflected components. The frequency of light does not change before and after diffuse reflection in stationary tissue. On the other hand, before and after diffuse reflection by red blood cells, the frequency of light changes by a change amount (hereinafter referred to as “frequency shift amount”) proportional to the moving speed of red blood cells (that is, blood flow velocity). That is, the light that passes through the measurement site H and reaches the light receiving portion R contains a component that is fluctuated (frequency shifted) by a frequency shift amount with respect to the frequency of the light emitted from the light emitting portion E. The detection signal ZA1 supplied to the control device 21 is an optical beat signal reflecting a frequency shift due to blood flow inside the measurement site H.

  The calculation unit 51A of the first embodiment includes an index calculation unit 51A1. The index calculation unit 51A1 calculates the blood volume index MA1 and the blood flow index FA1 of the measurement site H from the detection signal ZA1 generated by the detection device 30A1. The blood volume index MA1 (so-called MASS value) is an index related to the blood volume of the living body (specifically, the number of red blood cells in a unit volume). The blood volume fluctuates in conjunction with the pulsation of the blood vessel diameter synchronized with the heart beat. That is, the blood volume index MA1 is also correlated with the blood vessel diameter. Therefore, the blood volume index MA1 can be rephrased as an index of the blood vessel diameter of the living body (and also the cross-sectional area of the blood vessel). On the other hand, the blood flow index FA1 (so-called FLOW value) is an index related to the blood flow volume of the living body (that is, the volume of blood moving within the artery within a unit time).

  The index calculator 51A1 calculates an intensity spectrum from the detection signal ZA1, and calculates a blood volume index MA1 and a blood flow index FA1 from the intensity spectrum. The intensity spectrum is a distribution of the intensity (power or amplitude) G (f) of the signal component of the detection signal ZA1 at each frequency (Doppler frequency) on the frequency axis. For the calculation of the intensity spectrum, a known frequency analysis such as Fast Fourier Transform (FFT) can be arbitrarily employed. The calculation of the intensity spectrum is repeatedly executed with a short period compared to the analysis period T.

The blood volume index M (MA1) is expressed by the following formula (5a). The symbol <I ² > in Equation (5a) is the average intensity over the entire band of the detection signal ZA1, or the intensity G (0) at 0 Hz (that is, the intensity of the DC component) in the intensity spectrum.

As understood from the equation (5a), the blood volume index MA1 is obtained by integrating the intensity G (f) of each frequency f in the intensity spectrum with respect to the range between the lower limit value fL and the upper limit value fH on the frequency axis. Calculated. The lower limit value fL is lower than the upper limit value fH. Note that the blood volume index MA1 may be calculated by the calculation of the following formula (5b) in which the integral of the formula (5a) is replaced with the sum (Σ). The symbol Δf in the formula (5b) is a bandwidth corresponding to one intensity G (f) on the frequency axis, and each rectangle when the intensity spectrum is approximated by a plurality of rectangles arranged on the frequency axis. Corresponds to the width. The calculation of the blood volume index MA1 is repeatedly executed in a shorter cycle than the analysis period T. FIG. 5 is a graph showing the time change MT of the blood volume index M (MA1) calculated by the index calculation unit 51A1 for the analysis period T. In addition to the blood volume index MA1 of the first embodiment, the blood volume index M (MB1, MA3, MC) exemplified in each form described below is also calculated as the blood volume index M of the formula (5a) or the formula (5b). Is done. As understood from the above description, the blood volume index M is obtained from the intensity spectrum related to the frequency of the light reflected and received inside the living body by laser light irradiation (specifically, the intensity of each frequency in the intensity spectrum is measured). Calculated (accumulated for a given frequency range).

The blood flow index F (FA1) is expressed by the following formula (6a).

As understood from the equation (6a), the product (f × G (f)) of the intensity G (f) of each frequency f in the intensity spectrum and the frequency f is expressed as a lower limit value fL and an upper limit value fH on the frequency axis. The blood flow index FA1 is calculated by integrating the range between and. Hereinafter, the product of the intensity G (f) of each frequency f in the intensity spectrum and the frequency f (f × G (f)) is referred to as “frequency weighted intensity spectrum”. Note that the blood flow index FA1 may be calculated by calculation of the following formula (6b) in which the integral of formula (6a) is replaced with the sum (Σ). The calculation of the blood flow index FA1 is repeatedly executed in a shorter cycle than the analysis period T. FIG. 6 is a graph showing the time change FT of the blood flow index F (FA1) calculated by the index calculation unit 51A1 for the analysis period T. In addition to the blood flow rate index FA1 of the first embodiment, the blood flow rate index F (FB1, FA2, FC) exemplified in each form described later is also calculated as the blood flow rate index F of the formula (6a) or the formula (6b). Is done. As understood from the above description, the blood flow index F is obtained from the intensity spectrum related to the frequency of the light reflected and received inside the living body by laser light irradiation (specifically, the intensity of each frequency in the intensity spectrum). It is calculated by multiplying the product with the frequency over a predetermined frequency range.

  The pulse pressure calculation unit 53 in FIG. 4 calculates the pulse pressure ΔP. Specifically, the pulse pressure calculation unit 53 calculates the pulse pressure ΔP at the measurement site H using the blood volume index MA1 and the blood flow index FA1 calculated by the index calculation unit 51A1. The pulse pressure calculation unit 53 of the first embodiment includes an amplitude calculation unit 531, a resistance calculation unit 533, and a processing unit 535.

  The amplitude calculator 531 calculates an index related to the blood flow velocity amplitude ΔV (hereinafter referred to as “amplitude index”) using the blood volume index MA1 and the blood flow index FA1 generated by the index calculator 51A1. Specifically, the amplitude calculator 531 calculates the amplitude index according to the amplitude ΔM of the time change MT of the blood volume index MA1 and the amplitude ΔF of the time change FT of the blood flow index F. As illustrated in FIG. 5, the amplitude ΔM is the difference between the maximum value Mmax and the minimum value Mmin of the blood volume index M (MA1) in the analysis period T. Further, as illustrated in FIG. 6, the amplitude ΔF is a difference between the maximum value Fmax and the minimum value Fmin of the blood flow rate index F (FA1) in the analysis period T.

  FIG. 7 is a graph showing the relationship between the blood flow velocity amplitude ΔV actually measured for the subject and the amplitude ΔM specified by the index calculation unit 51A1, and FIG. 8 shows the blood flow velocity amplitude ΔV actually measured for the subject. It is a graph which shows the relationship with amplitude (DELTA) F which index calculation part 51A1 specifies. 7 and 8 show a plurality of cases where the skin thickness of the subject is changed. Skin thickness is the distance from the surface of the skin to the blood vessels. The blood flow velocity amplitude ΔV is an actual measurement value by a known measurement technique. As understood from FIGS. 7 and 8, each of the amplitude ΔM and the amplitude ΔF varies greatly depending on the skin thickness, although there is a correlation with the blood flow velocity amplitude ΔV. FIG. 9 shows the relationship between the blood flow velocity amplitude ΔV actually measured for the subject and the ratio of the amplitude ΔM and the amplitude ΔF specified by the index calculation unit 51A1 (specifically, the ratio of the amplitude ΔF to the amplitude ΔM). It is a graph shown about a plurality of cases where skin thickness was changed. As can be seen from FIG. 9, the ratio of the amplitude ΔF to the amplitude ΔM (ΔF / ΔM) has a positive correlation with the blood flow velocity amplitude ΔV (when one increases, the other increases), and according to the skin thickness The knowledge that the fluctuation was small was obtained. Based on the above knowledge, the amplitude calculation unit 531 of the first embodiment calculates the ratio (ΔF / ΔM) between the amplitude ΔM and the amplitude ΔF as an amplitude index.

  The resistance calculation unit 533 in FIG. 4 calculates an index related to the pulse wave velocity PWV using the blood volume index MA1 and the blood flow volume index FA1 generated by the index calculation unit 51A1. The pulse wave velocity PWV correlates with vascular resistance. Specifically, when the vascular resistance is high, the pulse wave velocity PWV tends to increase. Based on this tendency, an index related to the pulse wave velocity PWV is referred to as a “resistance index”. That is, the resistance calculation unit 533 calculates the resistance index using the blood volume index MA1 and the blood flow index FA1. Specifically, the value obtained by integrating the blood volume index MA1 for the integration period (hereinafter referred to as “blood volume integrated value”) SM and the value obtained by integrating the blood flow index FA1 for the integration period (hereinafter referred to as “blood flow integrated value”). The resistance index is calculated according to SF. For example, the integration period coincides with the analysis period T (that is, a period corresponding to one beat). Note that the integration period and the analysis period T may be different.

  In the first embodiment, the resistance index is determined according to the blood volume integrated value SM obtained by integrating the normalized blood volume index MN for the analysis period T and the blood flow integrated value SF obtained by integrating the normalized blood flow index FN for the analysis period T. Is calculated. The normalized blood volume index MN is a numerical value obtained by normalizing the blood volume index MA1 within the normalized range, and the normalized blood flow index FN is a numerical value obtained by normalizing the blood flow volume index FA1 within the normalized range.

  FIG. 10 is a graph showing the time change MNT of the normalized blood volume index MN and the time change FNT of the normalized blood flow index FN. FIG. 10 illustrates a case where each of the blood volume index MA1 and the blood flow volume index FA1 is normalized to a normalization range of 0 or more and 1 or less. That is, the blood volume index MA1 and the blood flow volume index FA1 are normalized so that the minimum value Mmin and the minimum value Fmin in the analysis period T become 0 and the maximum value Mmax and the maximum value Fmax in the analysis period T become 1. Is done. That is, the amplitude ΔMN of the normalized blood volume index MN and the amplitude ΔFN of the normalized blood flow index FN are 1. Specifically, the blood volume integrated value SM is a time integrated value of the normalized blood volume index MN in the analysis period T, and the blood flow integrated value SF is a time integrated value of the normalized blood flow index FN in the analysis period T. It is. The area surrounded by the curve representing the time change MNT of the normalized blood volume index MN and the time axis (straight line of MN = 0) is the blood volume integrated value SM, and the time change FNT of the normalized blood volume index FN In other words, the area of the region surrounded by the curve representing the time axis and the time axis (straight line of FN = 0) is the blood flow integrated value SF.

  FIG. 11 is a graph showing the relationship between the pulse wave propagation velocity PWV measured for a subject and the ratio between the blood volume integrated value SM and the blood flow integrated value SF for a plurality of subjects. The pulse wave velocity PWV is an actual measurement value by a known measurement technique. As can be seen from FIG. 11, the pulse wave propagation speed PWV and the ratio between the blood volume integrated value SM and the blood flow integrated value SF (specifically, the ratio of the blood flow integrated value SF to the blood volume integrated value SM). The knowledge that there is a correlation was obtained. Based on the above knowledge, the resistance calculation unit 533 of the first embodiment calculates the ratio (SF / SM) between the blood volume integrated value SM and the blood flow integrated value SF as a resistance index.

The processing unit 535 in FIG. 4 calculates the pulse pressure ΔP according to the amplitude index calculated by the amplitude calculation unit 531 and the resistance index calculated by the resistance calculation unit 533. Specifically, the processing unit 535 calculates the pulse pressure ΔP according to the product of the amplitude index and the resistance index using the above-described equation (4). FIG. 12 is a graph showing the relationship between the pulse pressure ΔP measured for a subject and the product of the amplitude index (ΔF / ΔM) and the resistance index (SF / SM) for each of a plurality of subjects. The pulse pressure ΔP is an actual measurement value by a known measurement technique. As understood from FIG. 12, there is a correlation (specifically, a proportional relationship) between the product of the amplitude index and the resistance index ((ΔF / ΔM) × (SF / SM)) and the pulse pressure ΔP. Therefore, the pulse pressure ΔP is expressed by the following formula (7). As understood from the equation (7), the pulse pressure ΔP can be calculated by multiplying the product of the amplitude index and the resistance index by a predetermined coefficient K. For example, the coefficient K is set according to the subject's attributes (for example, age, sex, and weight). As understood from the above description, the pulse pressure calculation unit 53 functions as an element for calculating the pulse pressure ΔP according to the blood volume integrated value SM and the blood flow volume integrated value SF.

  As described above, in the first embodiment, the amplitude index (ΔF / ΔM) is calculated according to the amplitude ΔM of the time change MT of the blood volume index MA1 and the amplitude ΔF of the time change FT of the blood flow index FA1. A resistance index (SF / SM) is calculated according to the blood volume integrated value SM and the blood flow volume integrated value SF, and the pulse pressure ΔP is calculated from the amplitude index and the resistance index. In calculating the above indices (amplitude index, resistance index, and pulse pressure ΔP), a cuff is not necessary in principle. Therefore, it is possible to calculate the pulse pressure ΔP with high accuracy while reducing the physical load on the subject.

  In the first embodiment, in particular, the product of the ratio (ΔF / ΔM) of the amplitude ΔM and the amplitude ΔF and the ratio of the blood volume integrated value SM and the blood flow integrated value SF (SF / SM) correlates with the pulse pressure ΔP. By using this tendency, it is possible to calculate the pulse pressure ΔP with high accuracy. Further, by taking the ratio of the amplitude ΔM of the blood volume index MA1 and the amplitude ΔF of the blood flow index FA1, the amplitude index can be calculated with high accuracy even when the skin thickness changes.

<Average blood pressure Pave>
Hereinafter, processing for calculating the average blood pressure Pave will be described. FIG. 13 is a schematic diagram of blood vessels in the arm. FIG. 13 shows an artery (for example, radial artery) Y1 and an arteriole (for example, finger artery) Y2 connected to the artery Y1. As illustrated in FIG. 3, the point X1 is a predetermined point in the artery Y1, the point X2 is a point between the artery Y1 and the arteriole Y2, and the point X3 is a point where the arteriole Y2 is erased. That is, the point X1 is closer to the heart than the point X3.

The relationship between the blood pressure P1 at the point X1 in the artery Y1, the blood pressure P2 at the point X2 between the artery Y1 and the arteriole Y2, and the blood pressure P3 at the extinction point X3 of the arteriole Y2 is expressed by Hagen Poiseuille ( Using the Hagen-Poiseuille's law, it is expressed by the following equations (8) and (9). The symbol L1 in Equation (8) is the length of the artery Y1, the symbol Q1 is the blood flow volume of the artery Y1, and the symbol d1 is the blood vessel diameter (radius) of the artery Y1. The symbol L2 in Equation (9) is the length of the arteriole Y2, the symbol Q2 is the blood flow of the arteriole Y2, and the symbol d2 is the blood vessel diameter (radius) of the arteriole Y2. In addition, the symbol ρ in the equations (8) and (9) is the blood density.

The amount of change in blood pressure from point X1 to point X3 (that is, P1-P3) is expressed by the following equation (10) using equations (8) and (9).

FIG. 14 is a graph showing the relationship between the distance from the heart to a specific site on the blood vessel and the blood pressure at that site. As can be seen from FIG. 14, the change in blood pressure (P1-P2) from point X1 to point X2 tends to be sufficiently smaller than the change in blood pressure (P2-P3) from point X2 to point X3. is there. Specifically, the amount of change (P1-P2) is about 1-5 mmHg, while the amount of change (P2-P3) is about 100 mmHg. Further, it is known that the blood pressure P3 at the extinction point X3 of the arteriole Y2 is very small (for example, several mmHg). Therefore, assuming that the amount of change (P1-P2) and the blood pressure P3 are 0 mmHg, the following equation (11) is derived from the equation (10). As understood from the equation (11), the blood pressure P1 approximates the amount of change (P1-P3).

The blood density ρ can be set to a predetermined value (for example, 1070 kg / m ³ ) because individual differences are small. The distance L2 can be set to a predetermined value estimated from the height and sex of the subject. That is, it is possible to calculate the blood pressure P1 of the artery Y1 by calculating the blood flow volume Q2 and the blood vessel diameter d2 of the arteriole Y2. Therefore, in the first embodiment, the average blood pressure Pave is calculated using Equation (11).

  FIG. 15 is a configuration diagram focusing on elements (detection unit 30B, calculation unit 51B, and average blood pressure calculation unit 55) for calculating average blood pressure Pave. The detection unit 30B of the first embodiment includes a detection device 30B1 (an example of the second detection device). The detection device 30B1 is an optical sensor module that generates a detection signal ZB1 corresponding to the state of the measurement site H. The detection device 30B1 includes a light emitting unit E and a light receiving unit R similar to the detection device 30A1 of FIG. The light emitting unit E and the light receiving unit R are installed, for example, at a position facing the measurement site H in the housing unit 12 (typically, a surface that contacts the measurement site H).

  The calculation unit 51B of FIG. 15 includes an index calculation unit 51B1. The index calculation unit 51B1 calculates the blood vessel diameter index and the blood flow index FB1 of the measurement site H. The blood vessel diameter index is an index related to the blood vessel diameter (and the cross-sectional area of the blood vessel) of the living body. As described above, the blood vessel diameter correlates with the blood volume index M. Therefore, in the first embodiment, the blood volume index M is exemplified as the blood vessel diameter index. Specifically, the index calculation unit 51B1 calculates the blood volume index MB1 and the blood flow volume index FB1 of the measurement site H from the detection signal ZB1 generated by the detection device 30B1. The blood volume index MB1 is calculated from the above formula (5a) or formula (5b), and the blood flow index FB1 is calculated from the above formula (6a) or formula (6b).

  The average blood pressure calculation unit 55 calculates the average blood pressure Pave of the living body. Specifically, the average blood pressure calculation unit 55 calculates the average blood pressure Pave of the living body according to the blood volume index MB1 and the blood flow volume index FB1 calculated by the index calculation unit 51B1. The average blood pressure calculation unit 55 of the first embodiment calculates the average blood pressure Pave according to the average value Mave obtained by averaging the blood volume index MB1 for the analysis period T and the average value Fave obtained by averaging the blood flow index FB1 for the analysis period T. Calculate. The average value Mave is an average (for example, simple average or weighted average) of a plurality of blood volume indices MB1 calculated within the analysis period T. The average value Fave is an average (for example, a simple average or a weighted average) of a plurality of blood flow indexes FB1 calculated within the analysis period T.

As described above, the blood volume index M correlates with the blood vessel diameter d. Specifically, the cube root (M ^1/3 ) of the blood volume index M corresponds to the blood vessel diameter d. In other words, the cube of the blood vessel diameter d2 corresponds to the blood volume index M. The blood flow index F corresponds to the blood flow Q. In consideration of the above relationship, the above formula (11) is transformed into the following formula (12).

The average blood pressure calculation unit 55 of the first embodiment calculates the average blood pressure Pave by the calculation of Expression (12). Symbol K is a coefficient determined in advance according to blood density ρ, arteriole length L2, and the like. As understood from the equation (12), the average blood pressure Pave is calculated according to Fave / Mave ^4/3 . The coefficient K is set, for example, from an actual measurement value of the average blood pressure Pave actually measured using a cuff or the like, and an arithmetic value of Fave / Mave ^{4/3 in} Expression (12) (for example, K = actual value / calculation). value).

  As described above, in the first embodiment, the average blood pressure Pave is calculated according to the blood vessel diameter index (blood volume index MB1) and the blood flow volume index FB1. Here, for example, in a configuration in which it is necessary to press the living body to calculate the average blood pressure (for example, a configuration in which the average blood pressure is calculated using a cuff or the like), an error due to a difference in pressing force may occur. On the other hand, in the first embodiment, since the average blood pressure Pave is calculated according to the blood vessel diameter index (blood volume index MB1) and the blood flow volume index FB1, it is not necessary to compress the living body. As a result, the error due to the difference in the pressing force can be reduced, and the average blood pressure Pave can be calculated with high accuracy.

  By the way, for calculating the blood flow index FB1, it is also possible to use a blood flow velocity sensor that irradiates a living body with ultrasonic waves. However, when an ultrasonic irradiation type blood flow velocity sensor is used, the blood flow index FB1 affects the skin thickness of the measurement site and the conditions (degree of adhesion and pressure) with which the ultrasonic irradiation surface comes into contact with the living body. Actually, it is difficult to specify an index related to blood pressure (for example, average blood pressure) with high accuracy. In addition, when an ultrasonic irradiation type blood flow velocity sensor is used, there is a problem that the bioanalyzer becomes large. On the other hand, in the first embodiment, since laser light is used for calculation of the blood flow index FB1, the influence of skin thickness and the like is reduced as compared with the case where an ultrasonic irradiation type blood flow velocity sensor is used. Thus, the average blood pressure Pave can be measured with high accuracy. It is also possible to reduce the size of the biological analysis device 100.

<Systolic blood pressure Pmax and diastolic blood pressure Pmin>
Hereinafter, processing for calculating the systolic blood pressure Pmax and the diastolic blood pressure Pmin will be described. 3 calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin according to the pulse pressure ΔP calculated by the pulse pressure calculating unit 53 and the average blood pressure Pave calculated by the average blood pressure calculating unit 55. Specifically, the blood pressure calculation unit 57 calculates the systolic blood pressure Pmax by the above-described equation (1), and calculates the diastolic blood pressure Pmin by the above-described equation (2). The control device 21 causes the display device 23 to display the systolic blood pressure Pmax and the diastolic blood pressure Pmin calculated by the blood pressure calculation unit 57.

  FIG. 16 is a flowchart of processing executed by the control device 21 (hereinafter referred to as “biological analysis processing”). The biological analysis process of FIG. 16 is executed every analysis period T on the time axis. When the biological analysis process is started, the control device 21 calculates the pulse pressure ΔP (Sa1). Next, the control device 21 calculates the average blood pressure Pave (Sa2). Then, the control device 21 (blood pressure calculation unit 57) calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin according to the calculated pulse pressure ΔP and the average blood pressure Pave (Sa3). For the calculation of the blood pressure P, the above formulas (1) and (2) are used. The control device 21 displays the calculated systolic blood pressure Pmax and diastolic blood pressure Pmin on the display device 23 (Sa4). Note that the order of calculating the pulse pressure ΔP (Sa1) and calculating the average blood pressure Pave (Sa2) may be reversed. The biological analysis process described above is executed every analysis period T, so that the time series of systolic blood pressure Pmax (that is, time change of systolic blood pressure Pmax) and the time series of diastolic blood pressure Pmin (the diastolic blood pressure Pmin Change with time).

  FIG. 17 is a flowchart showing specific contents of the processing Sa1 for calculating the pulse pressure ΔP. The index calculation unit 51A1 generates a time change MT of the blood volume index MA1 in the analysis period T (Sa11). For calculating the blood volume index MA1, the above formula (5a) or formula (5b) is used. Next, the index calculation unit 51A1 generates a time change FT of the blood flow index FA1 in the analysis period T (Sa12). For the calculation of the blood flow index FA1, the above formula (6a) or formula (6b) is used.

  The amplitude calculator 531 calculates the amplitude index according to the amplitude ΔM of the time change MT and the amplitude ΔF of the time change FT generated by the index calculator 51A1 (Sa13). Specifically, the ratio (ΔF / ΔM) between the amplitude ΔM and the amplitude ΔF is calculated as an amplitude index. Next, the resistance calculator 533 calculates a resistance index from the time change MT and the time change FT generated by the index calculator 51A1 (Sa14). Specifically, the ratio (SF / SM) between the blood volume integrated value SM and the blood flow integrated value SF is calculated as a resistance index. The processing unit 535 calculates the pulse pressure ΔP according to the amplitude index calculated by the amplitude calculation unit 531 and the resistance index calculated by the resistance calculation unit 533 (Sa15). For calculating the pulse pressure ΔP, the above-described equation (7) is used. That is, the pulse pressure ΔP corresponding to the product of the amplitude index and the resistance index is calculated. Note that the order of generation of the time change MT of the blood volume index MA1 (Sa11) and generation of the time change FT of the blood flow index FA1 (Sa12) may be reversed. Further, the order of the process of calculating the amplitude index (Sa13) and the process of calculating the resistance index (Sa14) may be reversed.

  FIG. 18 is a flowchart showing specific contents of the process Sa14 for calculating the resistance index. The resistance calculation unit 533 calculates a normalized blood volume index MN and a normalized blood flow index FN obtained by normalizing the blood volume index MA and the blood flow volume index FA within the normalization range (Sa141). Next, the resistance calculator 533 calculates a blood volume integrated value SM and a blood flow volume integrated value SF obtained by integrating the normalized blood volume index MN and the normalized blood flow index FN over the analysis period T (Sa142). The resistance calculator 533 calculates the ratio (SF / SM) between the blood volume integrated value SM and the blood flow integrated value SF as a resistance index (Sa143).

  FIG. 19 is a flowchart showing specific contents of the process Sa2 for calculating the average blood pressure Pave. The index calculation unit 51B1 calculates the blood volume index MB1 for each of a plurality of time points within the analysis period T (Sa21). For calculating the blood volume index MB1, the above formula (5a) or formula (5b) is used. Next, the index calculation unit 51B1 calculates a blood flow index FB1 for each of a plurality of time points within the analysis period T (Sa22). For the calculation of the blood flow index FB1, the above formula (6a) or formula (6b) is used. The average blood pressure calculator 55 calculates the average blood pressure Pave according to the blood volume index MB1 and the blood flow index FB1 calculated by the index calculator 51B1 (Sa23). The order of calculation of blood volume index MB1 (Sa21) and calculation of blood flow index FB1 (Sa22) may be reversed.

FIG. 20 is a flowchart showing specific contents of the process Sa23 for calculating the average blood pressure Pave. The average blood pressure calculation unit 55 calculates an average value Mave obtained by averaging the blood volume index MB1 over the analysis period T (Sa231). The average blood pressure calculation unit 55 calculates an average value Fave obtained by averaging the blood flow index FB1 over the analysis period T (Sa232). Then, the average blood pressure calculation unit 55 calculates the average blood pressure Pave according to the average value Mave and the average value Fave (Sa233). For calculating the average blood pressure Pave, the above-described equation (12) is used. That is, the average blood pressure Pave is calculated according to Fave / Mave ^4/3 . Note that the order of calculation of the average value Mave (Sa231) and calculation of the average value Fave (Sa232) may be reversed.

  As described above, in the first embodiment, since the systolic blood pressure Pmax and the diastolic blood pressure Pmin are calculated according to the pulse pressure ΔP and the average blood pressure Pave, for example, the maximum value or the minimum value of the blood vessel diameter is used. As compared with the configuration for calculating the systolic blood pressure Pmax and the diastolic blood pressure Pmin, the systolic blood pressure Pmax and the diastolic blood pressure Pmin can be calculated with high accuracy.

<Vessel of measurement site H>
FIG. 21 is a graph showing the relationship between blood vessel type and blood pressure in systemic circulation. As described above, the difference between the systolic blood pressure Pmax and the diastolic blood pressure Pmin is the pulse pressure ΔP. Therefore, the pulse pressure ΔP can be calculated with higher accuracy by using the blood vessel in which the difference between the systolic blood pressure Pmax and the diastolic blood pressure Pmin is large for the calculation of the pulse pressure ΔP. As can be seen from FIG. 21, pulsations appear larger in the blood pressure of arteries (larger arteries and smaller arteries) than other blood vessels. Therefore, for the calculation of the pulse pressure ΔP, it is preferable to use the detection signal ZA reflecting the state of an artery (for example, the brachial artery, radial artery or ulnar artery) existing in the measurement site H. The detection signal ZA reflecting the state of the arteriole may be used for calculating the pulse ΔP.

  Further, as understood from the equation (11), the blood pressure P1 approximates the amount of change (P1-P3). That is, the average blood pressure Pave can be calculated with higher accuracy by using a blood vessel having a large blood pressure change gradient (gradient) in the blood vessel for calculating the average blood pressure Pave. As can be seen from FIG. 21, the blood pressure of the arteriole has a larger slope than other blood vessels. Therefore, for calculating the average blood pressure Pave, it is preferable to use the detection signal ZB reflecting the state of the arteriole present inside the measurement site H.

  With the above knowledge as a background, in the first embodiment, the detection device 30A1 that generates the detection signal ZA1 is installed inside the measurement site H at a position facing the artery (diameter 2 mm to 5 mm). On the other hand, the detection device 30B1 that generates the detection signal ZB1 is installed inside the measurement site H at a position facing the arteriole (diameter 0.02 mm to 2 mm). In the case where the wrist is the measurement site H, for example, the detection device 30A1 is installed at a position close to the radial artery or ulnar artery on the palm side of the wrist, while the detection device 30B1 is installed on the back side of the wrist. When the upper arm is the measurement site H, for example, the detection device 30A1 is installed near the brachial artery inside the upper arm, while the detection device 30B1 is installed outside the upper arm. For example, as can be understood from the above description, the detection device 30A1 is installed on the body-side surface of the upper arm, and the detection device 30B1 is installed on the surface opposite to the body. Are provided at different positions in the circumferential direction of the limbs (for example, the upper arm or the wrist).

  According to the configuration in which the detection device 30A1 and the detection device 30B1 are provided at different positions in the circumferential direction of the limb of the living body, the states of two different blood vessels (for example, arteries and arterioles) are reflected at different positions in the living body. There is an advantage that two detection signals Z can be generated. However, the position where the two detection devices (30A1, 30B1) are arranged is not limited to the circumferential direction of the living body. For example, each detection device (30A1, 30B1) may be arranged on the ear, temple, torso, or the like. For example, a configuration in which the detection device 30A1 is arranged in one of the ear and the temple and the detection device 30B1 is arranged in the other, or the detection device 30A1 is arranged in either the ear or the inner ear and the detection device 30B1 is arranged in the other. The structure to do can also be employ | adopted. For the calculation of the pulse pressure ΔP, a detection signal ZB1 obtained from an arteriole may be used.

<Modification of First Embodiment>
Elements for calculating the pulse pressure ΔP (the detection unit 30A, the calculation unit 51A, and the pulse pressure calculation unit 53) are not limited to the configuration illustrated in FIG.

<Modification 1>
FIG. 22 is a configuration diagram paying attention to elements for calculating the pulse pressure ΔP according to the modification (Modification 1) of the first embodiment. In the first embodiment, the amplitude index and the resistance index are calculated using the detection signal ZA1 generated by the detection device 30A1. On the other hand, in the first modification, the amplitude index is calculated using the detection signal ZA1 generated by the detection device 30A1, and each of the two detection devices 30A (30A2, 30A3) separate from the detection device 30A1 is generated. The resistance index is calculated using the detection signal ZA (ZA2, ZA3).

  The detection unit 30A of Modification 1 includes a detection device 30A2 and a detection device 30A3 in addition to the detection device 30A1 similar to that of the first embodiment. The detection device 30A1 of Modification 1 has the same configuration and function as in the first embodiment, and generates a detection signal ZA1 corresponding to the state of the measurement site H. The detection device 30A2 includes a light receiving unit R and a light emitting unit E similar to those of the detection device 30A1, and generates a detection signal ZA2 corresponding to the state of the measurement site H. Similarly, the detection device 30A3 includes a light receiving unit R and a light emitting unit E, and generates a detection signal ZA3 corresponding to the state of the measurement site H. As the light emitting part E of the detection device 30A3, a light emitting element such as an LED (light emitting diode) that irradiates the measurement site H with incoherent light is preferably used. A VCSEL that emits coherent laser light may be used as the light emitting unit E. The light receiving unit R of the detection device 30A3 generates a detection signal ZA3 corresponding to the light reception level of the light that has passed through the measurement site H, similarly to the light reception unit R of the detection device 30A2. The detection signal ZA3 is a signal representing a photoelectric volume pulse wave. Note that a pressure sensor that generates a detection signal indicating the displacement of the surface of the measurement site H (that is, the displacement of the blood vessel diameter) may be employed as the detection device 30A3.

  The calculation unit 51A of the first modification includes an index calculation unit 51A2 and an index calculation unit 51A3 in addition to the index calculation unit 51A1 similar to that of the first embodiment. Similar to the first embodiment, the index calculation unit 51A1 of Modification 1 calculates the blood volume index MA1 and the blood flow index FA1 of the measurement site H from the detection signal ZA1 generated by the detection device 30A1.

  The index calculation unit 51A2 calculates the blood flow index FA2 from the detection signal ZA2 generated by the detection device 30A2. The blood flow index FA2 is calculated by the same method (formula (6a) or formula (6b)) as the blood flow index FA1. The index calculation unit 51A3 calculates the blood volume index MA3 from the detection signal ZA3 generated by the detection device 30A3. As described above, the blood volume index MA3 correlates with the blood vessel diameter. Based on the above relationship, the index calculation unit 51A3 calculates the displacement of the blood vessel diameter from the detection signal ZA3, and calculates the blood volume index MA3 from the displacement of the blood vessel diameter.

  The pulse pressure calculation unit 53 of Modification 1 includes an amplitude calculation unit 531, a resistance calculation unit 533, and a processing unit 535, as in the first embodiment. As in the first embodiment, the amplitude calculator 531 of the first modification calculates the amplitude index (ΔF / ΔM) from the blood volume index MA1 and the blood flow volume index FA1 calculated by the index calculator 51A1. The resistance calculation unit 533 of the first modification calculates the resistance index (SF / SM) from the blood flow index FA2 calculated by the index calculation unit 51A2 and the blood volume index MA3 calculated by the index calculation unit 51A3. The calculation method of the resistance index is the same as in the first embodiment. Similar to the first embodiment, the processing unit 535 calculates the pulse pressure ΔP according to the amplitude index calculated by the amplitude calculation unit 531 and the resistance index calculated by the resistance calculation unit 533. Also in Modification 2, the same effect as that of the first embodiment is realized.

<Modification 2>
FIG. 23 is a configuration diagram focusing on the elements for calculating the pulse pressure ΔP according to the modification example (modification example 2) of the first embodiment. In the first embodiment, a ratio (ΔF / ΔM) correlated with the blood flow velocity amplitude ΔV is calculated as an amplitude index. On the other hand, in the modified example 2, the blood flow velocity amplitude ΔV itself is calculated as an amplitude index.

  The detection unit 30A of Modification 2 includes a detection device 30A4 in addition to the same detection device 30A1 as in the first embodiment. The configuration and function of the detection device 30A1 of Modification 2 are the same as those in the first embodiment. The detection device 30A4 is an ultrasonic sensor module that generates a detection signal ZA4 according to the state of the measurement site H. Specifically, the detection device 30A4 includes a transmission unit E0 and a reception unit R0. The transmitter E0 transmits ultrasonic waves to the measurement site H. On the other hand, the receiver RD generates a detection signal ZA4 corresponding to the reception level of the ultrasonic wave transmitted from the transmitter E0 and passed through the measurement site H. For example, piezoelectric elements such as piezoelectric ceramics are preferably used as the transmitter E0 and the receiver R0.

  The calculation unit 51A of the second modification includes an index calculation unit 51A1 similar to that of the first embodiment. Similar to the first embodiment, the index calculation unit 51A1 of Modification 2 calculates the blood volume index MA1 and the blood flow index FA1 of the measurement site H from the detection signal ZA1 generated by the detection device 30A1.

  The pulse pressure calculation unit 53 of Modification 1 includes an amplitude calculation unit 531, a resistance calculation unit 533, and a processing unit 535, as in the first embodiment. As in the first embodiment, the resistance calculation unit 533 of Modification 2 calculates the resistance index (SF / SM) using the blood volume index MA1 and the blood flow index FA1 generated by the index calculation unit 51A1.

  The amplitude calculator 531 of the first embodiment calculates the amplitude index from the blood volume index MA1 and the blood flow index FA1 calculated by the index calculator 51A1. On the other hand, the amplitude calculator 531 of the second modification directly calculates the amplitude index (blood flow velocity amplitude ΔV) from the detection signal ZA4 generated by the detection device 30A4. As in the first embodiment, the processing unit 535 calculates the pulse pressure ΔP according to the amplitude index (ΔV) calculated by the amplitude calculation unit 531 and the resistance index (SF / SM) calculated by the resistance calculation unit 533. .

  Also in Modification 2, the same effect as that of the first embodiment is realized. In the second modification, in particular, the blood flow velocity amplitude ΔV is calculated as an amplitude index. Therefore, compared with the configuration in which the ratio (ΔF / ΔM) correlated with the blood flow velocity amplitude ΔV is calculated as the amplitude index, the pulse is highly accurate. It is possible to calculate the pressure ΔP.

<Modification 3>
FIG. 24 is a graph showing the temporal change FT of the blood flow index F. As illustrated in FIG. 24, the area OF of the region surrounded by the curve representing the time change FT of the blood flow index F and the straight line of the minimum value Fmin is the blood obtained by integrating the normalized blood flow index FN over the analysis period T. It is equal to the product (ΔF × SF) of the flow rate integrated value SF and the amplitude ΔF. Further, the area OM of the region surrounded by the curve representing the time change MT of the blood volume index M and the straight line of the minimum value Mmin is the blood volume integrated value SM obtained by integrating the normalized blood volume index MN over the analysis period T; It is equal to the product (ΔM × SM) with the amplitude ΔM. Therefore, the following equation (13) is derived from the above equation (7). As understood from the equation (13), the pulse pressure ΔP is expressed as a product of the ratio of the area OF to the area OM (specifically, the ratio of the area OF to the area OM) and the coefficient K. For the above reason, in Modification 3, the pulse pressure ΔP is calculated from the area OF and the area OM.

  FIG. 25 is a configuration diagram focusing on the elements for calculating the pulse pressure ΔP according to the modification example (modification example 3) of the first embodiment. The configurations of the detection unit 30A and the calculation unit 51A of Modification 2 are the same as those in the first embodiment.

  The pulse pressure calculation unit 53 of Modification 3 has a configuration in which the amplitude calculation unit 531 and the resistance calculation unit 533 are deleted. The processing unit 535 of the third modification calculates the pulse pressure ΔP from the blood volume index MA1 and the blood flow index FA1 calculated by the index calculation unit 51A1. The pulse pressure ΔP is calculated according to a blood volume integrated value SM obtained by integrating the blood volume index MA1 over the analysis period T and a blood flow integrated value SF obtained by integrating the blood flow index FA1 over the analysis period T. In the third modification, the processing unit 535 calculates the area OM as the blood volume integrated value SM, and calculates the area OF as the blood flow volume integrated value SF. That is, in the third modification, the process Sa13 for calculating the amplitude index and the process Sa14 for calculating the resistance index in FIG. 17 are omitted. Specifically, the processing unit 535 calculates the area OM and the area OF, and calculates the pulse pressure ΔP by multiplying the ratio of the area OF to the area OM (OF / OM) by the coefficient K. The area OM corresponds to a blood volume integrated value SM obtained by integrating the blood volume index MA1 for the analysis period T, and the area OF corresponds to a blood flow integrated value SF obtained by integrating the blood flow index FA1 for the analysis period T.

  Also in the modified example 3, as in the first embodiment, the effect that a cuff is unnecessary in principle is realized in calculating the pulse pressure ΔP. Therefore, it is possible to calculate the pulse pressure ΔP with high accuracy while reducing the physical load on the subject. In the third modification, in particular, the calculation of the amplitude ΔF and the amplitude ΔM and the normalization of the blood flow index FA1 and the blood volume index MA1 are not required, so that the processing load for calculating the pulse pressure ΔP is reduced.

<Modification 4>
FIG. 26 is a configuration diagram paying attention to elements for calculating the pulse pressure ΔP according to the modification (Modification 4) of the first embodiment. In the first embodiment, the ratio between the blood flow integrated value SF and the blood volume integrated value SM is calculated as a resistance index. In the fourth modification, the pulse wave velocity PWV is calculated as a resistance index.

  The detection unit 30A of Modification 4 includes a detection device 30A5 and a detection device 30A6 in addition to the detection device 30A1 similar to that of the first embodiment. The detection device 30A1 of Modification 1 has the same configuration and function as in the first embodiment, and generates a detection signal ZA1 corresponding to the state of the measurement site H. The detection device 30A5 and the detection device 30A6 are optical sensor modules similar to the detection device 30A1, for example. The detection device 30A5 generates a detection signal ZA5 that reflects the state of the measurement site H, and the detection device 30A6 generates a detection signal ZA6 that reflects the state of the measurement site H.

  The calculation unit 51A of Modification 4 includes an index calculation unit 51A1 as in the first embodiment. Similar to the first embodiment, the index calculation unit 51A1 of Modification 4 calculates the blood volume index MA1 and the blood flow index FA1 of the measurement site H from the detection signal ZA1 generated by the detection device 30A1.

  The pulse pressure calculation unit 53 of Modification 4 has a configuration including a PWV calculation unit 537 instead of the resistance calculation unit 533 of the first embodiment. The PWV calculation unit 537 calculates the pulse wave propagation velocity PWV as a resistance index using the detection signal ZA5 generated by the detection device 30A5 and the detection signal ZA6 generated by the detection device 30A6. The pulse pressure calculation unit 53 calculates the pulse pressure ΔP according to the amplitude index calculated by the amplitude calculation unit 531 and the resistance index calculated by the PWV calculation unit 537.

  Elements for calculating the average blood pressure Pave (the detection unit 30B, the calculation unit 51B, and the average blood pressure calculation unit 55) are not limited to the configuration illustrated in FIG.

<Modification 5>
The absorbance Abs of blood varies in conjunction with the pulsation of the blood vessel diameter. That is, the absorbance Abs correlates with the blood vessel diameter. Specifically, the relationship between the absorbance Abs and the blood vessel diameter d is expressed by the following formula (14). In the equation (14), the symbol ε is the molar extinction coefficient, and the symbol c is the red blood cell concentration. For the above reason, in the fifth modification, an index (hereinafter referred to as “absorbance index”) J related to the absorbance Abs of the living body is exemplified as the blood vessel diameter index calculated by the index calculation unit 51B1 of FIG.

The index calculation unit 51B1 of Modification 5 calculates the absorbance index J and the blood flow index FB1 similar to that of the first embodiment from the detection signal ZB1 generated by the detection device 30B1. Absorbance Abs is expressed by the following equation (15). The symbol I in Expression (15) is the intensity of the signal component of the detection signal ZB1, and the symbol I0 is the intensity of light incident on the measurement site (the intensity of the emitted light from the light emitting unit E). The following equation (16) is derived from the equations (14) and (15).

  The molar extinction coefficient ε and the red blood cell concentration c can be set to predetermined values. That is, the blood vessel diameter d can be calculated by calculating the common logarithm (log (I / I0)) of the ratio between the intensity I0 and the intensity I. Therefore, the index calculation unit 51B1 of Modification 5 calculates the common logarithm (log (I / I0)) of the ratio between the intensity I0 and the intensity I as the absorbance index J. The intensity I0 is set to a predetermined value, and the intensity I is calculated from the photoelectric volume pulse wave indicating the light reception level of the light received from the living body (measurement site H). That is, the absorbance index J is calculated from the photoelectric volume pulse wave. The photoelectric volume pulse wave is generated from the detection signal ZB1 generated by the detection device 30B1. For example, a photoelectric volume pulse wave is generated by a filtering process that suppresses a high frequency component of the detection signal ZB1 output from the detection device 30B1 and an amplification process that amplifies the signal after the filtering process. The blood flow index FB1 is calculated by the same method as in the first embodiment.

The average blood pressure calculation unit 55 of Modification 5 calculates the average blood pressure Pave from the absorbance index J and the blood flow index FB1 calculated by the index calculation unit 51B1. Specifically, the average blood pressure calculation unit 55 calculates the average blood pressure Pave according to the average value Jave obtained by averaging the absorbance index J for the analysis period T and the average value Fave obtained by averaging the blood flow index F for the analysis period T. To do. As described above, the absorbance index J correlates with the blood vessel diameter d2, and the blood flow index F corresponds to the blood flow Q2. Considering the above relationship, the following equation (17) is derived from the above equations (11) and (16). The average blood pressure calculation unit 55 calculates the average blood pressure Pave by the calculation of Equation (17). Symbol K is a coefficient determined in advance according to blood density ρ, arteriole length L2, and the like. The coefficient K is a coefficient determined in advance according to the molar extinction coefficient ε, red blood cell concentration c, blood density ρ, arteriole length L2, and the like. As will be understood from the formula (17), mean blood pressure Pave modification 5 is calculated according to the Fave / Jave ^4. The coefficient K is set, for example, from an actual measurement value actually measured using a cuff or the like, and a calculated value of Fave / Jave ⁴ in Expression (17) (for example, K = actual value / calculated value).

  The content of the process Sa2 for calculating the average blood pressure Pave in the modified example 5 is the same as that of the first embodiment illustrated in FIG. However, in step Sa21 in FIG. 19, the index calculation unit 51B1 calculates an absorbance index J instead of the blood volume index MB1. Further, in step Sa231 of FIG. 20, the average blood pressure calculation unit 55 calculates the average value Jave of the absorbance index J instead of the average value Mave of the blood volume index MB1.

  Also in the modification 5, the same effect as 1st Embodiment is implement | achieved. In the modified example 5, in particular, since the absorbance index J calculated from the photoelectric volume pulse wave indicating the received light level of the light received from the living body is used as the blood vessel diameter index, the blood volume index M calculated from the intensity spectrum is used as the blood vessel diameter. Compared with the configuration of the first embodiment used as an index, the processing load for calculating the blood vessel diameter index is reduced.

<Modification 6>
In the modified example 6, as in the modified example 5, the average blood pressure Pave is calculated according to the absorbance index J and the blood flow index FB1. However, in the modified example 5, the detection signal ZB1 generated by the common light receiving part R is used for the calculation of the absorbance index J and the blood flow index FB1, but in the modified example 6, the calculation of the absorbance index J and the blood flow rate are used. The detection signal Z generated by the separate light receiving unit R is used for calculation of the index FB1.

  FIG. 27 is a configuration diagram focusing on elements for calculating the average blood pressure Pave according to the sixth modification. The detection device 30B1 in Modification 6 includes a light emitting unit E and two light receiving units R (R1 and R2). As in the first embodiment, the light emitting unit E irradiates the measurement site H (living body) with a narrowband coherent laser beam. Each light receiving unit R receives light reflected by the laser beam inside the measurement site H, as in the fifth modification. Each light receiving part R is installed at a position where the distance from the light emitting part E is different. Details of the positions where the respective light receiving parts R are installed in the detection device 30B1 will be described later. Specifically, the light receiving unit R1 generates a detection signal ZB11 corresponding to the light receiving level of light that has passed through the measurement site H, and the light receiving unit R2 corresponds to the light receiving level of light that has passed through the measurement site H. A detection signal ZB12 is generated. The detection signal ZB11 is used for calculation of the blood flow index FB1. On the other hand, the detection signal ZB12 is used for calculating the absorbance index J.

  The index calculation unit 51B1 of the calculation unit 51B in Modification 6 calculates the blood flow index FB1 from the detection signal ZB11 generated by the light receiving unit R1, and calculates the absorbance index J from the detection signal ZB12 generated by the light receiving unit R2. The blood flow index FB1 and the absorbance index J are calculated by the same method as in the fifth modification. Similarly to the fifth modification, the average blood pressure calculation unit 55 of the sixth modification calculates the average blood pressure Pave from the absorbance index J and the blood flow index FB1 calculated by the index calculation unit 51B1.

  Hereinafter, the position where each light receiving part R is installed in the detection device 30B1 will be described. Here, the frequency band (frequency fL to fH in equation (6b)) used for calculating the blood flow index FB1 in the detection signal ZB1 is different from the frequency band used for calculating the absorbance index J. A distance between the light emitting part E and the light receiving part R1 (for example, a distance between the centers of the light emitting part E and the light receiving part R1) from which a detection signal ZB11 having a high S / N ratio is obtained in a frequency band suitable for the calculation of the blood flow index FB1; This is different from the distance between the light emitting part E and the light receiving part R2 (for example, the distance between the centers of the light emitting part E and the light receiving part R2) from which a detection signal ZB12 having a high S / N ratio is obtained in a frequency band suitable for calculating the absorbance index J To do.

  FIG. 28 shows the quality of the SN ratio in the frequency band used for calculating the blood flow index FB1 in the detection signal ZB11 and the quality of the SN ratio in the frequency band used for calculating the absorbance index J in the detection signal ZB12. Is a table showing a plurality of cases in which the distance between the light emitting unit E and the light receiving unit R is changed. As understood from FIG. 28, the SN ratio of the frequency band used for calculating the blood flow index FB1 in the detection signal ZB11 is obtained when the distance between the light emitting part E and the light receiving part R1 is 0.5 mm or more and 2 mm or less. High value. On the other hand, the knowledge that the SN ratio of the frequency band used for calculating the absorbance index J in the detection signal ZB12 shows a high value when the distance between the light emitting part E and the light receiving part R2 is 3 mm or more and 5 mm or less is obtained. It was.

  Based on the above knowledge, in the modified example 6, the distance between the light receiving part R1 and the light receiving part R2 and the light emitting part E is individually set. For example, the distance between the light receiving part R1 and the light emitting part E is set to a distance at which a detection signal ZB11 having a high S / N ratio is obtained in a frequency band suitable for calculating the blood flow index FB1, and the distance between the light receiving part R2 and the light emitting part E is set. The distance is set to a distance at which a detection signal ZB12 having a high S / N ratio can be obtained in a frequency band suitable for calculating the absorbance index J. Specifically, based on the results shown in FIG. 28, the distance between the light emitting part E and the light receiving part R1 is set to 0.5 mm or more and 2 mm or less, and between the light emitting part E and the light receiving part R2. Is set to 3 mm or more and 5 mm or less (preferably 4 mm).

  In the sixth modification, the same effect as in the fifth modification can be obtained. In the modified example 6, in particular, since the light receiving part R1 for calculating the blood flow index FB1 and the light receiving part R2 for calculating the absorbance index J are separate, SN in a frequency band suitable for calculating the blood flow index FB1. The detection signal ZB11 having a high ratio and the detection signal ZB12 having a high SN ratio in a frequency band suitable for calculating the absorbance index J can be generated. Therefore, the average blood pressure Pave can be calculated with high accuracy as compared with the configuration using the common light receiving part R for the calculation of the absorbance index J and the calculation of the blood flow index FB1.

<Modification 7>
In the first embodiment, in the detection device 30A1 and the detection device 30B1, the detection signal Z generated by the common light receiving unit R is used for the calculation of the blood volume index M and the calculation of the blood flow index F. It is also possible to use the detection signal Z generated by for calculating the blood vessel diameter index and the blood flow index F. Specifically, each detection device (30A1, 30B1) includes a light emitting unit E and two light receiving units R (R1 and R2), and the intensity spectrum of the detection signal Z generated by the light receiving unit R1 is used as a blood volume index. The intensity spectrum of the detection signal Z generated by the light receiving unit R2 is used for calculating the blood flow index F. However, according to the configuration of the first embodiment in which the detection signal Z generated by the common light receiving unit R is used for calculating the blood volume index M and the blood flow index F, the calculation of the blood volume index M and the blood flow volume are performed. A common intensity spectrum can be used for calculating the index F.

  Modifications 1 to 4 relating to the calculation of the pulse pressure ΔP and Modifications 5 and 6 relating to the calculation of the average blood pressure Pave can be arbitrarily combined.

Second Embodiment
A second embodiment of the present invention will be described. In addition, about the element which an effect | action or function is the same as that of 1st Embodiment in each form illustrated below, the code | symbol used by description of 1st Embodiment is diverted, and each detailed description is abbreviate | omitted suitably.

  FIG. 29 is a configuration diagram of the biological analysis apparatus 100 in the second embodiment. In the first embodiment, the detection signals Z (ZA1, ZB1) generated by the individual detection devices (30A1, 30B1) are used for the calculation of the pulse pressure ΔP and the average blood pressure Pave. In the second embodiment, The detection signal ZC generated by one detection device 30C1 is commonly used for the calculation of the pulse pressure ΔP and the average blood pressure Pave.

  The biological analysis apparatus 100 according to the second embodiment includes a detection unit 30C, a control device 21, a storage device 22, and a display device 23. The detection unit 30C includes a detection device 30C1. The detection device 30C1 has the same configuration as the detection device 30A1 of the detection unit 30A in the first embodiment, and generates a detection signal ZC that represents the light reception level of light that has passed through the measurement site H. A configuration in which the detection device 30C1 is installed at a position facing the arteriole existing inside the measurement site H (for example, the back side of the wrist) is preferable. That is, the detection signal ZC reflecting the state of the arteriole is generated.

  The control device 21 according to the second embodiment includes an index calculation unit 51C, a pulse pressure calculation unit 53, an average blood pressure calculation unit 55, and a blood pressure calculation unit 57. The index calculation unit 51C calculates the blood volume index MC and the blood flow index FC from the detection signal ZC generated by the detection device 30C1. The blood volume index MC is calculated in the same manner as the blood volume index MA1 in the first embodiment, and the blood flow index FC is calculated in the same manner as the blood flow index FA1 in the first embodiment. The pulse pressure calculation unit 53 of the second embodiment calculates the pulse pressure ΔP from the blood volume index MC and the blood flow volume index FC by the same method as in the first embodiment. The average blood pressure calculation unit 55 of the second embodiment calculates the average blood pressure Pave from the blood volume index MC and the blood flow volume index FC by the same method as in the first embodiment. The blood pressure calculation unit 57 of the second embodiment calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin according to the pulse pressure ΔP and the average blood pressure Pave, as in the first embodiment.

  In the second embodiment, the same effect as in the first embodiment is realized. Particularly in the second embodiment, since the detection signal ZC generated by the common detection device 30C1 is used for the calculation of the pulse pressure ΔP and the calculation of the average blood pressure Pave, the calculation of the pulse pressure ΔP and the calculation of the average blood pressure Pave are performed. Compared to a configuration using a detection signal Z generated by a separate detection device, the biological analysis device 100 can be downsized. However, according to the configuration of the first embodiment in which the detection signals Z (ZA1, ZB1) generated by the separate detection devices (30A1, 30B1) are used for the calculation of the pulse pressure ΔP and the average blood pressure Pave, respectively, The detection signal Z reflecting the state of the part suitable for the calculation of the pressure ΔP and the average blood pressure Pave can be generated.

  In the second embodiment, since the blood volume index MC and the blood flow volume index FC calculated by the common index calculation unit 51C and the calculation of the pulse pressure ΔP and the average blood pressure Pave are used, the calculation of the pulse pressure ΔP The processing load for calculating the systolic blood pressure Pmax and the diastolic blood pressure Pmin as compared with the configuration using the blood volume index M and the blood flow volume index F calculated by the separate index calculation unit 51A for calculating the average blood pressure Pave Is reduced.

  In the biological analysis apparatus 100 of the second embodiment, the resistance index is calculated for the elements (detection device 30A5, detection device 30A6, PWV calculation unit 537) for calculating the pulse wave propagation velocity PWV exemplified in FIG. May be replaced with an element for this purpose (resistance calculation unit 533).

  In the second embodiment in which the detection signal ZC generated by the detection device 30C1 is commonly used for the calculation of the pulse pressure Δ and the average blood pressure Pave, the pulse pressure ΔP and the average are obtained by installing the detection device 30C1 near the arteriole. A detection signal ZC suitable for calculating the blood pressure Pave can be generated. When the wrist is the measurement site H, for example, the detection device 30C1 is installed on the surface on the back side of the wrist. When the upper arm is the measurement site H, for example, the detection device 30C1 is installed on the surface of the upper arm opposite to the body.

<Third Embodiment>
FIG. 30 is a configuration diagram of the biological analysis apparatus 100 according to the third embodiment. The biological analysis apparatus 100 according to the third embodiment has a configuration in which an index calculation unit 51D is added to the biological analysis apparatus 100 according to the first embodiment. The detection unit 30A (detection device 30A1) and the calculation unit 51A (index calculation unit 51A1), the detection unit 30B (detection device 30B1) and the calculation unit 51B (index calculation unit 51B1) have the same configuration and configuration as in the first embodiment. It is a function. For example, the detection unit 30A is installed on the palm side of the wrist, and the detection unit 30B is installed on the back side of the wrist.

  The index calculation unit 51D adds or averages each index calculated by the calculation unit 51A and each index generated by the calculation unit 51B. Specifically, the index calculation unit 51D calculates an addition value Madd obtained by adding the blood volume index MA calculated by the calculation unit 51A and the blood volume index MB calculated by the calculation unit 51B. In addition, the index calculation unit 51D calculates an added value Fadd obtained by adding the blood flow rate index FA calculated by the calculation unit 51A and the blood flow rate index FB calculated by the calculation unit 51B. The index calculation unit 51D may calculate an average value obtained by averaging the blood volume index MA and the blood volume index MB and an average value obtained by averaging the blood flow index FA and the blood flow index FB.

The pulse pressure calculation unit 53 of the third embodiment calculates the pulse pressure ΔP using the addition value Madd and the addition value Fadd calculated by the index calculation unit 51D in the same manner as in the first embodiment. Specifically, the pulse pressure calculation unit 53 calculates the amplitude index and the resistance index from the time change of the added value Madd and the time change of the added value Fadd, and calculates the pulse pressure ΔP from the amplitude index and the resistance index. To do. The average blood pressure calculation unit 55 of the third embodiment calculates the average blood pressure Pave using the addition value Madd and the addition value Fadd calculated by the index calculation unit 51D in the same manner as in the first embodiment. Specifically, the average blood pressure calculation unit 55 calculates the average blood pressure Pave according to Fadd / Madd ^4/3 . The blood pressure calculator 57 calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin, as in the first embodiment.

  FIG. 31 is a graph showing a variation coefficient of the average value of the amplitude ΔF over a plurality of analysis periods T and a variation coefficient of the average value of the blood flow index F over a plurality of analysis periods T. In FIG. 31, when the blood flow rate index F is calculated from the detection signal Z generated by one detection device (the detection device installed on the palm side of the wrist and the detection device installed on the back side of the wrist), 2 The case where the blood flow index F calculated from the detection signals generated by the two detection devices is added is illustrated. The coefficient of variation is an index indicating the degree of variation of a plurality of numerical values. Specifically, a ratio between a standard deviation σ calculated from a plurality of measurement values and an average value x obtained by averaging the measurement values of a plurality of times ( σ / x). The smaller the variation coefficient, the smaller the variation in the blood flow index F and the amplitude ΔF. As understood from FIG. 31, in both the amplitude ΔF and the blood flow index F, the variation coefficient of the added value Fadd of the blood flow index F calculated from the two detection signals is the blood flow index calculated from one detection signal. It is smaller than the coefficient of variation of F. Therefore, according to the third embodiment in which the systolic blood pressure Pmax and the diastolic blood pressure Pmin are calculated from the added value obtained by adding the indexes calculated using the two detection devices 30A1 and 30B1, one detection device is generated. The systolic blood pressure Pmax and the diastolic blood pressure Pmin can be calculated with higher accuracy compared to the configuration (for example, the first embodiment) in which each index is calculated using the detected device.

<Fourth embodiment>
FIG. 32 is a schematic diagram illustrating a usage example of the biological analysis apparatus 100 according to the fourth embodiment. As illustrated in FIG. 32, the biological analysis apparatus 100 includes a detection unit 71 and a display unit 72 that are configured separately from each other. The detection unit 71 includes the detection unit 30 (30A, 30B) exemplified in the first embodiment. FIG. 32 illustrates a detection unit 71 that is mounted on the upper arm of the subject. As illustrated in FIG. 33, a detection unit 71 configured to be worn on the wrist of the subject is also suitable.

  The display unit 72 includes the display device 23 exemplified in the above-described embodiments. For example, an information terminal such as a mobile phone or a smartphone is a suitable example of the display unit 72. However, the specific form of the display unit 72 is arbitrary. For example, a wristwatch type information terminal that can be carried by the subject or a dedicated information terminal of the biological analysis device 100 may be used as the display unit 72.

  Elements for calculating the systolic blood pressure Pmax and the diastolic blood pressure Pmin from the detection signal Z (hereinafter referred to as “calculation processing unit”) are mounted on the display unit 72, for example. The calculation processing unit includes the elements illustrated in FIG. 3 (calculation unit 51A, calculation unit 51B, pulse pressure calculation unit 53, average blood pressure calculation unit 55, blood pressure calculation unit 57). A detection signal Z (ZA, ZB) generated by the detection unit 30 of the detection unit 71 is transmitted to the display unit 72 by wire or wirelessly. The arithmetic processing unit of the display unit 72 calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin from the detection signal ZA and the detection signal ZB and displays them on the display device 23.

  Note that the arithmetic processing unit may be mounted on the detection unit 71. The arithmetic processing unit calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin from the detection signal ZA and the detection signal ZB generated by the detection unit 30, and displays data for displaying the systolic blood pressure Pmax and the diastolic blood pressure Pmin. Transmit to the unit 72 by wire or wireless. The display device 23 of the display unit 72 displays the systolic blood pressure Pmax and the diastolic blood pressure Pmin indicated by the data received from the detection unit 71. The fourth embodiment can also be applied to the second embodiment and the third embodiment.

<Fifth Embodiment>
Figure 34 is a graph showing the measured values of the blood amount index M, the relationship between the cube of the blood flow index F of the measured value and the mean blood pressure vessel diameter d2 which is calculated from the measured value of Pave (d2 ^3). The actual measurement value of the blood volume index M and the actual measurement value of the blood flow index F are measured using, for example, a laser Doppler blood flow meter. The average blood pressure Pave is measured using a cuff or the like. Note that FIG. 34 shows the results measured for a plurality of subjects. As described above, since the blood vessel diameter d2 corresponds to the cube root (M ^1/3 ) of the blood volume index M, the following equation (18) is derived from the equation (12). d2 ³ is calculated using Equation (18).

As can be seen from FIG. 34, it has been found that the regression line indicating the relationship between d2 ³ and the measured value of blood volume index M is expressed by a linear function having a slope and an intercept. Assuming that the coefficient representing the slope is a and the coefficient representing the intercept is b, d2 ³ is expressed by the following equation (19). FIG. 34 illustrates a case where the coefficient a is 0.0889 and the coefficient b is 0.0023. It can be seen that there is a high correlation between d2 ³ and the measured value of the blood volume index M, and the correlation is appropriately approximated by the equation (19). The correlation coefficient R2 in FIG. 34 is 0.9488.

On the premise that the cube of the blood vessel diameter d2 corresponds to the blood volume index M and the blood flow index F corresponds to the blood flow volume Q2, the above formula (11) is transformed into the following formula (20). . Note that the symbol K ′ in Expression (20) is a coefficient determined in advance according to the blood density ρ, the length of arteriole L 2, and the like, similarly to the coefficient K in Expression (12).

FIG. 35 is a graph showing a relationship between an actual measurement value of the average blood pressure Pave measured by a cuff or the like and a calculated value of the average blood pressure Pave calculated by the equation (20). There may be a case where a negative correlation is observed between the calculated value of the average blood pressure Pave calculated on the assumption that d2 ³ does not have an intercept and the measured value of the average blood pressure Pave. On the other hand, as can be seen from FIG. 35, a positive correlation was observed between the calculated value of the average blood pressure Pave calculated by the equation (20) and the actual value of the average blood pressure Pave. The correlation coefficient R2 is 0.5858. Based on the above knowledge, in the fifth embodiment, the average blood pressure Pave is calculated using Equation (20). That is, the average blood pressure Pave is calculated according to F _ave / (a × M _ave + b) ^4/3 .

  The coefficient a and the coefficient b in the equation (20) are statistically set using, for example, measured values (average blood pressure Pave, blood volume index M, and blood flow index F) calculated from a plurality of subjects. The coefficient a and the coefficient b may be set for each user of the biological analysis apparatus 100, or the coefficient a and the coefficient b common to the users may be set. When the coefficient a and the coefficient b are set for each user, calibration using the actual measurement value measured for each user is required for the coefficient a and the coefficient b. On the other hand, when a common coefficient a and coefficient b are set among users, there is an advantage that calibration is unnecessary for each user. Note that one of the coefficient a and the coefficient b may be set in common among users, and the other may be set for each user.

As understood from the above description, in the fifth embodiment, the average blood pressure Pave is determined according to F _ave / (a × M _ave + b) ^{4/3 in} which a positive correlation is observed with respect to the actual measurement value of the average blood pressure Pave. Therefore, it is possible to calculate the average blood pressure Pave with high accuracy. Further, when the coefficient a and the coefficient b are set in common among users, there is an advantage that calibration at the time of using the biological analysis apparatus 100 is not necessary. The configuration of the fifth embodiment can be applied to any of the first to fourth embodiments.

<Sixth Embodiment>
The intensity spectrum related to the frequency of the detection signal ZB1 of the first embodiment may include noise (hereinafter referred to as “background noise”) distributed with substantially uniform intensity over the entire area on the frequency axis. The background noise is, for example, shot noise unique to an electric circuit constituting the biological analysis device 100 or noise caused by electromagnetic waves existing in the installation environment of the biological analysis device 100. In the sixth embodiment, the blood volume index M and the blood flow index F are calculated by reducing the background noise from the intensity spectrum specified from the detection signal ZB1.

  The detection device 30B1 according to the sixth embodiment generates a signal representing the background noise (hereinafter referred to as “observation signal”) in addition to the detection signal ZB1 exemplified in the above embodiments. The observation signal is generated in a state where blood flow is not observed. For example, a signal output from the light receiving unit R in a state where the light emitting unit E irradiates light to a stationary object that has low reflectance and does not include a moving object is generated as an observation signal. Note that a signal output from the light receiving unit R without irradiating light to a stationary object may be used as an observation signal. In addition, a signal output from the light receiving unit R in a state where the measurement site H or a position upstream from the measurement site H is stopped with a cuff or the like may be used as an observation signal. As understood from the above description, an observation signal that does not include a component derived from the blood flow of the measurement site H is generated. That is, an observation signal representing the background noise existing when calculating the blood volume index M and the blood flow index F of the measurement site H is generated.

  The index calculation unit 51B1 of the sixth embodiment subtracts the background noise intensity G (f) bg from the intensity G (f) of each frequency f in the intensity spectrum related to the frequency of the detection signal ZB1 to obtain the blood volume index M and A blood flow index F is calculated. The background noise intensity G (f) bg is the intensity at each frequency f in the intensity spectrum calculated from the observed signal. A value obtained by smoothing (for example, moving average) the intensity G (f) bg of the background noise may be subtracted from the intensity G (f). The smoothing of the intensity G (f) bg may be performed on the time axis or the frequency axis.

Specifically, the index calculation unit 51B1 specifies the correction strength G (f) c by subtracting the strength G (f) bg from the strength G (f) for each frequency f. The correction strength G (f) c is expressed by the following formula (21).

  The blood volume index M and the blood flow index F are calculated using the correction strength G (f) c calculated from the equation (21). That is, the blood volume index M and the blood flow volume index F with reduced influence of background noise are calculated. As in the previous embodiments, formula (5a) or formula (5b) is used to calculate blood volume index M, and formula (6a) or formula (6b) is used to calculate blood flow index F. Is done.

  As understood from the above description, in the sixth embodiment, the blood volume index is obtained by subtracting the intensity G (f) bg of the background noise from the intensity G (f) of each frequency f in the intensity spectrum of the detection signal ZB1. M and blood flow index F are calculated. Therefore, the blood volume index M and the blood flow volume index F with reduced influence of background noise are calculated. That is, the average blood pressure Pave can be calculated with high accuracy. In the above description, the average blood pressure Pave is focused on, but the formula (21) is similarly used for the blood volume index M and the blood flow volume index F used for calculating the pulse pressure ΔP. That is, it is possible to calculate the pulse pressure ΔP with high accuracy from the blood volume index M and the blood flow volume index F in which the influence of background noise is reduced.

  As understood from the formula (6a) or the formula (6b), the blood flow index F is obtained by multiplying the frequency f by the intensity G (f) (that is, using the frequency weighted intensity spectrum (f × G (f)). Calculated). Therefore, as the frequency f increases, the influence of background noise on the blood flow index F tends to increase. The configuration of the sixth embodiment that reduces background noise from the intensity spectrum is particularly effective when the blood flow index F is calculated. In addition, the structure of 6th Embodiment can be utilized in order to reduce a background noise about the intensity spectrum of the detection signal detected optically in 1st Embodiment to 5th Embodiment.

<Seventh embodiment>
In the sixth embodiment, in the frequency band (hereinafter referred to as “designated band”) in which the intensity G (f) does not change according to the pulsation of the measurement site H in the intensity spectrum of the detection signal ZB1, if background noise is removed, The intensity G (f) approaches zero. In other words, the closer the intensity G (f) is to 0 in the designated band, the more accurately the background noise is removed. Therefore, in the seventh embodiment, the intensity G (f) bg is subtracted from the intensity G (f) so that the result of subtracting the intensity G (f) bg from the intensity G (f) approaches 0 in the designated band. . The designated band is, for example, a band of 25 kHz to 30 kHz. The designated band is not limited to the above examples. For example, the designated band is appropriately changed according to the type of the measurement site H.

As in the sixth embodiment, the index calculation unit 51B1 of the seventh embodiment subtracts the background noise intensity G (f) bg from the intensity G (f) of each frequency f in the intensity spectrum related to the frequency of the detection signal ZB1. Then, the blood volume index M and the blood flow volume index F are calculated. Specifically, the index calculation unit 51B1 calculates the intensity G (f) bg from the intensity G (f) so that the result of subtracting the intensity G (f) bg from the intensity G (f) in the designated band approaches 0. By subtracting, the correction strength G (f) c is calculated. The correction strength G (f) c of the seventh embodiment is expressed by the following formula (22).

A symbol C in Expression (22) is a coefficient set so that the correction strength G (f) c approaches 0 in the designated band. Specifically, the coefficient C is set so that the value calculated from the following formula (23) is minimum (ideally 0). The symbol fmax in the equation (22) is the upper limit value of the frequency in the designated band, and fmin is the lower limit value of the frequency in the designated band. The coefficient C may be set according to the frequency f. For example, a different coefficient C may be set for each band in which the frequency axis is divided into a plurality.

  As understood from the equation (22), the corrected intensity G (f) c is calculated by subtracting the intensity G (f) bg multiplied by the coefficient C from the intensity G (f). The index calculation unit 51B1 calculates the blood volume index M and the blood flow volume index F by using the correction intensity G (f) c calculated by Expression (22) for each frequency f. As in the previous embodiments, formula (5a) or formula (5b) is used to calculate blood volume index M, and formula (6a) or formula (6b) is used to calculate blood flow index F. Is done.

  FIG. 36 shows a frequency weighted intensity spectrum (f × G () calculated by a configuration (hereinafter referred to as “proportional”) that calculates the corrected intensity G (f) c without multiplying the coefficient C by the intensity G (f) b. It is a graph which shows f) c) and the frequency weighting intensity spectrum (f * G (f) c) calculated from correction | amendment intensity | strength G (f) c by the calculation of Numerical formula (22). As can be seen from FIG. 36, in the configuration of the seventh embodiment, a frequency weighted intensity spectrum (f × G (f) c) in which the background noise is reduced with high accuracy is calculated as compared with the comparative example. In particular, the frequency weighted intensity spectrum (f × G (f) c) is calculated by effectively reducing the background noise on the high frequency side where the influence of the background noise becomes large. That is, it is possible to calculate the blood flow rate index F in which background noise is effectively reduced over the entire frequency axis.

  FIG. 37 is a graph showing the relationship between the calculated value of the average blood pressure Pave calculated in a proportional manner and the actual measured value of the average blood pressure Pave measured with a cuff or the like. FIG. 38 is a graph showing the relationship between the calculated value of average blood pressure Pave calculated in the configuration of the seventh embodiment and the actual value of average blood pressure Pave measured with a cuff or the like. As understood from FIGS. 37 and 38, according to the seventh embodiment, a higher correlation (positive correlation) between the calculated value of the average blood pressure Pave and the actually measured value of the average blood pressure Pave compared to the proportionality. Is observed. In addition, the standard deviation σ of the calculated value of the average blood pressure Pave in FIG. 37 is 22.5 mmHg, whereas the standard deviation σ of the calculated value of the average blood pressure Pave in FIG. 38 is 8.8 mmHg. From the above, it can be seen that according to the seventh embodiment, the average blood pressure Pave can be calculated with high accuracy as compared with the comparative example. In the above description, the average blood pressure Pave is focused on, but the formula (22) is similarly used for the blood volume index M and the blood flow volume index F used for calculating the pulse pressure ΔP.

  In the seventh embodiment, the same effect as in the first embodiment is realized. In the seventh embodiment, as in the sixth embodiment, the blood volume index M and the blood flow volume index F with reduced influence of background noise are calculated. According to the seventh embodiment, in particular, the intensity G (f) bg is subtracted from the intensity G (f) so that the result of subtracting the intensity G (f) bg from the intensity G (f) in the designated band approaches 0. Thus, the blood volume index M and the blood flow volume index F are calculated. Therefore, the blood volume index M and the blood flow volume index F can be calculated by reducing the influence of the background noise with high accuracy as compared with the proportionality.

<Modification>
Each form illustrated above can be variously modified. Specific modifications are exemplified below. Two or more modes arbitrarily selected from the following examples can be appropriately combined.

(1) In the above-described embodiments, the systolic blood pressure Pmax and the diastolic blood pressure Pmin are displayed on the display device 23. However, the pulse pressure ΔP and the average blood pressure Pave used for calculating the systolic blood pressure Pmax and the diastolic blood pressure Pmin are displayed. You may display on the display apparatus 23. FIG. That is, the pulse pressure ΔP and the average blood pressure Pave are used as biological information separate from the systolic blood pressure Pmax and the diastolic blood pressure Pmin.

(2) The type of the detection device that generates the detection signal Z used for calculating the blood volume index M and the absorbance index J used for calculating the pulse pressure ΔP and the average blood pressure Pave is arbitrary. For example, an optical sensor module that emits coherent light or incoherent light to generate a detection signal Z corresponding to the state of the measurement site H, and a pressure sensor that generates a detection signal Z representing the displacement of the surface of the measurement site H Alternatively, an ultrasonic sensor module that generates a detection signal Z corresponding to the state of the measurement site H can be suitably employed. However, there is a configuration in which at least one of the pulse pressure index and the average blood pressure index is calculated according to the blood flow index F calculated from the intensity spectrum related to the frequency of the light reflected and received inside the living body by the laser light irradiation. desirable.

(3) In each of the above-described embodiments, the blood pressure calculation unit 57 calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin, but the indexes calculated by the blood pressure calculation unit 57 are not limited to the systolic blood pressure Pmax and the diastolic blood pressure Pmin. For example, using the calculated systolic blood pressure Pmax and the diastolic blood pressure Pmin, the blood pressure calculating unit 57 uses the indicators (for example, abnormal / high eye / normal, Etc.) may be specified.

(4) In each of the above-described embodiments, as understood from the equation (1), the systolic blood pressure Pmax is calculated by adding the value obtained by multiplying the pulse pressure ΔP by 2/3 to the average blood pressure Pave. ) Is not limited to 2/3. Similarly, for diastolic blood pressure Pmin, in equation (2), pulse pressure ΔP may be multiplied by a coefficient other than 1/3. The systolic blood pressure Pmax is calculated by adding a value obtained by multiplying the pulse pressure ΔP by the first coefficient to the average blood pressure Pave when the coefficient multiplied by the pulse pressure ΔP in the formula (1) is the first coefficient. On the other hand, the diastolic blood pressure Pmin is calculated by subtracting the value obtained by multiplying the pulse pressure ΔP by the second coefficient from the average blood pressure Pave when the coefficient multiplied by the pulse pressure ΔP in the formula (2) is the second coefficient. The Arbitrary values can be set for the first coefficient and the second coefficient.

  Further, the calculation method of the systolic blood pressure Pmax and the diastolic blood pressure Pmin is not limited to the calculation of the above-described mathematical formulas (1) and (2). If the systolic blood pressure Pmax and the diastolic blood pressure Pmin are calculated according to the pulse pressure ΔP and the average blood pressure Pave, a specific calculation method is arbitrary. However, the value obtained by multiplying the pulse pressure ΔP by the first coefficient is added to the average blood pressure Pave to calculate the systolic blood pressure Pmax, and the value obtained by multiplying the pulse pressure ΔP by the second coefficient is subtracted from the average blood pressure Pave. According to the above-described embodiments for calculating the systolic blood pressure Pmin, the value obtained by multiplying the pulse pressure ΔP by the first coefficient is added to the average blood pressure Pave to approximate the systolic blood pressure Pmax, and the second coefficient is applied to the pulse pressure ΔP. The systolic blood pressure Pmax and the diastolic blood pressure Pmin can be calculated with high accuracy by utilizing the tendency that the value obtained by subtracting the multiplied value from the average blood pressure Pave approximates the diastolic blood pressure Pmin.

(5) In each embodiment described above, the pulse pressure calculation unit 53 calculates the pulse pressure ΔP, but the index calculated by the pulse pressure calculation unit 53 is not limited to the pulse pressure ΔP. For example, the pulse pressure calculation unit 53 can calculate, for example, a value calculated by substituting the pulse pressure ΔP into a predetermined function, or a value obtained by multiplying the pulse pressure ΔP by a coefficient. As understood from the above description, the index calculated by the pulse pressure calculation unit 53 is comprehensively expressed as an index related to the pulse pressure ΔP (hereinafter referred to as “pulse pressure index”), and the pulse pressure index includes the pulse pressure ΔP. And both the value calculated using the pulse pressure ΔP.

  Alternatively, the pulse pressure calculation unit 53 may calculate an amplitude index and cause the display device 23 to display the amplitude index. As understood from the above description, the amplitude index and the resistance index calculated by the pulse pressure calculation unit 53 may be presented to the subject as independent indexes. Even in a configuration where the amplitude index or resistance index is calculated as an independent index, cuffs are not necessary in principle, so it is possible to calculate each index with high accuracy while reducing the physical load on the subject. .

(6) In each of the embodiments described above, the pulse pressure calculation unit 53 (resistance calculation unit 533) calculates the ratio (SF / SM) between the blood volume integrated value SM and the blood flow integrated value SF as a resistance index. The value calculated as the index is not limited to the ratio (SF / SM). For example, a configuration for calculating the resistance index by substituting the ratio (SF / SM) into a predetermined function, or a configuration for calculating the resistance index by multiplying the ratio (SF / SM) by a coefficient may be employed. Further, for example, a configuration in which a difference between the blood volume integrated value SM and the blood flow integrated value SF is calculated as a resistance index may be employed. However, according to the configuration in which the resistance index is calculated using the ratio between the blood volume integrated value SM and the blood flow integrated value SF, the ratio between the blood volume integrated value SM and the blood flow integrated value SF is the pulse wave propagation speed. The resistance index can be calculated with high accuracy by utilizing the tendency of correlation.

(7) In each of the embodiments described above, the pulse pressure calculation unit 53 (amplitude calculation unit 531) calculates the ratio (ΔF / ΔM) between the amplitude ΔF and the amplitude ΔM as an amplitude index, but the value calculated as the amplitude index is It is not limited to the ratio (ΔF / ΔM). For example, a configuration for calculating the amplitude index by substituting the ratio (ΔF / ΔM) into a predetermined function, or a configuration for calculating the amplitude index by multiplying the ratio (ΔF / ΔM) by a coefficient may be employed. Further, for example, a configuration in which a difference between the amplitude ΔF and the amplitude ΔM is calculated as an amplitude index may be employed. However, according to the configuration in which the amplitude index is calculated using the ratio between the amplitude ΔF and the amplitude ΔM, the tendency that the ratio (ΔF / ΔM) between the amplitude ΔM and the amplitude ΔF and the blood flow velocity are correlated is used. The amplitude index can be calculated with high accuracy. In addition, the amplitude index can be calculated while reducing the influence of skin thickness.

(8) In each of the above-described embodiments, the pulse pressure calculation unit 53 uses the time change MT of the blood volume index M in one analysis period T for calculation of the pulse pressure ΔP, but blood in each of the plurality of analysis periods T. The time change MT obtained by averaging the time change MT of the quantity index M over a plurality of analysis periods T may be used for calculating the pulse pressure ΔP. As for the blood flow index F, a time change FT obtained by averaging the time changes FT of the blood flow index F in each of the plurality of analysis periods T over the plurality of analysis periods T may be used for calculating the pulse pressure ΔP.

(9) In each of the embodiments described above, the pulse pressure calculation unit 53 (resistance calculation unit 533) normalizes each of the blood volume index M and the blood flow volume index F to a normalization range of 0 or more and 1 or less. If the volume index M and the blood flow volume index F are normalized within a common range, the upper limit value and the lower limit value of the normalization range are arbitrary.

(10) In each embodiment described above, the average blood pressure calculation unit 55 calculates the average blood pressure Pave, but the biological information calculated by the average blood pressure calculation unit 55 is not limited to the above examples. For example, the average blood pressure calculation unit 55 can calculate a value calculated by substituting the average blood pressure Pave into a predetermined function or a value obtained by multiplying the average blood pressure Pave by a coefficient. As understood from the above description, the index calculated by the average blood pressure calculation unit 55 is comprehensively expressed as an index related to the average blood pressure Pave (hereinafter referred to as “average blood pressure index”), and the average blood pressure index includes the average blood pressure Pave. And both the value calculated using the average blood pressure Pave.

(11) In each of the embodiments described above, the average blood pressure calculation unit 55 averages the blood vessel diameter index (blood volume index M or absorbance index J) for the analysis period T and the blood flow index F is averaged for the analysis period T. Although the average blood pressure Pave is calculated according to the average value Fave, the calculation method of the average blood pressure Pave is not limited to the above examples. Further, a configuration in which the time length of the analysis period T for averaging the blood vessel diameter index is different from the time length of the analysis period T for averaging the blood flow index F, or the analysis period T for averaging the blood vessel diameter index and the blood flow index F It is also possible to adopt a configuration in which the analysis period T that averages is not overlapping on the time axis.

  Further, in each of the above-described embodiments, the average blood pressure calculation unit 55 calculates the average value Mave by the average of the plurality of blood volume indexes M within the analysis period T, and calculates the average value Fave by the average of the plurality of blood flow volume indexes F. However, the method for calculating the average value Mave and the average value Fave is not limited to the above examples. For example, the average intensity spectrum may be calculated by averaging a plurality of intensity spectra calculated for different time points in the analysis period T, and the average value Mave and the average value Fave may be calculated by calculation on the average intensity spectrum. Similarly, the average value Jave can also be calculated from the average intensity spectrum. When the average intensity <I2> fluctuates within the analysis period T, there is a possibility that the average blood pressure Pave cannot be calculated properly with the configuration using the average intensity spectrum. Therefore, from the viewpoint of calculating the average blood pressure Pave with high accuracy even when the average intensity <I2> fluctuates, the average value Mave and the average for each time point in the analysis period T as illustrated in the first embodiment described above. A configuration for calculating the value Fave is preferred.

(12) In each of the above-described embodiments, the biological analysis device 100 configured as a single device has been illustrated. However, as illustrated below, a plurality of elements of the biological analysis device 100 can be realized as separate devices. . In the following description, an element for calculating the systolic blood pressure Pmax and the diastolic blood pressure Pmin from the detection signal Z will be referred to as an “arithmetic processing unit 27”. The arithmetic processing unit 27 includes, for example, the elements illustrated in FIG. 3 (the calculating unit 51A, the calculating unit 51B, the pulse pressure calculating unit 53, the average blood pressure calculating unit 55, and the blood pressure calculating unit 57). In other forms than the first embodiment, the arithmetic processing unit 27 includes similar elements.

  In each of the above-described embodiments, the biological analysis apparatus 100 including the detection unit 30 (30A, 30B...) Is exemplified. However, as illustrated in FIG. 39, the detection unit 30 is separated from the biological analysis apparatus 100. Is also envisaged. The detection unit 30 is a portable optical sensor module that is attached to a measurement site H such as a wrist or upper arm of a subject. The biological analysis apparatus 100 is realized by an information terminal such as a mobile phone or a smartphone. The biological analysis apparatus 100 may be realized by a wristwatch type information terminal. The detection signal Z generated by the detection unit 30 is transmitted to the biological analysis apparatus 100 by wire or wireless. The arithmetic processing unit 27 of the biological analyzer 100 calculates the systolic blood pressure Pmax and the diastolic blood pressure Pmin from the detection signal Z and displays them on the display device 23. As understood from the above description, the detection unit 30 can be omitted from the biological analysis apparatus 100.

  In each of the above-described embodiments, the biological analysis apparatus 100 including the display device 23 is illustrated. However, as illustrated in FIG. 40, a configuration in which the display device 23 is separated from the biological analysis device 100 is also assumed. The arithmetic processing unit 27 of the biological analyzer 100 calculates the systolic blood pressure Pmax and the diastolic blood pressure PminP from the detection signal Z, and transmits data for displaying the systolic blood pressure Pmax and the diastolic blood pressure Pmin to the display device 23. To do. The display device 23 may be a dedicated display device, but may be mounted on, for example, an information terminal such as a mobile phone or a smartphone, or a wristwatch type information terminal that can be carried by a subject. The systolic blood pressure Pmax and the diastolic blood pressure Pmin calculated by the arithmetic processing unit 27 of the biological analyzer 100 are transmitted to the display device 23 by wire or wirelessly. The display device 23 displays the systolic blood pressure Pmax and the diastolic blood pressure Pmin received from the biological analysis device 100. As understood from the above description, the display device 23 can be omitted from the biological analysis device 100.

  As illustrated in FIG. 41, a configuration in which the detection unit 30 and the display device 23 are separated from the biological analysis device 100 (arithmetic processing unit 27) is also assumed. For example, the biological analysis apparatus 100 (arithmetic processing unit 27) is mounted on an information terminal such as a mobile phone or a smartphone.

  Note that, in a configuration in which the detection unit 30 and the biological analysis device 100 are separated, the calculation unit 51A can be mounted on the detection unit 30. The blood volume index M and the blood flow volume index F calculated by the calculation unit 51 are transmitted from the detection unit 30 to the biological analyzer 100 by wire or wirelessly. As understood from the above description, the index calculation unit 51A can be omitted from the biological analysis apparatus 100.

(13) In each of the above-described embodiments, the wristwatch-type biological analysis device 100 including the casing unit 12 and the belt 14 has been exemplified. However, the specific configuration of the biological analysis device 100 is arbitrary. For example, a patch type that can be applied to the subject's body, an ear-mounted type that can be attached to the subject's ear, a finger-mounted type that can be attached to the subject's fingertips (for example, a fingernail type), or a head that can be attached to the subject's head Any type of biological analysis apparatus 100 such as a head-mounted type may be employed. Further, a handle-type or grip-type biological analysis apparatus 100 that can measure biological information when the subject holds the hand with the hand may be employed.

(14) In each of the above-described embodiments, the systolic blood pressure Pmax and the diastolic blood pressure Pmin of the subject are displayed on the display device 23, but the configuration for notifying the subject of the systolic blood pressure Pmax and the diastolic blood pressure Pmin is described above. It is not limited to. For example, the systolic blood pressure Pmax and the diastolic blood pressure Pmin can be notified to the subject by voice. In the ear-mounted biological analysis apparatus 100 that can be mounted on the ear of the subject, a configuration in which the systolic blood pressure Pmax and the diastolic blood pressure Pmin are notified by voice is particularly preferable. It is not essential to notify the subject of the pulse pressure ΔP. For example, the systolic blood pressure Pmax and the diastolic blood pressure Pmin calculated by the biological analyzer 100 may be transmitted from the communication network to another communication device. In addition, the systolic blood pressure Pmax and the diastolic blood pressure Pmin may be stored in a storage medium 22 of the biological analyzer 100 or a portable recording medium that can be attached to and detached from the biological analyzer 100.

(15) The biological analysis apparatus 100 according to each embodiment described above is realized by the cooperation of the control device 21 and the program as illustrated above. The program according to a preferred aspect of the present invention can be provided in a form stored in a computer-readable recording medium and installed in the computer. It is also possible to provide a program stored in a recording medium included in the distribution server to a computer in the form of distribution via a communication network. The recording medium is, for example, a non-transitory recording medium, and an optical recording medium (optical disk) such as a CD-ROM is a good example, but a known arbitrary one such as a semiconductor recording medium or a magnetic recording medium This type of recording medium can be included. Note that the non-transitory recording medium includes any recording medium except for a transient propagation signal (transitory, propagating signal), and does not exclude a volatile recording medium.

DESCRIPTION OF SYMBOLS 100 ... Biological analyzer, 12 ... Housing | casing part, 14 ... Belt, 21 ... Control apparatus, 22 ... Memory | storage device, 23 ... Display apparatus, 27 ... Arithmetic processing part, 30A, 30B, 30C ... Detection unit, 30A1-A6, 30B1, 30C1... Detecting device, 51A, 51B. Amplitude calculator, 533 ... resistance calculator, 535 ... pulse pressure calculator, 537 ... PWV calculator, 71 ... detection unit, 72 ... display unit, 90 ... actual product, 91 ... detector, 93 ... processor, E, E1, E2 ... light emitting unit, E0 ... transmitting unit, R, R1, R2 ... light receiving unit, R0 ... receiving unit.

Claims (14)

A pulse pressure calculation unit for calculating a pulse pressure index related to the pulse pressure of a living body;
An average blood pressure calculation unit for calculating an average blood pressure index related to the average blood pressure of the living body;
A blood pressure calculating unit that calculates systolic blood pressure and diastolic blood pressure according to the pulse pressure index and the average blood pressure index;
According to the blood flow index related to the blood flow of the living body calculated from the intensity spectrum related to the frequency of the light reflected and received inside the living body by the laser light irradiation, the pulse pressure index and the average blood pressure index Biological analyzer that at least one of them is calculated. The biological analysis apparatus according to claim 1, wherein the blood flow index is calculated by integrating a product of an intensity of each frequency in the intensity spectrum and the frequency over a predetermined frequency range. The pulse pressure calculation unit is configured to determine the pulse according to a blood volume integrated value obtained by integrating a blood volume index related to the blood volume of the living body over an integration period and a blood flow integrated value obtained by integrating the blood flow index for the integration period. The biological analysis apparatus according to claim 1 or 2, wherein a pressure index is calculated. The biological analysis apparatus according to any one of claims 1 to 3, wherein the average blood pressure calculation unit calculates the average blood pressure index according to a blood vessel diameter index related to a blood vessel diameter of the living body and the blood flow volume index. The biological analysis apparatus according to claim 1, wherein the biological analysis apparatus is attached to an upper arm or a wrist of the living body. A first detection device and a second detection device each including a light emitting unit that irradiates the living body with laser light and a light receiving unit that receives the laser light reflected inside the living body;
The pulse pressure calculation unit calculates the pulse pressure index using a detection signal representing a light reception level by the light receiving unit of the first detection device,
The biological analysis device according to any one of claims 1 to 5, wherein the average blood pressure calculation unit calculates the average blood pressure index using a detection signal indicating a light reception level by the light receiving unit of the second detection device. The biological analysis device according to claim 6, wherein the first detection device and the second detection device are provided at different positions in the circumferential direction of the limb of the living body. The first detection device is installed on a body side surface of the upper arm of the living body,
The biological analysis apparatus according to claim 7, wherein the second detection device is installed on a surface of the upper arm opposite to the body. The first detection device is installed on a palm side surface of the wrist of the living body,
The biological analysis device according to claim 7, wherein the second detection device is installed on a surface on the back side of the wrist. A detection device comprising: a light emitting unit that irradiates the living body with laser light; and a light receiving unit that receives the laser light reflected inside the living body.
The pulse pressure calculation unit calculates the pulse pressure index using a detection signal representing a light reception level by the light receiving unit of the detection device,
The biological analysis apparatus according to claim 1, wherein the average blood pressure calculation unit calculates the pulse pressure index using a detection signal representing a light reception level by the light receiving unit of the detection apparatus. The biological analysis device according to claim 10, wherein the detection device is installed on a surface of the upper arm of the living body opposite to the trunk. The biological analysis apparatus according to claim 10, wherein the detection device is installed on a surface on the back side of the wrist of the living body. Calculate the pulse pressure index related to the pulse pressure of the living body,
Calculating an average blood pressure index related to the average blood pressure of the living body,
A biological analysis method for calculating systolic blood pressure and diastolic blood pressure according to the pulse pressure index and the average blood pressure index,
From an intensity spectrum related to the frequency of light reflected and received inside the living body by irradiation with laser light, at least one of the pulse pressure index and the average blood pressure index is determined according to a blood flow index related to the blood flow of the living body. Calculated biological analysis method. A pulse pressure calculation unit for calculating a pulse pressure index related to the pulse pressure of a living body;
An average blood pressure calculation unit for calculating an average blood pressure index related to the average blood pressure of the living body;
According to the pulse pressure index and the average blood pressure index, a program that causes a computer to function as a blood pressure calculation unit that calculates systolic blood pressure and diastolic blood pressure,
According to the blood flow index related to the blood flow of the living body calculated from the intensity spectrum related to the frequency of the light reflected and received inside the living body by the laser light irradiation, the pulse pressure index and the average blood pressure index A program in which at least one is calculated.

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