JP5447942B2 - Biological information measuring instrument, electronic device having biological information measuring instrument, biological information measuring method, and biological information measuring program - Google Patents

Description

  The present invention relates to a technique for measuring water content on the skin surface of a living body.

  With the progress of IT (Information Technology) and network technology, the amount of information handled by electronic devices and the amount of stored information are steadily increasing. In addition, as electronic parts become lighter, thinner, and smaller, small electronic devices such as mobile phones and notebook PCs have become widespread and convenience has increased.

  Under these circumstances, obtaining information accurately from sensors that are input devices, and allowing people to recognize it as useful information that has been accurately analyzed, judged, and processed can create a safe, secure, comfortable, and environmentally friendly society. It is in an important position in forming.

  In addition, with the aging of society as society matures, there is a demand for the realization of a health sensor that can measure biometric information on the skin where health and aging are prominent at a low cost, simply and accurately, regardless of location. A health information service by an electronic device equipped with a biosensor satisfies the above-mentioned demand.

  In this regard, biological information associated with health and aging includes the amount of water associated with sweating stored in human skin or secreted from the skin surface. It is generally known that a person's water content is closely related to a person's health and psychological state, such as fatigue and stress.

  As a method for measuring the amount of moisture as biological information of the human skin, an invention of an apparatus using a capacitive moisture sensor has been disclosed (for example, see Patent Document 1).

  In the invention described in Patent Document 1, as shown in FIG. 17, a pair of cross comb-like electrodes 53 facing in a plane are formed on the surface of the square insulating substrate 52, and the capacitance type A moisture sensor 51 is formed. FIG. 17 is a diagram corresponding to FIG.

  And the water content contained in skin can be measured by knowing the change in the electrostatic capacity when the human skin touches the surface of the cross comb electrode using such a configuration.

Japanese Patent Laid-Open No. 2005-52212

  As described above, the moisture content of the skin can be measured by using the moisture sensor. However, the general moisture sensor as described above has the following problems.

  The first problem is that the moisture content of the skin cannot be measured accurately. One reason for this is that when measuring the moisture content of human skin, the degree of contact between the skin and the sensor differs from measurement to measurement, and the values differ and become inaccurate. Furthermore, another reason is that the temperature of the skin rises and the components of the skin fall off and adhere due to friction caused by contact between the electrode and the skin during measurement.

  Next, as a second problem, electronic devices and health information services that accurately capture skin aging and aging information, process it into useful information for the user, and convey it to the user have not been realized. There are also challenges. This is because there is no moisture sensor that accurately measures the amount of moisture as described above.

  Then, this invention aims at providing the biological information measuring device which can measure the moisture content of skin correctly, the electronic device which has a biological information measuring device, a biological information measuring method, and a biological information measuring program. .

According to the first aspect of the present invention, in the biological information measuring instrument for measuring the moisture content of the skin, the sensor has an electrode formed on the substrate and measures the charge amount of the skin in contact with the electrode. And an oscillating means for applying an AC signal to the sensor, and an AC voltage signal that is output in proportion to the amount of charge measured until the sensor leaves the electrode after the skin comes into contact with the electrode. the amount of charge based on the DC voltage signal sequentially stored in every predetermined time, a charge amount adding means for calculating the total amount of by Ri electric load amount by adding the amount of charge the stored, said charge amount adding means Based on the average charge amount calculating means for calculating the average charge amount per unit time by dividing the calculated total amount of charge by the measurement time, and the average charge amount calculated by the average charge amount calculation means, Moisture amount for calculating the moisture content of the skin Biological information measuring device, characterized in that it comprises means out, is provided.

According to a second aspect of the present invention, you accumulate in mounting electronic apparatus biological information measurement device provided, the amount of water the biological information measuring device is calculated by the first aspect of the present invention e Bei means, electronic apparatus, characterized by presenting information about the time-aging of the water content on the basis of the quantity of water before Ki蓄 product is provided.

According to the third aspect of the present invention, in the biological information measuring method for measuring the moisture content of the skin, the sensor has an electrode formed on the substrate and measures the charge amount of the skin in contact with the electrode. And an oscillation step of applying an AC signal to the sensor, and an AC voltage signal that is output in proportion to the amount of charge measured until the sensor leaves the electrode after the skin contacts the electrode. the charge amount based on the rectified-obtained DC voltage signal sequentially stored at predetermined time intervals, the charge amount adding step of calculating the total amount of by Ri electric load amount by adding the amount of charge the storage, the charge An average charge amount calculating step for calculating an average charge amount per unit time by dividing the total amount of the charge amount calculated in the amount adding step by a measurement time; and the average charge calculated in the average charge amount calculating step. Based on the amount of charge, the biological information measuring method characterized by and a water amount calculating step of calculating the moisture content of the skin is provided.

According to a fourth aspect of the present invention, in the biological information measurement program for measuring the moisture content of the skin, the sensor has an electrode formed on the substrate and measures the charge amount of the skin in contact with the electrode And an oscillating means for applying an AC signal to the sensor, and an AC voltage signal that is output in proportion to the amount of charge measured until the sensor leaves the electrode after the skin comes into contact with the electrode. the amount of charge based on the DC voltage signal sequentially stored in every predetermined time, a charge amount adding means for calculating the total amount of by Ri electric load amount by adding the amount of charge the stored, said charge amount adding means Based on the average charge amount calculating means for calculating the average charge amount per unit time by dividing the calculated total amount of charge by the measurement time, and the average charge amount calculated by the average charge amount calculation means, Calculate the moisture content of the skin Biological information measuring program for causing a computer to function as a biological information measuring device comprising a water amount calculation means, is provided.

  According to the present invention, since the average amount of charge per unit time is calculated, and the amount of moisture can be calculated from the average amount of charge, the amount of moisture in the skin can be accurately measured.

It is a figure showing the basic composition of the embodiment of the present invention. It is a figure showing about basic operation of an embodiment of the present invention. It is a figure explaining the relationship between the measurement time and output voltage of embodiment of this invention. It is a figure showing about the sensor 10 in Example 1 of this invention. It is a figure showing about the sensor 10 in Example 2 of this invention. It is a figure showing about the sensor 10 in Example 3 of this invention. It is a figure showing about the sensor 10 in Example 4 of this invention. It is a figure showing about the sensor 10 in Example 5 of this invention. It is a figure showing about the sensor 10 in Example 6 of this invention. It is a figure showing about the sensor 10 in Example 7 and 8 of this invention. It is a figure showing about the sensor 10 in Example 9 of this invention. It is a figure showing about the motion of the measuring object in the Example of this invention. It is a figure showing about the electronic device 110 which is embodiment of this invention. It is a figure (1/3) showing about the maximum fluctuation rate in the Example of this invention. It is a figure (2/3) showing about the maximum fluctuation rate in the Example of this invention. It is a figure (3/3) showing about the maximum fluctuation rate in the Example of this invention. It is a figure for demonstrating the invention described in cited reference.

  Next, embodiments and examples of the present invention will be described in detail with reference to the drawings. In the configuration of each embodiment and example described below, the same structure is denoted by the same reference numeral, and redundant description is omitted. In the following description of the embodiments and examples, each dimension is described with specific numerical values, but these numerical values are merely examples. Embodiments of the present invention are not limited to these illustrated dimensions, and can be realized with any dimensions.

  Further, in the present embodiment and examples, for convenience, the measurement target is assumed to be a human body, but this does not limit the measurement targets of the present embodiment and examples. In the present embodiment and examples, the skin of animals other than human beings can be measured.

  Referring to FIG. 1, the embodiment of the present invention includes a sensor 10, an oscillating unit 11, a charge amount adding unit 12, an average charge amount calculating unit 13, and a moisture amount calculating unit 14.

  The sensor 10 has a function of measuring the amount of charge on the skin. The oscillation unit 11 has a function of applying an AC signal to the sensor 10.

  The charge amount adding unit 12 has a function of sequentially storing and storing the charge amount measured by the sensor 10 at regular intervals until the skin comes into contact with the electrode and then leaves. Further, the charge amount adding unit 12 has a function of adding the stored and stored charge amount. Thereby, the charge amount addition unit 12 can calculate the total amount of charge measured within the measurement time (hereinafter, referred to as “total charge amount” as appropriate).

  The average charge amount calculation unit 13 has a function of calculating the average charge amount per unit time by dividing the total charge amount calculated by the charge amount addition unit 12 by the measurement time. In addition, there is no restriction | limiting in particular about the length of specific measurement time and unit time, It can set to arbitrary length according to use environment etc.

  The moisture amount calculation unit 14 has a function of calculating the moisture amount from the average charge amount calculated by the average charge amount calculation unit 13. Note that any calculation method can be used as the method for calculating the amount of water based on the charge amount, and the description is omitted because it is not the gist of the present invention.

  Next, the operation of this embodiment will be described using the flowchart of FIG.

  First, the oscillation unit 11 applies an AC signal to the sensor 10 (step S201).

  Next, the sensor 10 starts measuring the amount of charge on the skin (step S202).

  Then, along with the measurement, the charge amount adding unit 12 sequentially stores and stores the charge amount measured by the sensor 10 at regular intervals. The stored charge amount is also added (step S203).

  The measurement and the addition of the charge amount in step S202 and step S203 are continued until the measurement time ends (NO in step S204).

  On the other hand, when the measurement time ends (YES in step S204), the average charge amount calculation unit 13 calculates the average charge amount per unit time by dividing the total charge amount calculated by the charge amount addition unit 12 by the measurement time. (Step S205).

  Finally, the moisture amount calculation unit 14 calculates a moisture amount from the average charge amount calculated by the average charge amount calculation unit 13 (step S206).

  Next, the relationship between the measurement time and the output voltage in this embodiment will be described with reference to FIG.

  As shown in FIG. 3, an AC voltage signal 20 output in proportion to the amount of charge that can be accumulated between the electrodes when the skin comes into contact with the electrodes is rectified to obtain a DC voltage signal 21.

  This time, the determination of the start and end of measurement was made when the DC voltage signal 21 was 100 mV or more, and when the DC voltage signal 21 was less than 100 mV, the measurement end threshold was set. Here, the AC signal output from the oscillation unit 11 was 1 kHz and 1 Vrms. In addition, the specific numerical value shown by the present Example and the following Example is an illustration to the last.

  As shown in FIG. 3, the amount of charge measured by the sensor 10 is sequentially stored at regular intervals until the skin comes into contact with the electrode and then leaves, and the stored amount of charge is added and divided by the measurement time. By calculating the average charge amount per unit time, the difference in the degree of contact between the electrode and the skin can be reduced. Therefore, the amount of moisture can be accurately measured.

  Next, an example is shown and demonstrated for every specific shape of the sensor 10 of the above-mentioned embodiment.

  The structure of the sensor 10 in the first embodiment is such that a pair of opposing electrodes 32 are formed on a sensor substrate 31 as shown in FIG. Also shown are electrode terminals 30a and 30b.

  Here, as a mounting example, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are the width (a): 0.25 mm, Length (W): 9 mm and distance between electrodes (p): 0.25 mm.

  FIG. 14 shows the fluctuation rate of the measured value of the moisture content of the skin according to this example. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 14, in this example, compared with a general moisture sensor, an accurate measurement result with less fluctuation for each measurement was obtained.

  Here, the “general moisture sensor” refers to a moisture sensor to which the embodiments and examples in this specification are not applied. Moreover, the case where this general moisture sensor is used in each figure is described as “general example”.

  As shown in FIG. 5, the structure of the sensor 10 according to the second embodiment is such that a plurality of opposing cross comb electrodes 33 are formed on a sensor substrate 31. Also shown are electrode terminals 30a and 30b. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, distance between electrodes (p): 0.25 mm, number of electrode pairs: 4 pairs.

  The amount of charge accumulated between the opposing electrodes increases as the number of opposing electrodes increases. Therefore, as shown in FIG. 5, by forming a plurality of opposing cross comb electrodes on the sensor substrate 31, the amount of charge measured by the sensor 10 increases. Therefore, the amount of moisture can be accurately measured.

  FIG. 14 shows the fluctuation rate of the measured value of the moisture content of the skin according to this example. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 14, in this embodiment, an accurate measurement result with less fluctuation for each measurement is obtained as compared with a general moisture sensor.

  As shown in FIG. 6, the structure of the sensor 10 in the third embodiment is such that a pair of opposing electrodes 32 that are curved are formed on a sensor substrate 31. Also shown are electrode terminals 30a and 30b. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, and distance between electrodes (p): 0.25 mm.

  As shown in FIG. 6, the electrodes and the skin are smoothly in contact with each other by forming the opposing electrodes in a curved shape. Therefore, the friction at the time of contact between the electrode and the skin is reduced, and the temperature rise caused by the friction can be suppressed. Therefore, the amount of moisture can be accurately measured.

  FIG. 14 shows the fluctuation rate of the measured value of the moisture content of the skin according to this example. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 14, in this example, compared with a general moisture sensor, an accurate measurement result with less fluctuation for each measurement was obtained.

  The structure of the sensor 10 in the fourth embodiment is such that a plurality of curved crossing comb electrodes 33 facing each other are formed on a sensor substrate 31 as shown in FIG. Also shown are electrode terminals 30a and 30b. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, distance between electrodes (p): 0.25 mm, number of electrode pairs: 4 pairs.

  As shown in FIG. 7, by forming a plurality of opposing cross comb electrodes on the sensor substrate 31, the amount of charge measured by the sensor 10 increases. Furthermore, by making the opposing electrodes have a curved shape, the electrodes and the skin are in smooth contact. Therefore, the friction at the time of contact between the electrode and the skin is reduced, and the temperature rise caused by the friction can be suppressed. Therefore, the amount of moisture can be accurately measured.

  FIG. 14 shows the fluctuation rate of the measured value of the moisture content of the skin according to this example. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 14, in this example, compared with a general moisture sensor, an accurate measurement result with less fluctuation for each measurement was obtained.

  As shown in FIG. 8, the structure of the sensor 10 in the fifth embodiment is such that a plurality of opposing cross comb electrodes 33 are formed on a sensor substrate 31, and the electrodes to be formed have a distance between the electrodes of the opposing electrodes. , Gradually spread in the opposite direction. Also shown are electrode terminals 30a and 30b. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, minimum distance between electrodes: 0.1 mm, number of electrode pairs: 4 pairs, and the distance between the electrodes was gradually increased with the rate of change shown in FIG.

  Further, as shown in FIG. 12, as a measurement method, the skin is moved in the opposite electrode direction, that is, in one direction until the skin comes in contact with the electrode and then leaves, and the measurement is performed.

  The amount of charge accumulated between the electrodes facing each other is inversely proportional to the distance between the electrodes. Therefore, when the distance between the electrodes is increased, the amount of charge accumulated between the electrodes decreases. Therefore, as shown in FIG. 8, the amount of charge accumulated between specific electrodes can be increased or decreased by locally changing the interelectrode distance of the electrodes 33 formed on the sensor substrate 31. On the other hand, when the skin first comes into contact with the electrode, the skin is caught on the electrode, and the measured value fluctuates due to the skin falling off. Therefore, the distance between the electrodes at the electrode ends was increased. Thereby, the moisture content can be accurately measured.

  FIG. 14 shows the fluctuation rate of the measured value of the moisture content of the skin according to this example. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 14, in this example, as the rate of change in the distance between the electrodes increased, an accurate measurement result with little fluctuation for each measurement was obtained.

  As shown in FIG. 9, the structure of the sensor 10 according to the sixth embodiment is such that a pair of opposing electrodes 32 are formed on a sensor substrate 31 and the opposing electrodes are formed at positions where the opposing electrodes are formed. The concave shape 34 is formed on the surface. Also shown are electrode terminals 30a and 30b. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, distance between electrodes (p): 0.25 mm, and the concave curvature (κ) was changed at 20 m−1 <κ <100 m−1.

  As shown in FIG. 9, this invention has the concave shape 34 in the thickness direction of a board | substrate in the position which forms the electrode which opposes. Due to this concave shape, the entire surfaces of the opposing electrodes are in contact with each other along the skin of the portion having the curvature of the person. This eliminates a non-contact portion between the skin and the electrode, and serves as a guide path when moving the skin on the electrode. Therefore, the amount of moisture can be accurately measured.

  In FIG. 16, the fluctuation rate of the measured value of the moisture content of the skin by a present Example is shown. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 16, in this example, the fluctuation decreased as the concave curvature increased. When the curvature of the skin coincided, the fluctuation decreased most, and an accurate measurement result with little fluctuation for each measurement was obtained. Thereafter, when the curvature is further increased, the non-contact surface between the electrode and the skin increases, so that the fluctuation increases.

  As shown in FIG. 10, the structure of the sensor 10 in the seventh embodiment includes a plurality of curved crossing comb electrodes 33 opposed to each other on a sensor substrate 31, and the formed electrodes are between the electrodes of the opposed electrodes. The distance is gradually increased in the facing direction, and the concave shape 34 is formed in the thickness direction of the substrate at the position where the opposing electrodes are formed. Also shown are electrode terminals 30a and 30b. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, minimum interelectrode distance: 0.1 mm, change rate of interelectrode distance: 25%, concave curvature (κ): 60 m−1.

  In FIG. 16, the fluctuation rate of the measured value of the moisture content of the skin by a present Example is shown. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 16, in this example, compared with a general moisture sensor, an accurate measurement result with less fluctuation for each measurement was obtained.

  In the sensor 10, the larger the difference between the dielectric constant of the substrate on which the electrode is formed and the dielectric constant of human skin, the greater the amount of charge that can be accumulated between the opposing electrodes when the skin contacts the electrode. Therefore, a dielectric constant of 10 or less is desirable as a sensor substrate to be used. Further, since the amount of charge that can be accumulated between the electrodes is inversely proportional to the distance, the amount of charge decreases as the distance between the electrodes increases. Accordingly, the distance between the electrodes is preferably 1 mm or less in practice.

  As shown in FIG. 10, the sensor 10 according to the eighth embodiment has a plurality of curved cross comb electrodes 33 opposed to each other on a sensor substrate 31, and the formed electrodes are between the electrodes of the opposed electrodes. The distance is gradually widened in the facing direction, and a concave shape is formed in the thickness direction of the substrate at a position where the opposing electrodes are formed. Also shown are electrode terminals 30a and 30b. Further, the water repellent film 100 was formed on the sensor substrate 31 and the cross comb electrode 33. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, minimum interelectrode distance: 0.1 mm, change rate of interelectrode distance: 25%, concave curvature (κ): 60 m−1, and PTFE (Polytetrafluoroethylene) was used for the water repellent film.

  As shown in FIG. 12, as a measurement method, the skin that is moved in the opposite electrode direction, that is, in one direction from when the skin comes into contact with the electrode until the skin is separated, is measured.

  As shown in FIG. 11, the friction when moving the skin on the electrode can be reduced. Accordingly, it is possible to suppress sweating caused by the skin temperature increase caused by friction between the electrode and the skin, and to suppress the skin dropout and adhesion to the sensor surface as shown in FIG. Therefore, the amount of moisture can be accurately measured.

  FIG. 14 shows the fluctuation rate of the measured value of the moisture content of the skin according to this example. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 14, in this example, compared with a general moisture sensor, an accurate measurement result with less fluctuation for each measurement was obtained.

  As shown in FIG. 11, the structure of the sensor 10 in Example 9 is formed by forming a plurality of curved crossing comb electrodes 33 opposite to each other on the sensor substrate 31 and forming electrodes between the electrodes of the opposing electrodes. The distance is gradually increased in the facing direction, and the concave shape 34 is formed in the thickness direction of the substrate at the position where the opposing electrodes are formed. Also shown are electrode terminals 30a and 30b. Further, the water repellent film 100 was formed on the sensor substrate 31 and the cross comb electrode 33. Here, a low dielectric constant substrate having an outer dimension of □ 100 mm, a thickness (t): 1 mm and a dielectric constant of 7 is used for the substrate 31, and the electrode dimensions are as follows: width (a): 0.25 mm, length ( W): 9 mm, minimum interelectrode distance: 0.1 mm, change rate of interelectrode distance: 25%, concave curvature (κ): 60 m−1, and PTFE was used as the water repellent film.

  As shown in FIG. 12, by measuring the skin moving in the opposite electrode direction, that is, in one direction, until the skin comes in contact with the electrode, the water content in a wide range of skin is measured. Can be measured. Therefore, the amount of moisture can be accurately measured.

  FIG. 14 shows the fluctuation rate of the measured value of the moisture content of the skin according to this example. The measurement conditions were that the same part of the skin was measured 20 times in an environment where the temperature and humidity were kept constant. Moreover, the measurement result normalized each measured value with the first measured value. As shown in FIG. 14, in this Embodiment, compared with the general moisture sensor, the exact measurement result with few fluctuation | variations for every measurement was obtained.

  As an embodiment using the sensor of each example described above, an embodiment like the electronic device 110 shown in FIG. 13 is conceivable.

  In this embodiment, the sensor 10 is mounted at the position shown in FIG. 13, and the electronic circuit 114 and the storage device 112 are mounted on the main board 113 inside the casing 111 of the electronic device 110. Note that the storage device and the prediction device may be provided in different electronic devices via a network, and are not necessarily limited to electronic devices used for measurement. By utilizing the biological information measuring instrument according to the present invention, the moisture content of the skin can be accurately measured. The electronic circuit 114 and the storage device 112 cooperate to store the moisture content. The electronic circuit 114 and the storage device 112 cooperate to accumulate the stored amount of water, and accurately transmit the aging and secular change of the human body to the user based on the accumulated amount of water. In addition, for the presentation to the user, a display unit may be further provided in the electronic device 110, and information on aging and secular change may be displayed on the display unit. Further, information on aging / aging change may be transmitted to another device, and the other device may display information on aging / aging change.

  Thus, the convenience of the user is improved because the information about the aging and the secular change is displayed.

  The electronic apparatus having the biological information measuring instrument according to the embodiment of the present invention can be realized by hardware. However, the computer uses a program for causing the computer to function as the electronic apparatus having the biological information measuring instrument. It can also be realized by reading and executing from a readable recording medium.

  In addition, the biological information measuring method according to the embodiment of the present invention can be realized by hardware, but the computer reads a program for causing the computer to execute the method from a computer-readable recording medium and executes the program. Can also be realized.

  Moreover, although the above-described embodiment is a preferred embodiment of the present invention, the scope of the present invention is not limited only to the above-described embodiment, and various modifications are made without departing from the gist of the present invention. Implementation in the form is possible.

DESCRIPTION OF SYMBOLS 10 Sensor 11 Oscillation part 12 Charge amount addition part 13 Average charge amount calculation part 14 Water content calculation part 20 AC voltage signal 21 DC voltage signal 30a, 30b Electrode terminal 31 Sensor substrate 32 Electrode 33 Cross comb electrode 110 Electronic equipment 111 Case 112 Storage device 113 Main board 114 Electronic circuit 121 Finger 122 Contact surface 123 Skin that has fallen

Claims (13)

In a biological information measuring instrument for measuring the moisture content of the skin,
A sensor having an electrode formed on a substrate and measuring the amount of electric charge of the skin in contact with the electrode;
Oscillating means for applying an AC signal to the sensor;
The amount of electric charge based on the DC voltage signal obtained by rectifying the AC voltage signal output in proportion to the amount of electric charge measured from when the sensor comes into contact with the electrode until the skin leaves the electrode sequentially, at regular intervals. Save a charge amount adding means for calculating the total amount of by Ri electric load amount by adding the amount of charge the storage,
An average charge amount calculating means for calculating an average charge amount per unit time by dividing the total amount of the charge amount calculated by the charge amount adding means by a measurement time;
Based on the average charge amount calculated by the average charge amount calculation means, a moisture amount calculation means for calculating the moisture amount of the skin;
A biological information measuring instrument comprising:   2. The biological information measuring instrument according to claim 1, wherein the electrodes of the sensor are a pair of opposing electrodes formed on a substrate.   2. The biological information measuring instrument according to claim 1, wherein the electrodes of the sensor are a pair of opposing electrodes formed on a substrate and curved.   2. The biological information measuring instrument according to claim 1, wherein the electrode of the sensor is a plurality of opposing cross comb electrodes formed on a substrate.   2. The biological information measuring instrument according to claim 1, wherein the electrodes of the sensor are a plurality of curved crossing comb electrodes facing each other, which are formed on a substrate.   6. The biological information measuring instrument according to claim 4 or 5, wherein the plurality of opposed comb electrodes facing each other have different inter-electrode distances.   The biological information measuring instrument according to claim 6, wherein the plurality of mutually facing cross comb electrodes of the sensor form cross comb electrodes whose distance between the electrodes is increased by 25% in the facing electrode direction. A biometric information measuring instrument.   The biological information measuring instrument according to claim 1, wherein the sensor has a concave shape in a thickness direction of the sensor substrate at a position where opposing electrodes are formed. Measuring instrument. In the biological information measuring device according to claim 8, wherein the sensor, the biological information measuring device, characterized in that it has a concave shape along a part position shape of the skin to be subjected to the measurement. The living body information measuring instrument according to any one of claims 1 to 9, wherein the sensor forms a water repellent film on a surface of the electrode. Information measuring instrument. In the electronic device carrying the living body information measuring instrument according to any one of claims 1 to 10,
E Bei means you accumulate the amount of water the biological information measuring device is calculated,
Electronic apparatus, characterized by presenting information about the time-aging of the water content on the basis of the quantity of water before Ki蓄 product. In the biological information measurement method for measuring the moisture content of the skin,
Providing a sensor having an electrode formed on a substrate and measuring a charge amount of skin in contact with the electrode;
An oscillation step of applying an AC signal to the sensor;
The amount of electric charge based on the DC voltage signal obtained by rectifying the AC voltage signal output in proportion to the amount of electric charge measured from when the sensor comes into contact with the electrode until the skin leaves the electrode sequentially, at regular intervals. Save a charge amount adding step of calculating the total amount of by Ri electric load amount by adding the amount of charge the storage,
An average charge amount calculation step of calculating an average charge amount per unit time by dividing the total amount of the charge amount calculated in the charge amount addition step by a measurement time;
A moisture content calculating step for calculating the moisture content of the skin based on the average charge amount calculated in the average charge amount calculating step;
A biological information measuring method comprising: In the biological information measurement program for measuring the moisture content of the skin,
A sensor having an electrode formed on a substrate and measuring the amount of electric charge of the skin in contact with the electrode;
Oscillating means for applying an AC signal to the sensor;
The amount of electric charge based on the DC voltage signal obtained by rectifying the AC voltage signal output in proportion to the amount of electric charge measured from when the sensor comes into contact with the electrode until the skin leaves the electrode sequentially, at regular intervals. Save a charge amount adding means for calculating the total amount of by Ri electric load amount by adding the amount of charge the storage,
An average charge amount calculating means for calculating an average charge amount per unit time by dividing the total amount of the charge amount calculated by the charge amount adding means by a measurement time;
Based on the average charge amount calculated by the average charge amount calculation means, a moisture amount calculation means for calculating the moisture amount of the skin;
A biological information measuring program that causes a computer to function as a biological information measuring instrument.

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