JP2019047950A - Detection device, biological information measurement device, biological information measurement method, and program - Google Patents

Abstract

To generate a detection signal reducing an influence of body motion of a living body.SOLUTION: A detection device generating a detection signal utilized for a calculation of oxygen saturation of a living body, comprises: a light-emitting part irradiating the living body with irradiation light having a peak wavelength of 500 nm or more and of 590 nm or less; a first filter transmitting light of a wavelength region having a center wavelength of 560 nm out of the irradiation light reflected inside the living body; a second filter transmitting light of a wavelength region having a center wavelength of 577 nm out of the irradiation light reflected inside the living body; a first light reception part generating a first detection signal corresponding to a light reception level of the light transmitted through the first filter; and second light reception part generating a second detection signal corresponding to a light reception level of the light transmitted through the second filter.SELECTED DRAWING: Figure 3

Description

  The present invention relates to a technique for measuring biological information.

  Various measurement techniques for measuring biological information such as oxygen saturation have been conventionally proposed. For example, Patent Document 1 discloses a configuration in which oxygen saturation is calculated by irradiating a living body with infrared light. Specifically, the oxygen saturation is calculated from the light intensity signal obtained by the light receiving unit that receives the infrared light emitted from the light emitting unit and passing through the living body.

JP, 2016-002167, A

  However, when infrared light is used to calculate oxygen saturation, the light intensity signal is susceptible to body movement. Therefore, there is a problem that the oxygen saturation can not be calculated with high accuracy. In consideration of the above circumstances, the present invention aims to generate a detection signal in which the influence of body movement of a living body is reduced.

  In order to solve the above problems, a detection device according to a preferred embodiment of the present invention is a detection device that generates a detection signal used to calculate the oxygen saturation of a living body, and has a peak wavelength of 500 nm or more in the living body. A light emitting portion for emitting irradiation light of 590 nm or less, a first filter for transmitting light in a wavelength range having a central wavelength of 560 nm among the irradiation light reflected inside the living body, and irradiation light reflected inside the living body Among them, a second filter for transmitting light in a wavelength range having a central wavelength of 577 nm, a first light receiving unit for generating a first detection signal according to the light reception level of light transmitted through the first filter, and a second filter And a second light receiving unit that generates a second detection signal according to the light reception level of the transmitted light. According to the above aspect, since the irradiation light having a peak wavelength of 500 nm or more and 590 nm or less is irradiated to the living body, the influence of the body movement of the living body is reduced as compared with the configuration of irradiating the living body with near infrared light, for example. A detection signal can be generated. Consequently, it is possible to calculate the oxygen saturation with high accuracy. In addition, since the first detection signal and the second detection signal corresponding to the light of different wavelengths are generated from the light emitted from the common light emitting unit, the light emitting units that individually emit the light of different wavelengths are separately provided. Compared with the configuration, miniaturization and power saving of the biological information measuring device are possible. Furthermore, since light in a wavelength range centered on 560 nm and 577 nm, where the difference in absorbance between oxygenated hemoglobin and reduced hemoglobin is large, is transmitted by the first filter and the second filter, respectively, and thus oxygenation in blood It is possible to generate a first detection signal and a second detection signal that further reflect the difference between the states of hemoglobin and reduced hemoglobin. Consequently, it is possible to calculate the oxygen saturation with high accuracy.

  In a preferred embodiment of the present invention, the half-width of the transmission peak of the first filter and the second filter is 27 nm or less. The oxygen saturation can be calculated according to the signal ratio between the signal component ratio of the high band component and the low band component of the first detection signal and the signal component ratio of the high band component and the low band component of the second detection signal. In the configuration in which the half width is 27 nm or less, the signal ratio largely changes with respect to the change in the oxygen saturation of the living body as compared with the configuration in which the half width is larger than 27 nm. Therefore, even if noise is included in the detection signal, it is possible to calculate the oxygen saturation with high accuracy.

  In a preferred embodiment of the present invention, the half width is 13 nm or less. In the configuration in which the half width is 13 nm or less, the signal ratio largely changes with respect to the change in the oxygen saturation of the living body as compared with the configuration in which the half width is larger than 13 nm. Therefore, the effect that the oxygen saturation can be calculated with high accuracy even if noise is included in the detection signal is more remarkable.

  In a preferred aspect of the present invention, each of the above-described detection devices is attached to the upper arm or wrist of a living body. Therefore, the detection device can be easily attached to the living body.

  In the biological information measuring method according to a preferred aspect of the present invention, the received light level of light having a central wavelength of 560 nm in the irradiation light having a peak wavelength of 500 nm or more and 590 nm or less reflected by the computer The oxygen saturation of the living body is calculated from the first detection signal corresponding to the second detection signal according to the light reception level of the light in the wavelength range having a center wavelength of 577 nm among the irradiation light reflected inside the living body .

  A program according to a preferred embodiment of the present invention is a first detection according to the light reception level of light in a wavelength range having a central wavelength of 560 nm among the irradiation light having a peak wavelength of 500 nm to 590 nm reflected inside the living body The computer functions as a calculation unit that calculates the oxygen saturation of the living body from the signal and the second detection signal according to the received light level of the light in the wavelength range whose center wavelength is 577 nm among the irradiation light reflected inside the living body Let

It is a side view of a living body information measuring device concerning a 1st embodiment of the present invention. It is the block diagram which paid its attention to the function of a living body information measuring device. It is a top view of a detecting device. FIG. 4 is a cross-sectional view of the detection device of FIG. 3 taken along line IV-IV. It is a graph showing the absorption spectrum of oxygenated hemoglobin and reduced hemoglobin. It is a graph which shows the relationship between the absorption spectrum in 500 nm-590 nm or less vicinity of oxygenated hemoglobin and reduced hemoglobin, and the transmission characteristic of each filter. It is a graph which shows the relationship of the signal ratio and oxygen saturation which were calculated from the 1st detection signal and the 2nd detection signal about a plurality of cases where the half value width of a filter was changed. It is a graph which shows the relationship between an error index and the half value width of a filter. It is a schematic diagram which shows the usage example of the biometric analyzer which concerns on 2nd Embodiment. It is a schematic diagram which shows the other usage example of the biometric analyzer which concerns on 2nd Embodiment. It is a block diagram of the biometric analyzer in a modification. It is a block diagram of the biometric analyzer in a modification. It is a block diagram of the biometric analyzer in a modification.

First Embodiment
FIG. 1 is a side view of a biological information measurement apparatus 100 according to a first embodiment of the present invention. The biological information measurement apparatus 100 according to the first embodiment is a biological measurement device that noninvasively measures biological information of a subject, and is attached to a site (hereinafter referred to as a “measurement site”) M to be measured in the subject's body. Be done. The biological information measurement apparatus 100 according to the first embodiment is a wristwatch-type portable device including a housing 12 and a belt 14. By winding a belt-like belt 14 around the measurement site M (upper arm or wrist), the biological information measurement device 100 is attached to the subject's wrist. The biological information measurement device 100 according to the first embodiment contacts the surface of the subject's wrist. In the first embodiment, oxygen saturation (SpO2) is illustrated as biological information. Oxygen saturation means the percentage (%) of hemoglobin (oxygenated hemoglobin) bound to oxygen in hemoglobin in the subject's blood.

  FIG. 2 is a block diagram focusing on the function of the biological information measurement apparatus 100. As shown in FIG. The biological information measurement device 100 according to the first embodiment includes a detection device 30, a calculation unit 40, a display device 50, and a storage device 60. The display device 50 (for example, a liquid crystal display panel) is installed on the surface (for example, the surface on the opposite side to the measurement site M) of the housing 12 and displays various images including the measurement result. The calculating unit 40 and the storage device 60 are installed inside the housing unit 12. The calculating unit 40 is realized by an arithmetic processing unit such as a central processing unit (CPU) or a field-programmable gate array (FPGA). The storage device 60 is configured of, for example, a non-volatile semiconductor memory, and stores various data (for example, a table for specifying the oxygen saturation) used by the calculation unit 40.

  The detection device 30 is an optical sensor module that generates a detection signal Z according to the state of the measurement site M, and is installed, for example, on the opposite surface of the housing 12 to the measurement site M. FIG. 3 is a plan view of the detection device 30 as viewed from the measurement site M side, and FIG. 4 is a cross-sectional view of the detection device 30 of FIG. 3 taken along line IV-IV. The detection device 30 includes a housing 31, a light emitting unit 33, a first light receiving unit 35, a second light receiving unit 37, and a protection unit 39. In the housing 31, three housing portions S corresponding to the light emitting portion 33, the first light receiving unit 35, and the second light receiving unit 37 are formed. Each accommodation portion S is a bottomed hole that opens in a surface opposite to the measurement site M. The light emitting portion 33, the first light receiving unit 35, and the second light receiving unit 37 are accommodated in the respective accommodating portions S. The housing 31 is formed of a light shielding material, and the space between the housing portions S is shielded from light.

  The light emitting unit 33 is installed such that the optical axis faces the opening side of the housing unit S (that is, the measurement site M side). The first light receiving unit 35 includes a first filter 351 and a first light receiving unit 353. The first light receiving unit 353 is installed on the bottom surface of the storage unit S, and the first filter 351 is installed to close the opening of the storage unit S. The second light receiving unit 37 includes a second filter 371 and a second light receiving unit 373. The second filter 371 and the second light receiving unit 373 are accommodated in the accommodation unit S in the same manner as the first light receiving unit 35. The protection unit 39 (for example, a glass plate) is installed in the housing 31 so as to cover the surface on the measurement site M side.

  The light emitting unit 33 emits light to a living body (measurement site M). The light emitting unit 33 according to the first embodiment irradiates the living body with irradiation light having a peak wavelength (a wavelength of a peak at which the intensity is maximum when there are a plurality of peaks) in the range of 500 nm to 590 nm. A light emitting element such as an LED (light emitting diode) that emits light in a wavelength range having a peak wavelength in the vicinity of 570 nm is suitably used as the light emitting unit 33.

  The light that has entered the measurement site M from the light emitting unit 33 passes through the inside of the measurement site M, repeats diffuse reflection, and exits to the detection device 30 side. Specifically, the light passing through the blood vessel present inside the measurement site M and the blood in the blood vessel is emitted from the measurement site M to the detection device 30 side. That is, the detection device 30 is a reflective optical sensor in which the light emitting unit 33 and the light receiving unit (35, 37) are positioned on one side with respect to the measurement site M. However, a transmissive optical sensor in which the light emitting unit 33 and the light receiving unit are located on the opposite side of the measurement site M may be used as the detection device 30.

  Each light receiving unit (the first light receiving unit 35, the second light receiving unit 37) generates a detection signal Z according to the light reception level of the light reflected inside the measurement site M. That is, the detection signal Z represents the state of the measurement site M. The emitted light from the measurement site M is incident on the filters (first filter 351 and second filter 371) of each light receiving unit. Each filter is an optical filter that selectively transmits a component in a predetermined pass band (wavelength band) of the irradiation light reflected inside the measurement site M and blocks the other components. For example, a band pass filter having a structure in which a plurality of transmission films having different refractive indexes are stacked is suitable as the first filter 351 and the second filter 371. Details of the transmission characteristics of each filter will be described later. Each filter (351, 371) may be configured by a low pass filter for transmitting light below a predetermined frequency (cutoff frequency) and a high pass filter for transmitting light above the predetermined frequency.

  The light receiving unit (the first light receiving unit 353 and the second light receiving unit 373) of each light receiving unit receives the light transmitted through the filter. Specifically, the light receiving unit generates a detection signal Z according to the light receiving level of the light transmitted through the filter. For example, a light receiving element such as a photodiode (PD: Photo Diode) that generates a charge according to the light receiving intensity is used as the light receiving unit. For example, a silicon (Si) photodiode exhibiting high sensitivity in a wavelength range of 500 nm to 590 nm is suitably used as the light receiving section. The detection device 30 may be, for example, a drive circuit that drives the light emitting unit 33 by supplying a drive current, and an output circuit that amplifies and A / D converts an output signal of the light receiving unit (for example, an amplification circuit and an A / D converter) Although not shown in FIG. 3 and FIG. The light emitting unit 33 may alternately emit light and turn off light in time division to generate the detection signal Z in which the influence of external light is reduced. Specifically, from the signal corresponding to the light reception level of the light emitted from the light emission unit 33, the difference between the signals according to the light reception level of light (that is, the external light) when the light emission unit 33 is extinguished I assume.

  Hereinafter, transmission characteristics of the first filter 351 of the first light receiving unit 35 and the second filter 371 of the second light receiving unit 37 will be described. Here, the oxygen saturation can be measured by receiving the light of two different wavelengths reflected inside the living body. Hereinafter, one of the two wavelengths is referred to as “first wavelength λ1”, and the other wavelength is referred to as “second wavelength λ2”. FIG. 5 is a graph showing the absorption spectra of oxygenated hemoglobin and reduced hemoglobin, and FIG. 6 is a graph showing the relationship between the absorption spectra of oxygenated hemoglobin and reduced hemoglobin and the transmission characteristics of each filter. FIG. 6 shows an absorption spectrum in the vicinity of 500 nm or more and 590 nm or less which is the peak wavelength of the irradiation light. The first wavelength λ1 and the second wavelength λ2 are set so as to reflect the difference in the state (specifically, the concentration) of oxygenated hemoglobin and reduced hemoglobin in blood. Specifically, the first wavelength λ1 and the second wavelength λ2 are set to wavelengths at which the difference in absorbance between oxygenated hemoglobin and reduced hemoglobin is large. As understood from FIG. 6, the first wavelength λ1 is, for example, 560 nm, and the second wavelength λ2 is, for example, 577 nm. Thus, in the first embodiment, the first filter 351 transmits light in a wavelength range having a central wavelength of 560 nm, and the second filter 371 transmits light in a wavelength range having a central wavelength of 577 nm.

  The first light receiving unit 353 of the first light receiving unit 35 generates a first detection signal Z1 according to the light receiving level of the light transmitted through the first filter 351 (that is, the light in the wavelength range whose center wavelength is 560 nm). On the other hand, the second light receiving unit 373 of the second light receiving unit 37 generates the second detection signal Z2 according to the light receiving level of the light transmitted through the second filter 371 (that is, the light in the wavelength range whose center wavelength is 577 nm). .

The calculator 40 of FIG. 2 calculates the oxygen saturation from the first detection signal Z1 and the second detection signal Z2 generated by the detection device 30. A well-known technique can be arbitrarily employ | adopted for calculation of the oxygen saturation by the calculation part 40. FIG. For example, it is possible to specify the degree of oxygen saturation using the correlation between the signal ratio Φ calculated from the detection signals (Z1, Z2) and the degree of oxygen saturation. The signal ratio Φ is a ratio of the signal component ratio X2 to the signal component ratio X1 as expressed by the following equation (1). The signal component ratio X1 is an intensity ratio between the component value Q1 (AC) of the high frequency component of the first detection signal Z1 and the component value Q1 (DC) of the low frequency component. The signal component ratio X2 is an intensity ratio between the component value Q2 (AC) of the high frequency component of the second detection signal Z2 and the component value Q2 (DC) of the low frequency component. The signal ratio Φ in equation (1) and the oxygen saturation correlate with each other.

  The calculation unit 40 calculates the signal ratio か ら from Equation (1) by analyzing the first detection signal Z1 and the second detection signal Z2. Then, the calculation unit 40 refers to a table in which each numerical value of the signal ratio と and each numerical value of the oxygen saturation correspond to each other, and the numerical value corresponding to the calculated signal ratio Φ corresponds to the oxygen saturation of the subject (measurement Identified as a value). The display unit displays the oxygen saturation calculated by the calculation unit 40.

  Here, in the first embodiment, since the oxygen saturation is calculated according to the signal ratio 、, in order to calculate the oxygen saturation with high accuracy, the signal ratio に 対 し て of the change amount of the oxygen saturation is calculated. It is desirable that the amount of change be large. Here, the signal ratio Φ is calculated from the first detection signal Z1 and the second detection signal Z2 as described above, but even if the first detection signal Z1 and the second detection signal Z2 contain noise. When the change amount of the signal ratio Φ is large relative to the change amount of the oxygen saturation, the oxygen saturation can be calculated with high accuracy. FIG. 7 is a graph showing the relationship between the signal ratio Φ calculated from the first detection signal Z1 and the second detection signal Z2 and the oxygen saturation for a plurality of cases in which the half width Δλ of the filter is changed. Here, the half width Δλ of the filter is the width of the wavelength of the peak at a point where the transmittance is half of the maximum transmittance when focusing on one peak in the transmission characteristics of the filter. As understood from FIG. 7, the amount of change of the signal ratio に 対 す る with respect to the amount of change of the oxygen saturation fluctuates according to the half width Δλ of the filter. Specifically, the smaller the filter half width Δλ, the larger the change in the signal ratio に 対 し て relative to the change in oxygen saturation, and the larger the filter half width Δλ, the larger the signal ratio relative to the change in oxygen saturation. The amount of change in Φ is small. As understood from the above description, as the filter half width Δλ is smaller, the oxygen saturation can be calculated with high accuracy even if the detection signal Z contains noise.

  In JIS T 80601-2-61 and ISO 80601-2-61, 2/3 or more of the measured value of oxygen saturation needs to be within ± 4% of the reference value (for example, average value) . Therefore, the conditions for keeping the error of oxygen saturation within ± 4% are examined below.

  FIG. 8 shows the relationship between the amount of change in the signal ratio Φ (hereinafter referred to as “error index”) E and the half width Δλ (horizontal axis) of the filter when the oxygen saturation changes by 4% near 100%. Is illustrated. As understood from FIG. 8, the error indicator E depends on the half width Δλ of the filter. Specifically, the error index E decreases as the filter half width Δλ increases. The smaller the error index E, the larger the amount of change (error) in oxygen saturation relative to the change in the signal ratio Φ. As understood from FIG. 8, the fact that the error index E is 0.01 means that the error of the oxygen saturation is exactly 4% when the signal ratio に な る changes by 0.01. Therefore, when the signal ratio Φ changes by 0.01 under the configuration in which the error index E is less than 0.01, the error of the oxygen saturation exceeds 4%. Conversely, even if the signal ratio が changes by 0.01 under the configuration in which the error index E exceeds 0.01, the error of the oxygen saturation falls below 4%. Considering the above tendency, it is desirable that the numerical value of the error index E be large from the viewpoint of reducing the oxygen saturation error.

  According to a test by the present inventor, the standard deviation σ of the signal ratio Φ is about 0.01. Therefore, if the error index E is 0.01, the error falls within ± 4% for about 2/3 of the measured value of oxygen saturation. That is, it is possible to reduce the error of oxygen saturation within the range of the above-mentioned standard. In consideration of the above knowledge, in the first embodiment, the half width Δλ of the filter is set so that the error index E is 0.01 or more.

  Referring to FIG. 8, the half value width Δλ of the filter when the error index E is 0.01 or more is 27 nm or less. From the above findings, in the first embodiment, the half width Δλ of the filter is set to 27 nm or less. From the viewpoint of suppressing the error of the oxygen saturation, it is desirable to set the half width Δλ of the filter so that the error index E is 0.02 or more. Referring to FIG. 8, since the half width Δλ of the filter when the error index E is 0.02 or more is 13 nm or less, in a more preferable aspect, the half width Δλ of the filter is set to 13 nm or less. As understood from the above description, in the first embodiment, since the half width Δλ of the filter is set to 27 nm or less (more preferably 13 nm or less), it is possible to suppress an error in oxygen saturation. .

  In the first embodiment, irradiation light having a peak wavelength of 500 nm or more and 590 nm or less is irradiated to a living body (measurement site M). Here, it is known that infrared light and near-infrared light have high bio-permeability as compared with irradiation light having a peak wavelength of 500 nm or more and 590 nm or less, and can be incident to a deep position of a living body. Therefore, in the configuration in which the living body is irradiated with infrared light or near infrared light (hereinafter referred to as “comparative example”), there is a problem that the living body is easily influenced by body movement. According to the first embodiment in which the irradiation light with a peak wavelength of 500 nm or more and 590 nm or less is irradiated to the living body, the detection signal Z in which the influence of the body movement of the living body is reduced (that is, less noise) is generated as compared with the comparative example. can do. Consequently, it is possible to calculate the oxygen saturation with high accuracy.

  In the first embodiment, the first detection signal Z1 and the second detection signal Z2 according to light of different wavelengths (first wavelength λ1 and second wavelength λ2) are generated from the light emitted from the common light emitting unit 33 Thus, the size and power saving of the biological information measuring apparatus 100 can be reduced as compared with a configuration in which the light emitting unit that emits the light of the first wavelength λ1 and the light emitting unit that emits the light of the second wavelength λ2 are separately provided. It is. In addition, by setting the first wavelength λ1 and the second wavelength λ2 to 560 nm and 577 nm, respectively, where the difference in absorbance between oxygenated hemoglobin and reduced hemoglobin is large, the difference between the states of oxygenated hemoglobin and reduced hemoglobin in blood can be obtained. The more reflected first detection signal Z1 and the second detection signal Z2 can be generated. Consequently, it is possible to calculate the oxygen saturation with high accuracy.

  Particularly in the first embodiment, since the half width of each filter is set to 27 nm or less (more preferably 13 nm or less), the signal ratio Φ of the living body is smaller than that of the configuration in which the half width of each filter is larger than 27 nm. It changes significantly with changes in oxygen saturation. Therefore, even if the detection signal Z contains noise, it is possible to calculate the oxygen saturation with high accuracy.

Second Embodiment
FIG. 9 is a schematic view showing an example of use of the biological information measurement apparatus 100 in the second embodiment. As illustrated in FIG. 9, the biological information measurement device 100 includes a detection unit 71 and a display unit 72 which are separately configured. The detection unit 71 includes the detection device 30 illustrated in the above-described embodiment. FIG. 10 exemplifies a detection unit 71 mounted on the upper arm of the subject. As illustrated in FIG. 10, a detection unit 71 configured to be worn on the wrist of a subject is also suitable.

  The display unit 72 includes the display device 50 exemplified in the above-described embodiment. For example, an information terminal such as a mobile phone or a smartphone is a preferred example of the display unit 72. However, the specific form of the display unit 72 is arbitrary. For example, a wristwatch-type information terminal portable by a subject or a dedicated information terminal of the biological information measuring apparatus 100 may be used as the display unit 72.

  The calculating unit 40 exemplified in the above-described embodiment is mounted on, for example, the display unit 72. The first detection signal Z1 and the second detection signal Z2 generated by the detection device 30 of the detection unit 71 are transmitted to the display unit 72 in a wired or wireless manner. The calculator 40 of the display unit 72 calculates the oxygen saturation from the first detection signal Z1 and the second detection signal Z2 and displays the oxygen saturation on the display 50.

  The calculating unit 40 may be mounted on the detection unit 71. The calculation unit 40 calculates the oxygen saturation from the first detection signal Z1 and the second detection signal Z2 generated by the detection device 30, and transmits data for displaying the oxygen saturation to the display unit 72 by wire or wirelessly Do. The display device 50 of the display unit 72 displays the oxygen saturation indicated by the data received from the detection unit 71.

<Modification>
Each form illustrated above can be variously deformed. The aspect of a specific deformation | transformation is illustrated below. It is also possible to appropriately merge two or more aspects arbitrarily selected from the following exemplifications.

(1) In the above-mentioned each form, although calculation part 40 calculated oxygen saturation, an index which calculation part 40 calculates is not limited to oxygen saturation. For example, the calculation unit 40 may specify an index (for example, abnormality / high / normal, etc.) indicating the state of the oxygen saturation from the calculated oxygen saturation.

(2) In each embodiment described above, the first wavelength λ1 is 560 nm and the second wavelength λ2 is 577 nm. However, the first wavelength λ1 and the second wavelength λ2 are not limited to the above examples. The first wavelength λ1 and the second wavelength λ2 are arbitrary as long as they can generate the detection signal Z reflecting the difference between the states of oxygenated hemoglobin and reduced hemoglobin in blood.

(3) In each of the above-described embodiments, the biological information measurement apparatus 100 configured as a single device is illustrated, but as illustrated below, a plurality of elements of the biological information measurement apparatus 100 are realized as separate devices. It can be done.

  In each of the above-described embodiments, the biological information measurement device 100 including the detection device 30 is illustrated. However, as illustrated in FIG. 11, a configuration in which the detection device 30 is separated from the biological information measurement device 100 is also assumed. . The detection device 30 is, for example, a portable optical sensor module mounted on a measurement site M such as the subject's wrist or upper arm. The biological information measuring device 100 is realized by an information terminal such as a mobile phone or a smartphone. The biological information measuring device 100 may be realized by a wristwatch type information terminal. The detection signal Z (Z1, Z2) generated by the detection device 30 is transmitted to the biological information measurement device 100 by wire or wirelessly. The calculating unit 40 of the biological information measuring device 100 calculates the oxygen saturation from the detection signal Z and displays it on the display device 50. As understood from the above description, the detection device 30 can be omitted from the biological information measurement device 100.

  Although the biological information measuring device 100 having the display device 50 is illustrated in each of the above-described embodiments, a configuration in which the display device 50 is separated from the biological information measuring device 100 is also assumed as illustrated in FIG. . The calculating unit 40 of the biological information measuring device 100 calculates the oxygen saturation from the detection signal Z, and transmits data for displaying the oxygen saturation to the display device 50. The display device 50 may be a dedicated display device, but may be mounted on, for example, an information terminal such as a mobile phone or a smart phone, or a watch-type information terminal portable by a subject. The oxygen saturation calculated by the calculating unit 40 of the biological information measuring device 100 is transmitted to the display device 50 by wire or wirelessly. The display device 50 displays the degree of oxygen saturation received from the biological information measurement device 100. As understood from the above description, the display device 50 can be omitted from the biological information measurement device 100.

  As exemplified in FIG. 13, a configuration in which the detection device 30 and the display device 50 are separated from the biological information measurement device 100 (calculation unit 40) is also assumed. For example, the biological information measurement device 100 (calculation unit 40) is mounted on an information terminal such as a mobile phone or a smartphone.

  The calculating unit 40 may be mounted on the detection device 30 in a configuration in which the detection device 30 and the biological information measurement device 100 are separated. The oxygen saturation calculated by the calculation unit 40 is transmitted from the detection device 30 to the biological information measurement device 100 by wire or wireless. As understood from the above description, the calculating unit 40 can be omitted from the biological information measuring device 100.

(4) In the first embodiment, the wristwatch-type biological information measuring apparatus 100 including the housing unit 12 and the belt 14 is illustrated, but the specific form of the biological information measuring apparatus 100 is arbitrary. For example, a patch type that can be applied to the subject's body, an ear worn type that can be worn on the subject's ear, a finger worn type that can be worn on the subject's fingertip (for example, nailed), or can be worn on the subject's head Any form of biological information measurement apparatus 100 such as a head-mounted type can be employed.

(5) In the above-mentioned each form, although the test subject's oxygen saturation was displayed on the display apparatus 50, the structure for alerting a test subject to oxygen saturation is not limited to the above illustration. For example, it is also possible to notify the subject of the oxygen saturation by voice. In the ear-worn type biological information measuring apparatus 100 that can be attached to the subject's ear, a configuration in which the oxygen saturation is notified by voice is particularly preferable. Moreover, it is not essential to notify the subject of the oxygen saturation. For example, the oxygen saturation calculated by the biological information measurement device 100 may be transmitted from the communication network to another communication device. In addition, the oxygen saturation may be stored in a storage device 60 of the biological information measurement device 100 or a portable recording medium that is removable from the biological information measurement device 100.

(6) The biological information measurement apparatus 100 according to each of the above-described embodiments is realized by the cooperation of a computer such as a CPU and a program, as described above. The program according to the preferred embodiment of the present invention may be provided in the form of being stored in a computer readable recording medium and installed on the computer. Moreover, it is also possible to provide a computer stored in a recording medium of the distribution server in the form of distribution via a communication network. The recording medium is, for example, a non-transitory recording medium, and is preferably an optical recording medium (optical disc) such as a CD-ROM, but any known medium such as a semiconductor recording medium or a magnetic recording medium may be used. Recording media of the form Note that non-transitory recording media include any recording media except transient propagation signals, and do not exclude volatile recording media.

DESCRIPTION OF SYMBOLS 100 ... Biological information measuring apparatus, 12 ... Housing | casing part, 14 ... Belt, 30 ... Detection apparatus, 40 ... Calculation part, 50 ... Display apparatus, 60 ... Storage apparatus, 31 ... Housing | casing, 33 ... Light emission part, 35 ... The 4th 1 light receiving unit, 351 ... first filter, 353 ... first light receiving unit, 37 ... second light receiving unit, 371 ... second filter, 373 ... second light receiving unit, 39 ... protection unit, 71 ... detection unit, 72 ... display unit.

Claims (7)

A detection device that generates a detection signal used to calculate the oxygen saturation of a living body, comprising:
A light emitting unit for irradiating the living body with irradiation light having a peak wavelength of 500 nm or more and 590 nm or less;
A first filter for transmitting light in a wavelength range having a central wavelength of 560 nm among the irradiation light reflected inside the living body;
A second filter for transmitting light in a wavelength range having a center wavelength of 577 nm among the irradiation light reflected inside the living body;
A first light receiving unit that generates a first detection signal according to a light reception level of light transmitted through the first filter;
And a second light receiving unit configured to generate a second detection signal according to a light reception level of light transmitted through the second filter. The detection device according to claim 1, wherein a half width of each of the first filter and the second filter is 27 nm or less. The detection device according to claim 2, wherein a half width of each of the first filter and the second filter is 13 nm or less. The detection device according to any one of claims 1 to 3, wherein the detection device is attached to the upper arm or the wrist of the living body. The detection device according to any one of claims 1 to 4.
A biological information measuring device comprising: a calculating unit that calculates an oxygen saturation level from the first detection signal generated by the detection device and the second detection signal. The computer is
The first detection signal according to the light reception level of the light of the wavelength range whose center wavelength is 560 nm among the irradiation light having a peak wavelength of 500 nm or more and 590 nm or less reflected inside the living body and the irradiation reflected inside the living body A biological information measurement method for calculating the oxygen saturation of a living body from a second detection signal according to the light reception level of light in a wavelength range where the center wavelength is 577 nm among light. The first detection signal according to the light reception level of the light of the wavelength range whose center wavelength is 560 nm among the irradiation light having a peak wavelength of 500 nm or more and 590 nm or less reflected inside the living body and the irradiation reflected inside the living body A program that causes a computer to function as a calculation unit that calculates the oxygen saturation of a living body from a second detection signal according to the light reception level of light in a wavelength range where the center wavelength is 577 nm among light.

Images