TW202214179A - Blood measuring device - Google Patents

Abstract

The present invention provides a blood measuring device that allows various light rays which are used for calculating amounts of components in blood to pass along the same optical axis to accurately estimate the amounts of components in blood. A blood measuring device 10 of the present invention includes: a light emitting portion 11, a light receiving portion 19, an actuator 16, and an arithmetic control portion 17, and the light emitting portion 11 includes a first light emitting portion 111 and a second light emitting portion 112, and the calculation control portion 17 estimates an amount of glucose and controls an operation of the actuator 16. In addition, when the first light emitting portion 111 is to irradiate a first light to a measurement site, the arithmetic control portion 17 uses the actuator 16 to move a light emitting point of the first light emitting portion 111 to an optical axis 22 which is predetermined for passing through the measurement site. Furthermore, when the second light emitting portion 112 is to irradiate a second light to the measurement site, the arithmetic control portion 17 uses the actuator 16 to move a light emitting point of the second light emitting portion 112 to the optical axis 22.

Description

blood measuring device

The present invention relates to a blood measurement device that optically measures the amount of components contained in blood inside a part to be measured, such as a human body.

There are invasive methods and non-invasive methods for detecting the sugar content in the measurement site. The so-called invasive method is a method in which blood is collected from, for example, a fingertip of a human body, and the amount of glucose is measured using the blood. The so-called non-invasive method is a method of measuring the amount of glucose using a sensor placed outside the human body without taking blood from the human body. In general, an invasive method is used to calculate the correct amount of glucose. However, in order to reduce the pain of the user and improve the convenience, a non-invasive method is desired to be used.

An example of a known device for measuring the amount of glucose by a non-invasive method is a device that performs optical measurement by irradiating a human body with near-infrared rays or the like.

An optical measuring device for the amount of glucose, which detects the difference in the amount of near-infrared rays due to absorption of glucose. Specifically, this device transmits near-infrared rays through a certain portion, and measures the amount of glucose from the amount of transmitted light (for example, Patent Document 1 and Patent Document 2).

(prior art literature)

(patent literature)

Patent Document 1: Japanese Patent No. 3093871

Patent Document 2: Japanese Patent No. 3692751

However, the non-invasive method for measuring the amount of glucose disclosed in each of the above-mentioned patent documents has the problem that it is difficult to say that the amount of glucose can be accurately measured.

Specifically, since the measurement technique disclosed in Patent Document 1 calculates the amount of glucose by the glucose oxidase method, there is a problem that the calculation of the amount of glucose is complicated. In addition, the measurement technique disclosed in Patent Document 2 uses optical means to measure the amount of glucose, but only to the extent that the possibility of diabetes can be determined, and it is not enough to measure the amount of glucose quantitatively.

The present invention has been made in view of the above-mentioned problems. An object of the present invention is to provide a blood measuring device that can accurately estimate the amount of components contained in blood by allowing each light beam used to calculate the amount of components contained in blood to pass along the same optical axis.

The blood measuring apparatus of the present invention includes: a light emitting part having a first light emitting part irradiating a first light ray of a first wavelength and a second light emitting part irradiating a second light ray of a second wavelength; A light-receiving part for irradiating the light and the second light; an actuator for moving the light-emitting part; The calculation control part for the operation of the actuator, the calculation control part is to irradiate the first light beam to the measured object in the first light emitting part When measuring the part, the light-emitting point of the first light-emitting part is moved to an axis defined to pass through the optical axis of the part to be measured by the actuator, and the second light-emitting part is irradiated with the second light to the At the measurement site, the light-emitting point of the second light-emitting portion is moved to the axis of the optical axis by the actuator.

In the blood measurement device of the present invention, the measurement site is a mesothelial membrane (finger web, also called a finger web, that is, a membrane-like site formed between fingers), and a sandwich is formed on the outside of the light-emitting portion and the light-receiving portion. The clipping portion of the aforementioned finger mesothelial membrane.

In the blood measurement device of the present invention, the actuator moves the light-emitting portion or the light-receiving portion along the optical axis, so that the light-emitting portion or the light-receiving portion approaches the finger mesothelial membrane.

The blood measurement apparatus of the present invention includes a first pressing portion and a second pressing portion for pressing a region near the interdigital film when the interdigital film is inserted into the holding portion.

In the blood measurement device of the present invention, abutting portions on which the fingers on both sides of the interdigital mesothelial membrane are abutted are formed on the outer side of the holding portion.

In the blood measuring apparatus of the present invention, the light-emitting portion further includes a third light-emitting portion for irradiating a third light with a third wavelength, and the calculation control portion is to emit the third light from the third light-emitting portion to the part to be measured. At the same time, the light-emitting point of the third light-emitting portion is moved to the axis of the optical axis by the actuator, and the components contained in the blood are estimated based on the received light intensity of the first light ray, the second light ray and the third light ray quantity.

The blood measurement device of the present invention includes a main body, a first waveguide and a second waveguide protruding from the main body, and built in the first waveguide and the second waveguide, respectively. In the first mirror and the second mirror in the two waveguides, the optical axis is defined to pass through the first waveguide, the first mirror, the second waveguide and the second mirror.

In the blood measuring apparatus of the present invention, the amount of the component contained in the blood is the amount of glucose.

The blood measuring apparatus of the present invention includes: a light emitting part having a first light emitting part irradiating a first light ray of a first wavelength and a second light emitting part irradiating a second light ray of a second wavelength; A light-receiving part for irradiating the light and the second light; an actuator for moving the light-emitting part; When the first light emitting part is about to irradiate the first light beam to the measured part, the calculation control part uses the actuator to move the light emitting point of the first light emitting part to the measured part. When the second light emitting part is to irradiate the second light beam to the measured part on the axis passing through the optical axis of the measured part, the light emitting point of the second light emitting part is moved by the above-mentioned actuator to the position to be measured. on the axis of the aforementioned optical axis. Therefore, according to the blood measurement apparatus of the present invention, the first light beam and the second light beam are irradiated along the optical axis defined to penetrate the measurement site, so that the optical paths and optical path lengths of the respective light beams are unified. Therefore, since the optical conditions of the first light beam and the second light beam are made uniform, the amount of the component contained in the blood can be accurately measured based on the received light intensity of the first light beam and the second light beam.

Furthermore, in the blood measurement device of the present invention, the measurement site is a mesothelial membrane, and a holding portion for sandwiching the finger mesothelial membrane is formed on the outside of the light-emitting portion and the light-receiving portion. Therefore, according to the blood measuring device of the present invention, the user can hold the finger mesothelial membrane with the holding portion, On the other hand, if the finger mesothelial membrane is reliably arranged between the light-emitting part and the light-receiving part, the amount of the components contained in the blood can be measured more accurately. In addition, the mesothelial membrane of the finger is very suitable as the measurement site because of its short transmission distance.

Furthermore, in the blood measuring apparatus of the present invention, the actuator moves the light-emitting portion or the light-receiving portion along the optical axis, so that the light-emitting portion or the light-receiving portion is brought close to the finger mesothelial membrane. Therefore, according to the blood measuring apparatus of the present invention, the amount of the component contained in the blood can be calculated more accurately by bringing the light-emitting portion or the light-receiving portion close to the finger mesothelial membrane by using the actuator.

Furthermore, the blood measurement device of the present invention includes a first pressing portion and a second pressing portion for pressing a region near the interdigital membrane when the interdigital membrane is inserted into the holding portion. Therefore, according to the blood measurement device of the present invention, the first pressing part and the second pressing part can press the muscles in the vicinity of the interdigital membrane, so that the positions of the interdigital membrane, the light-emitting part and the light-receiving part when irradiated with each light can be adjusted. relationship is more appropriate.

In addition, in the blood measuring apparatus of the present invention, abutting portions on which the fingers on both sides of the interdigital mesothelial membrane are abutted are formed on the outer side of the holding portion. Therefore, according to the blood measuring apparatus of the present invention, the finger mesothelial membrane can be expanded, and the thickness of the finger mesothelial membrane during measurement can be kept constant.

In addition, in the blood measuring device of the present invention, the light-emitting portion further includes a third light-emitting portion for irradiating a third light beam with a third wavelength, and the calculation control portion irradiates the third light-emitting portion on the third light-emitting portion to the target. When measuring the part, the light-emitting point of the third light-emitting part is moved to the axis of the optical axis by the actuator, and the blood is estimated based on the received light intensity of the first light ray, the second light ray and the third light ray content of ingredients. Therefore, according to the blood measuring apparatus of the present invention, the amount of the component contained in the blood is calculated using the received light intensity of the third light beam in addition to the first light beam and the second light beam, and the amount of the component contained in the blood can be calculated more accurately.

Furthermore, the blood measuring apparatus of the present invention includes a main body, a first waveguide and a second waveguide protruding from the main body, and a first reflection mirror and a second waveguide built in the first waveguide and the second waveguide, respectively. Two reflecting mirrors, and the optical axis system is defined so as to pass through the first waveguide, the first reflecting mirror, the second waveguide, and the second reflecting mirror. Therefore, according to the blood measuring apparatus of the present invention, the amount of components contained in the blood can be measured without compressing the blood flow of the site to be measured.

Further, in the blood measuring device of the present invention, the amount of the component contained in the blood is the amount of glucose. Therefore, according to the blood measuring apparatus of the present invention, the amount of glucose contained in the blood can be accurately estimated.

10: Blood measuring device

11: Light-emitting part

12: Operation input part

13: Memory Department

14: Lens

15: Display part

16: Actuator

17: Calculation Control Department

18: Measured part

19: Receiver

20: Upper side panel

21: Temperature measurement section

22: Optical axis

24: Thumb Adductors

25: The first pressing part

26: Thumb Ball

27: The second pressing part

28, 29: Abutment

30: Actuator storage part

31: Light-emitting part storage part

32: Light-receiving part storage part

33: Inclined surface

34: Shell

35: Cover

36: Bracket

37: Motor

38: Rotary axis

39: Screw part

40, 41, 42: Opening

43: Protrusions

44: Hole

45: Ontology

46, 47: Reflector

48, 49: Waveguide

50,51: Opening

111: The first light-emitting part

112: Second light-emitting part

113: The third light-emitting part

231, 232: Clamping part

FIG. 1 is a diagram showing a blood measuring apparatus according to an embodiment of the present invention, and FIGS. 1(A) and 1(B) are perspective views showing the blood measuring apparatus.

FIG. 2 is a conceptual diagram showing the connection structure of the blood measuring apparatus according to the embodiment of the present invention.

FIG. 3 is a perspective view showing the actuator of the blood measuring apparatus according to the embodiment of the present invention.

FIG. 4 is an exploded perspective view showing the actuator of the blood measuring apparatus according to the embodiment of the present invention.

5 is a diagram showing a method of measuring the amount of glucose using the blood measurement device according to the embodiment of the present invention, and FIGS. 5(A) and 5(B) are plan views showing the method of applying the blood measurement device to the finger mesothelial membrane in sequence.

FIG. 6 is a cross-sectional view showing a method of detecting the amount of glucose using the blood measuring device according to the embodiment of the present invention, and showing a state in which the blood measuring device is applied to the finger mesothelial membrane.

FIG. 7 is a diagram showing a method for calculating the amount of glucose according to the embodiment of the present invention, and FIGS. 7(A), 7(B), 7(C) and 7(D) show that while moving the light-emitting point, and A side view of the state in which the measurement is performed while the light-emitting part and the light-receiving part are brought close to each other.

FIG. 8 is a diagram showing a method for calculating the amount of glucose according to an embodiment of the present invention, FIG. 8(A) is a schematic diagram of a finger mesothelial membrane, and FIG. 8(B) is a graph showing the results obtained by measuring the amount of glucose at the fingertip , Figure 8(C) is a graph showing the results obtained by measuring the amount of glucose in the mesothelial membrane of the finger.

9 is a cross-sectional view showing a method for detecting the amount of glucose using the blood measuring device according to another embodiment of the present invention, and showing the state where the blood measuring device is applied to the finger mesothelial membrane.

Hereinafter, the blood measuring apparatus 10 according to the embodiment of the present invention will be described in detail with reference to the drawings. In the following description, the same components are denoted by the same reference numerals in principle, and repeated descriptions will not be given. In the present embodiment, the amount of glucose is used as an example of the amount of components contained in the blood measured by the blood measuring device 10 .

Referring to FIG. 1 , the appearance and the like of the blood measuring apparatus 10 of the present embodiment will be described. FIG. 1(A) is a perspective view of the blood measurement device 10 viewed from the upper front, and FIG. 1(B) is a perspective view of the blood measurement device 10 viewed from the lower front.

Referring to FIGS. 1(A) and 1(B) , the outer portion of the blood measurement apparatus 10 is formed of synthetic resin or the like. Furthermore, the blood measurement apparatus 10 has a substantially cubic shape having a longitudinal direction along the front-rear direction as a whole. When the blood measurement apparatus 10 is viewed from above, the center portion of the front end protrudes forward. In addition, the size and weight of the blood measuring device 10 are determined so that the blood The fluid measuring device 10 measures the extent to which a user of the amount of glucose can be grasped with one hand. Here, the amount of glucose refers to the amount of glucose in the blood or in the interstitium. In addition, the amount of glucose is also referred to as a blood sugar level or the like.

An actuator housing portion 30 is formed in the lower portion of the blood measurement apparatus 10 . The actuator accommodating portion 30 accommodates a mechanism for displacing the light-emitting portion 11 to be described later, and the configuration thereof will be described later. The vicinity of the front center portion of the actuator housing portion 30 protrudes forward to form the second pressing portion 27 . When the blood measurement device 10 is used to measure the amount of glucose, the second pressing part 27 presses a specific part of the human body, which will be described in detail later with reference to FIG. 6 .

An upper plate portion 20 is formed on the upper end portion of the blood measurement device 10 . The vicinity of the front center part of the upper side plate part 20 protrudes forward, and is formed as a first pressing part 25 . When the blood measurement device 10 is used to measure the amount of glucose, the first pressing part 25 presses a specific part of the human body, which will be described in detail later with reference to FIG. 6 .

Referring to FIG. 1(A) , a contact portion 28 is formed on the upper portion of the right side surface of the blood measurement device 10 . The abutting portion 28 may be a flat surface, or may be a curved surface concave inwardly on which the user's fingers can easily fit. The abutting portion 28 is a portion on which, for example, a user's thumb is abutted when the blood measuring device 10 is to be used to calculate the amount of glucose.

A notch is formed in part of the front end portion of the contact portion 28 as a holding portion 232 . The width in the up-down direction of the holding portion 232 is such that the interdigital mesothelial membrane described later can be inserted. The rear end of the holding portion 232 is disposed behind the opening portion 41 through which the light for measurement passes. Therefore, when the peripheral edge of the finger mesothelial membrane, which is the part to be measured, comes into contact with the rear end of the holding portion 232, the finger mesothelial membrane can be surely positioned in the opening portion 41, and the light passing through the opening portion 41 can be surely transmitted through the finger mesothelial membrane. .

Referring to FIG. 1(B) , an abutting portion 29 is formed on the upper left side surface of the blood measurement device 10 . The abutting portion 29 may be a flat surface, or may be a curved surface concave inwardly on which the user's fingers can easily fit. The abutting portion 29 is a portion on which, for example, a user's index finger abuts when the blood measuring device 10 is to be used to calculate the amount of glucose.

A portion of the front end of the contact portion 29 is formed with a notch as a holding portion 231 . The specific shape of the holding portion 231 is the same as that of the holding portion 232 described above.

Referring to FIG. 1(A) , a light-emitting portion accommodating portion 31 is formed in the vicinity of the front end of the upper surface of the actuator accommodating portion 30 . In addition, the light-emitting portion housing portion 31 is disposed between the holding portion 231 and the holding portion 232 in the left-right direction. The light-emitting portion housing portion 31 is a portion where the light-emitting portion 11 to be described later is disposed. In addition, an inclined surface 33 is formed on the front portion of the light-emitting portion housing portion 31, and the inclined surface 33 is inclined forward and downward. By forming the inclined surface 33 , when the amount of glucose is to be measured, the finger mesothelial membrane can be guided to the holding portion 231 and the holding portion 232 along the inclined surface 33 . In addition, the top surface of the light-emitting portion housing portion 31 is opened to form the opening portion 41 .

Referring to FIG. 1(B) , from the front of the lower surface of the upper plate portion 20, a light-receiving portion accommodating portion 32 protruding downward is formed. The light-receiving portion accommodating portion 32 is a portion that houses the light-receiving portion 19 to be described later. In addition, on the bottom surface of the light-receiving portion housing portion 32, an opening portion 42 through which light for measuring the amount of glucose passes is formed.

FIG. 2 is a conceptual diagram showing the basic configuration of the blood measuring apparatus 10 . Referring to FIG. 2 , the blood measurement apparatus 10 is provided with: a light emitting unit 11 that emits light for measurement, a lens 14 belonging to an optical element that guides the light emitted from the light emitting unit 11 to the portion to be measured 18 , The light receiving unit 19 that receives the light transmitted through the measurement site 18, the calculation control unit 17 that calculates the amount of glucose based on the output of the light receiving unit 19, the memory unit 13, the display unit 15, the operation input The inlet part 12 and the temperature measuring part 21 . Here, a pinhole can also be used instead of the lens 14 to condense the light.

The function of the blood measurement device 10 is to measure the amount of glucose in the human body by a non-invasive method by transmitting light through the measured part of the human body.

The light emitting unit 11 emits light of a predetermined wavelength for measuring the amount of glucose. The light-emitting portion 11 includes a first light-emitting portion 111 , a second light-emitting portion 112 and a third light-emitting portion 113 each of which emits light of different wavelengths. The first light emitting part 111 , the second light emitting part 112 and the third light emitting part 113 are all composed of light emitting diodes. For example, the wavelength of the first light emitted by the first light emitting portion 111 is 1310 nm, the wavelength of the second light emitted by the second light emitting portion 112 is 1450 nm, and the wavelength of the third light emitted by the third light emitting portion 113 is 1550 nm.

The first ray is light that is not absorbed by the components in the organism, and the second and third rays are light that is absorbed by the glucose, protein, and water in the organism. The optical path length of the optical axis 22 is measured by the first light ray to measure the influence of the optical path length on the absorption rate of each light ray, the influence of the optical path length can be excluded, and the amount of glucose can be accurately calculated.

The actuator 16 moves the light emitting unit 11 to the left and right. By moving the light-emitting portion 11 , the light-emitting point of any one of the first light-emitting portion 111 , the second light-emitting portion 112 , and the third light-emitting portion 113 can be arranged on the same axis of the optical axis 22 . Here, the case where the light-emitting point of the second light-emitting portion 112 is arranged on the axis of the optical axis 22 is shown.

In addition, the actuator 16 moves either one or both of the light-emitting unit 11 and the light-receiving unit 19 in the vertical direction. For example, the actuator 16 causes the light-receiving part 19 to move away from the light-emitting part 11 when the blood measuring device 10 is not measuring the amount of glucose. On the other hand, the actuator 16 causes the light-receiving part 19 and the light-emitting part 11 to communicate with each other when the blood measuring device 10 is to measure the amount of glucose. near. An example of a specific configuration of the actuator 16 will be described later with reference to FIGS. 3 and 4 .

In this embodiment, the first light ray, the second light ray and the third light ray are irradiated from the light-emitting portion 11 to the light-receiving portion 19 along the same optical axis 22 . That is, the propagation paths and propagation lengths of the first light ray, the second light ray and the third light ray inside the measured portion 18 are the same.

By making the optical axis 22 common to each light beam as described above, the amount of glucose can be accurately measured. Specifically, the amount of glucose is calculated by the following formula 1 based on the Lambert-Beer law.

Formula 1: C=-log ₁₀ (I/I ₀ )/(0.434×μ _a ×r)

In the above formula 1, C is the amount of glucose, I is the intensity of transmitted light, I ₀ is the intensity of incident light, μ _a is the absorption coefficient of the skin, and r is the optical path length.

In this embodiment, the first light, the second light, and the third light share the optical axis 22, so that the optical path length r is the same, the number of unknowns to be calculated can be reduced, and the amount of glucose can be calculated accurately and easily. C.

The lens 14 utilizes its refraction and diffraction effects to guide the first, second and third light rays emitted from the first light-emitting portion 111 , the second light-emitting portion 112 and the third light-emitting portion 113 to the lens 14 . Measured part 18 .

The measurement site 18 is a site where the amount of glucose is measured by the blood measuring apparatus 10 of the present embodiment. Specifically, fingertips, earlobes, interdigital membranes, etc. can be used as the measurement site 18 . As will be described later, a finger mesothelial membrane that contains little fat, has little individual variation in thickness, and is not formed with thick blood vessels is suitable as the measurement site 18 .

The light-receiving portion 19 is a semiconductor element composed of, for example, a photodiode, and is formed to receive the irradiation of the first light, the second light and the third light transmitted through the measured portion 18, The light-receiving part of its intensity is detected. The light receiving unit 19 transmits signals corresponding to the received light intensities of the first light beam, the second light beam and the third light beam to the calculation control unit 17 .

The memory unit 13 is a semiconductor memory device or the like composed of RAM or ROM, and stores a formula for calculating the amount of glucose from the output value of the light-receiving unit 19, parameters, estimation results, and a program for executing the method for calculating the amount of glucose.

The operation input unit 12 is a portion where the user instructs the calculation control unit 17 , and is composed of switches, a touch panel, and the like.

The temperature measuring unit 21 is a part that contacts the user's body to measure the user's body temperature.

The calculation control unit 17 is constituted by a CPU, and performs various calculations and controls the operation of each part constituting the blood measurement apparatus 10 . Specifically, the calculation control unit 17 causes the first light emitting unit 111 , the second light emitting unit 112 and the third light emitting unit 113 of the light emitting unit 11 to emit the first light, the second light and the third light. In addition, the calculation control unit 17 estimates the amount of glucose using a conversion formula based on electrical signals input from the light receiving unit 19 and the temperature measuring unit 21 and the like. In addition, the calculation control unit 17 can display the calculated amount of glucose on the display unit 15 . Displaying the amount of glucose on the display unit 15 such as a liquid crystal display allows the user who uses the blood measuring apparatus 10 to know the change in the amount of his own glucose in real time. In addition, at the time of measurement, the arithmetic control unit 17 operates the actuator 16 to move the light-emitting unit 11 and the light-receiving unit 19 so that the light-emitting point of each light-emitting unit is arranged on the axis of the optical axis 22 .

The actuator 16 will be described in detail with reference to FIGS. 3 and 4 . FIG. 3 is a perspective view showing the actuator 16 , and FIG. 4 is an exploded perspective view showing the actuator 16 exploded in the up-down direction.

3 , the actuator 16 mainly includes a housing 34 , a cover 35 , a bracket 36 , a motor 37 , a rotating shaft 38 and a screwing portion 39 . The actuator 16 moves the light-emitting portion 11 in the left-right direction according to the instruction of the above-mentioned calculation control portion 17, thereby arranging the light-emitting points of the first light-emitting portion 111, the second light-emitting portion 112, or the third light-emitting portion 113 in the light-emitting portion. on the axis of the optical axis 22 . In addition, the light receiving point of the light receiving unit 19 is also arranged on the axis of the optical axis 22 .

The specific operation of the actuator 16 is that the motor 37 rotates the rotation shaft 38 according to the instruction of the calculation control unit 17, and the screw part 39 screwed or engaged with the rotation shaft 38 moves in the left-right direction. The screwing part 39 moves in the left-right direction, and the holder 36 on which the light-emitting part 11 is mounted also moves in the left-right direction. In this way, the light-emitting points of the first light-emitting portion 111 , the second light-emitting portion 112 or the third light-emitting portion 113 can be arranged on the axis of the optical axis 22 .

With reference to FIG. 4, each part which comprises the actuator 16 is demonstrated. The casing 34 is a substantially box-shaped portion with an upper opening. The housing 34 accommodates a motor 37 , a rotating shaft 38 and a screwing portion 39 .

Inside the casing 34 , a part of the rotating shaft 38 led out from the motor 37 is arranged in the screwing portion 39 . Threads are formed on the side surface of the rotating shaft 38 . The screwing portion 39 moves in the left-right direction along with the rotation of the rotating shaft 38 by being screwed or engaged with the thread of the rotating shaft 38 . A hole portion 44 is formed on the upper surface of the screwing portion 39 . The hole portion 44 is arranged below the opening portion 40 to be described later.

The cover portion 35 is a plate-shaped member that covers the upper opening of the case 34 . The lid portion 35 is formed with an elongated opening portion 40 along the left-right direction.

The holder 36 has a substantially cubic shape, and the light-emitting portion 11 is disposed on the upper surface thereof. Further, the bracket 36 is formed with a substantially rod-shaped protrusion 43 that protrudes downward. The protruding portion 43 is inserted into the hole portion 44 through the opening portion 40 .

The actuator 16 is configured as described above, and when the motor 37 rotates the rotating shaft 38 in one direction according to the instruction of the calculation control unit 17 , the screwing part 39 moves to the right in accordance with the rotation, and the bracket 36 and the light-emitting part 11 move in the right direction. Also move to the right. Conversely, when the motor 37 rotates the rotating shaft 38 in the opposite direction according to the instruction of the arithmetic control unit 17, the screwing part 39 moves to the left according to the rotation, and the bracket 36 and the light-emitting part 11 also move to the left. . By doing so, the light-emitting point of any one of the first light-emitting portion 111 , the second light-emitting portion 112 , and the third light-emitting portion 113 can be arranged on the same axis of the optical axis 22 . On the other hand, the position of the light-receiving portion 19 in the front-rear left-right direction is always fixed in the front-rear left-right direction, and is arranged on the axis of the optical axis 22 .

Next, a specific method of measuring a user's glucose level using the blood measuring device 10 having the above-described configuration will be described with reference to FIGS. 5 to 7 , and also with reference to FIGS. 1 to 4 .

Referring to FIG. 5 , first, the blood measurement apparatus 10 is set at the measurement site of the user. FIGS. 5(A) and 5(B) are diagrams showing the state in which the blood measurement apparatus 10 is sequentially set to the finger mesothelial membrane as the measurement site. Here, the interdigital mesothelial membrane formed between the thumb and the index finger of the left hand is used as a site for measuring the amount of glucose. Therefore, the user can easily operate the blood measurement device 10 with his right hand.

Referring to FIG. 5(A) , the blood measurement device 10 is loaded from the index finger side portion of the finger mesothelial membrane. Specifically, the gripping portion 232 and the gripping portion 231 of the blood measurement device 10 are slid from the index finger side portion of the interdigital mesothelial membrane. At this time, the user spreads the thumb and the index finger to spread the interdigital epithelium.

Referring to FIG. 5(B) , next, the blood measurement device 10 is moved to the thumb side while pressing the blood measurement device 10 to the left in a state in which the interdigital membrane is sandwiched between the clamping portion 231 and the clamping portion 232 . Here, the blood measurement device 10 is slid until the front end of the blood measurement device 10 reaches the base of the thumb or its vicinity.

Here, the end of the finger mesothelial membrane is in contact with the rear ends of the clamping portion 231 and the clamping portion 232 . In this way, the light-emitting portion 11 and the light-receiving portion 19 can be arranged at the portion overlapping the mesothelial membrane of the finger. In this state, each light emitted from the light-emitting portion 11 is transmitted through the interdigital membrane to reach the light-receiving portion 19 .

Here, the base of the thumb or its vicinity can be brought into contact with the contact portion 28 of the blood measurement device 10 . Furthermore, the base of the index finger or its vicinity may be brought into contact with the contact portion 29 of the blood measurement device 10 . In this way, the thumb and the index finger can be stretched to a certain angle or more, which can prevent the deflection of the interdigital epithelium. Furthermore, when measuring the amount of glucose, the angle between the thumb and the index finger can be made uniform, and the thickness of the interdigital membrane can be kept constant.

Fig. 6 is a cross-sectional view taken along the line A-A of Fig. 5(B). Referring to FIG. 6 , the first pressing portion 25 of the blood measurement device 10 presses the adductor 24 of the hand or its vicinity toward the front. Furthermore, the second pressing portion 27 of the blood measurement device 10 presses the thumb ball 26 or its vicinity forward. In this way, the relative positions of the light-emitting portion 11 and the light-receiving portion 19 and the finger mesothelial membrane can be brought into a predetermined positional relationship, and the amount of glucose can be more accurately calculated using the light transmitted through the finger mesothelial membrane.

7 , an example in which the light-emitting portion 11 is displaced to emit each light beam will be described. FIG. 7(A) shows the light-emitting portion 11 before the light is irradiated, FIG. 7(B) shows the state where the second light is irradiated from the second light-emitting portion 112 , and FIG. 7(C) shows the state where the first light is irradiated from the first light-emitting portion 111 In the state, FIG. 7(D) shows the state in which the third light beam is irradiated from the third light emitting unit 113 . Here, although the second light-emitting portion 112, The order of the first light-emitting portion 111 and the third light-emitting portion 113 is to emit light along the optical axis 22, but the order can be changed.

Referring to FIG. 7(A) , the light-emitting portion 11 and the light-receiving portion 19 are arranged so as to sandwich the interdigital epithelium, which is an example of the site to be measured 18, in the up-down direction. The actuator 16 moves one or both of the light-emitting portion 11 and the light-receiving portion 19 in the up-down direction to shorten the distance between the light-emitting portion 11 and the light-receiving portion 19 in the up-down direction.

Here, the actuator 16 moves the light receiving unit 19 downward in accordance with the instruction of the above-mentioned calculation control unit 17 . For example, referring to FIG. 7(A) , by moving the light-receiving portion housing portion 32 downward, the light-receiving portion 19 provided in the light-receiving portion housing portion 32 can be lowered. Here, the finger mesothelial film may be sandwiched between the light-emitting portion housing portion 31 and the light-receiving portion housing portion 32 to have a constant thickness, or the finger mesothelial film may not be sandwiched.

7(B), when the second light-emitting portion 112 is about to emit the second light, first, the calculation control portion 17 moves the light-emitting portion 11 through the actuator 16 to make the light-emitting point of the second light-emitting portion 112 and the optical axis 22 overlapping. After the light-emitting point of the second light-emitting portion 112 overlaps with the optical axis 22, the calculation control portion 17 causes the second light-emitting portion 112 to emit a second light beam. The emitted second light ray travels along the optical axis 22 , passes through the measured portion 18 , and then irradiates the light receiving portion 19 . The light receiving unit 19 transmits an electrical signal representing the intensity of the received second light beam to the calculation control unit 17 .

7(C) , next, the calculation control unit 17 moves the light-emitting unit 11 to the right through the actuator 16 so that the light-emitting point of the first light-emitting unit 111 overlaps the optical axis 22 . After the light-emitting point of the first light-emitting portion 111 overlaps with the optical axis 22, the calculation control portion 17 causes the first light-emitting portion 111 to emit the first light beam. The emitted first light ray travels along the optical axis 22 and is transmitted through the part 18 to be measured. Then, the light-receiving part 19 is irradiated. The light receiving unit 19 transmits an electrical signal representing the intensity of the received first light beam to the calculation control unit 17 .

7(D) , next, the calculation control unit 17 moves the light-emitting unit 11 to the left through the actuator 16 so that the light-emitting point of the third light-emitting unit 113 overlaps the optical axis 22 . After the light-emitting point of the third light-emitting portion 113 overlaps with the optical axis 22, the calculation control portion 17 causes the third light-emitting portion 113 to emit a third light beam. The emitted third light ray travels along the optical axis 22 , passes through the measured portion 18 , and then irradiates the light receiving portion 19 . The light receiving unit 19 transmits an electrical signal representing the intensity of the received third light beam to the calculation control unit 17 .

In addition, according to the instruction of the calculation control unit 17 , the temperature measurement unit 21 measures the body temperature of the user, and transmits an electrical signal representing the body temperature to the calculation control unit 17 .

After measuring the received light intensity of the first light ray, the second light ray and the third light ray by the above-mentioned method, the user's glucose level is calculated from the light receiving intensity of each light ray, body temperature, and the like. As a calculation method, a statistical method can be used, for example. For example, a multiple regression curve is created by statistical analysis using the user's blood glucose level, received light intensity of each light, body temperature, and the like. Then, the estimated glucose amount is calculated from the received light intensity and body temperature of each light using the multiple regression curve.

8 , the reason why the finger mesothelial membrane is suitable as a measurement site to be irradiated with each light for estimating the amount of glucose will be described. Fig. 8(A) is a schematic diagram showing the user's hand, Fig. 8(B) is a graph showing the results of Error Grid analysis obtained by using fingertips to estimate the amount of glucose, and Curve of Error Grid analysis results obtained by estimating the amount of glucose. In FIGS. 8(B) and 8(C) , the horizontal axis represents the blood glucose level, and the vertical axis represents the estimated glucose level measured by the method of this embodiment.

Referring to FIG. 8(A) , the mesothelial membrane refers to a membrane-like portion formed between human fingers. Here, the interdigital epithelium formed between the other fingers may be used as the measurement site.

Referring to FIG. 8(B), the points representing the measurement results are distributed away from the reference line represented by the dotted line. The reason for this is conceivable that the thickness of the fingertip varies greatly among individuals, so the length of the light path varies, and the thick blood vessels present at the fingertip have adverse effects.

On the other hand, referring to FIG. 8(C), the points representing the measurement results are distributed in the vicinity of the reference line represented by the dotted line. The reason for this can be imagined as follows: the thickness of the mesothelial membrane is about 2mm to 4mm, the difference between individuals is small, the fat content is also very small, and there are no thick blood vessels inside, so it can be measured in capillaries and dermis. reason. Furthermore, when the mesothelial membrane of the finger is used as the measurement site, the length of the optical path can be shortened, and the amount of glucose can be measured with low-output light.

Referring to Table 1, the reason why the finger mesothelial membrane is suitable as the measurement site will be explained from the viewpoint of the fat content.

[Table 1]

Table 1 shows the measured first rays related to the sample 1 containing fat (epidermal 0.2mm, dermis 0.8mm, fat 1.5mm) and the sample 2 without fat (epidermal 0.2mm, dermis 0.8mm, no fat). , the transmittance of the second light and the third light. For example, the specimen 1 is the fingertip of a human body containing fat, and the specimen 2 is the finger mesothelial membrane.

1.5mm、受光面徑為

3mm或

1mm。 The simulation conditions here are: the number of light channels is 5000, the number of scattering is 1000 times per channel, and the incident light path of the skin is

1.5mm, the diameter of the light-receiving surface is

3mm or

1mm.

As shown in Table 1, under the first light with a wavelength of 1310 nm, the transmittance of the specimen 2 is 3.4 times that of the specimen 1; under the second light with a wavelength of 1450 nm, the transmittance of the specimen 2 is 3.4 times that of the specimen 6.2 times the transmittance of 1; in the third light with a wavelength of 1550 nm, the transmittance of specimen 2 is 3.5 times that of specimen 1.

From the above results, it can be seen that the specimen 1, such as a fingertip, is not suitable as a site for measuring the amount of glucose because the transmittance of the first light to the third light is low. In addition, considering that the amount of fat varies greatly among individuals, the amount of fat affects the transmittance, so it is difficult to estimate the amount of glucose from the portion with fat.

On the other hand, the sample 2 of the mesothelial membrane, for example, has a very small content of fat, so the first light, the second light and the third light can be transmitted well, and the intensity of the transmitted light can be determined according to the intensity of the transmitted light. Correctly calculate the amount of glucose. Moreover, even if the user is obese, the fat contained in the finger mesothelial membrane does not increase much. Therefore, the glucose amount can be estimated accurately by using each light transmitted through the finger mesothelial membrane, regardless of whether the user is obese or not.

The configuration of another type of blood measuring apparatus 10 will be described with reference to FIG. 9 . FIG. 9 is a cross-sectional view of another type of blood measuring device 10 . The blood measurement device 10 shown in this figure has The basic configuration is the same as that shown in FIG. 1 to FIG. 4 , so the description of the overlapping configuration and method is omitted, and only the different parts will be mainly described.

The blood measurement device 10 has a main body 45 , and each constituent member constituting the blood measurement device 10 is provided in the main body 45 . Here, the light-emitting portion 11 and the light-receiving portion 19 provided in the main body 45 are shown.

A waveguide 48 and a waveguide 49 protrude from the front end surface of the main body 45 , a reflection mirror 46 is provided in the waveguide 48 , and a reflection mirror 47 is provided in the waveguide 49 . In addition, the light receiving portion 19 is arranged behind the waveguide 48 , and the light emitting portion 11 is arranged behind the waveguide 49 . Further, the waveguide 48 below the mirror 46 is opened to form the opening 50 , and the waveguide 49 above the mirror 47 is opened to form the opening 51 . Furthermore, the mirror 46 and the mirror 47 are arranged at the front ends of the waveguide 48 and the waveguide 49 . In addition, the temperature measuring unit 21 is arranged between the waveguide 48 and the waveguide 49 .

Inside the main body 45, there is formed an optical axis 22 through which each light beam passes when measuring the amount of glucose. The optical axis 22 is defined so that the light-emitting portion 11 reaches the light-receiving portion 19 via the waveguide 49 , the reflection mirror 47 , the opening 51 , the opening 50 , the reflection mirror 46 , and the waveguide 48 .

When the amount of glucose is calculated using the blood measurement device 10 , the finger mesothelial membrane is first arranged between the waveguide 48 and the waveguide 49 . In this way, the mesothelial membrane of the finger is located between the opening 50 and the opening 51 . Then, the temperature measuring unit 21 is brought into contact with the interdigital membrane to measure the body temperature.

Next, the calculation control unit 17 causes the light emitting unit 11 to emit light rays, and the light rays are irradiated along the optical axis 22 . Each light emitted from the light-emitting portion 11 passes through the waveguide 49 and is reflected by the reflecting mirror 47 , then passes through the opening 51 , transmits through the interdigital epithelium, passes through the opening 50 , is reflected by the reflecting mirror 46 and passes through the waveguide 48 to reach the light-receiving portion 19 light spot. The arithmetic control unit 17 moves the light-emitting unit 11 in the vertical direction so that the first light-emitting unit 111, the second light-emitting unit 112, and the third light-emitting unit The first light, the second light and the third light emitted by the light-emitting point of the light-emitting portion 113 are all along the optical axis 22 . Here, the waveguide 48 is separated from the waveguide 49 to such an extent that it does not compress the finger mesothelial membrane or lightly contact the finger mesothelial membrane.

Next, the light receiving unit 19 transmits an electrical signal representing the received light intensity of each light beam to the calculation control unit 17 . The calculation control unit 17 calculates the amount of glucose using the received light intensity of each light beam, the temperature of the finger mesothelial membrane measured by the temperature measurement unit 21 , and the like using a conversion formula such as a multivariate regression formula.

In the blood measurement device 10 shown in FIG. 9, the waveguide 48 and the waveguide 49 do not press the interdigital membrane and its vicinity. Therefore, the amount of glucose can be accurately calculated in a state where the blood flow in the finger mesothelial membrane is good.

The embodiments of the present invention have been disclosed above, but the present invention is not limited to the above embodiments.

For example, the present embodiment described above uses the first light, the second light, and the third light with different wavelengths to calculate the amount of glucose, but two light rays (for example, the first light with a wavelength of 1310 nm, the second light with a wavelength of 1550 nm) can be used to calculate the amount of glucose. three rays) to calculate the amount of glucose.

In addition, the above-described blood measuring device 10 can also be used for the purpose of measuring amounts other than the amount of glucose. For example, there is a possibility that a diagnosis of a disease such as cancer can be performed from the intensity of each light beam transmitted through the human body and received by the light receiving unit 19 .

In addition, the above-described embodiment uses the interdigital membrane formed between the thumb and the index finger as the measurement site, but the interdigital membrane formed between other fingers and fingers may be used as the measurement site.

10: Blood measuring device

11: Light-emitting part

12: Operation input part

13: Memory Department

14: Lens

15: Display part

16: Actuator

17: Calculation Control Department

18: Measured part

19: Receiver

21: Temperature measurement section

22: Optical axis

111: The first light-emitting part

112: Second light-emitting part

113: The third light-emitting part

Claims (8)

A blood measuring device is provided with: The light-emitting part has: a first light-emitting part and a second light-emitting part, the first light-emitting part irradiates the first light of the first wavelength, and the second light-emitting part irradiates the second light of the second wavelength; The light-receiving part receives the irradiation of the first light and the second light passing through the measured part; an actuator for moving the light-emitting portion; and The calculation control part calculates the amount of components contained in the blood according to the received light intensity of the first light beam and the second light beam, and controls the action of the actuator; The aforementioned calculation control unit is composed of: When the first light-emitting portion is to irradiate the first light beam to the measurement site, the actuator is used to move the light-emitting point of the first light-emitting portion to an axis defined to pass through the measurement site's optical axis , When the second light-emitting portion is to irradiate the second light beam to the measurement site, the actuator is used to move the light-emitting point of the second light-emitting portion to the axis of the optical axis. The blood measurement device of claim 1, wherein, The aforementioned part to be measured refers to the mesothelial membrane, In addition, a holding portion for holding the finger mesothelial film is formed on the outside of the light-emitting portion and the light-receiving portion. The blood measuring device of claim 2, wherein, The actuator moves the light-emitting portion or the light-receiving portion along the optical axis, so that the light-emitting portion or the light-receiving portion is brought close to the interdigital epithelium. The blood measuring device according to claim 2 or 3, comprising: The first pressing portion and the second pressing portion press a portion near the interdigital film when the interdigital film is inserted into the holding portion. The blood measurement device according to any one of claims 2 to 4, wherein, An abutting portion on which the fingers on both sides of the interdigital epithelium abut on is formed on the outer side of the holding portion. The blood measurement device of any one of claims 1 to 5, wherein, The aforementioned light-emitting portion further includes a third light-emitting portion, and the third light-emitting portion irradiates a third light with a third wavelength; The aforementioned calculation control unit is composed of: When the third light-emitting part is going to irradiate the third light beam to the measured part, the actuator is used to move the light-emitting point of the third light-emitting part to the axis of the optical axis, The amount of the component contained in the blood is estimated according to the received light intensities of the first light ray, the second light ray and the third light ray. The blood measurement device according to any one of claims 1 to 6, comprising: ontology; a first waveguide and a second waveguide protruding from the body; and The first reflecting mirror and the second reflecting mirror are built in the first waveguide and the second waveguide respectively; The optical axis system is defined so as to pass through the first waveguide, the first reflection mirror, the second waveguide, and the second reflection mirror. The blood measurement device of any one of claims 1 to 7, wherein, The amount of the component contained in the aforementioned blood is the amount of glucose.

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