JPWO2020110222A1 - Concentration measuring device, concentration measuring method and non-temporary recording medium - Google Patents

Abstract

One aspect of the present invention is a first irradiation unit that irradiates light of a first wavelength, a second irradiation unit that irradiates light of a second wavelength, a light of a first wavelength, and a first intensity. A first acquisition unit that acquires a physical quantity caused by a change in the measurement target when the measurement target is irradiated with light of two wavelengths, and a second intensity that is different from the light of the first wavelength and the first intensity. The second acquisition unit that acquires the physical quantity caused by the change in the measurement target when the measurement target is irradiated with light of two wavelengths, and the temperature at which information on the temperature change of the measurement target is acquired based on the acquired physical quantity. It is a concentration measuring device including an information acquisition unit and a concentration acquisition unit that acquires the concentration of a non-target component contained in a measurement target based on information on a temperature change and the acquired physical quantity.

Description

The present invention relates to a concentration measuring device, a concentration measuring method, and a non-temporary recording medium.

In recent years, the number of diabetic patients has increased explosively, and it is predicted that the number of diabetic patients will reach 550 million worldwide by 2030 (see Non-Patent Document 1). Diabetes treatment is based on diet and exercise therapy based on blood glucose control, and it is necessary to measure the blood glucose level several times a day for blood glucose control. A general blood glucose meter requires blood sampling, but pain, hygiene, and medical waste are problems. Therefore, the establishment of a non-invasive and non-invasive blood glucose level measuring device is eagerly desired.

In response to such demands, methods for measuring blood glucose levels from information on light transmission, reflection, and scattering have been energetically studied (see Patent Documents 1 to 4 and Non-Patent Documents 2). However, these methods have a problem that it is difficult to accurately estimate the blood glucose level because the transmitted light intensity is insufficient for the measurement accuracy (about ± 10 milligrams per deciliter) required for blood glucose level control.

On the other hand, a blood glucose level measuring method using a photoacoustic effect in which light energy absorbed by a substance is converted into heat waves and elastic waves has been studied (see Patent Documents 5 to 6). These methods have a feature that the detection signal is larger than the method using transmitted light, and the measurement region can be specified in the depth direction by controlling the modulation frequency of the excitation light (see Non-Patent Document 3). ).

However, when the above-mentioned method is used, there is a problem that noise due to a signal derived from water, which is a non-target component, is mixed in the measurement result, and the reliability and accuracy of the measured blood glucose level is significantly lowered. This is because the spectral spectrum of glucose contained in the living body to be measured and the spectral spectrum of water overlap each other.

That is, when the glucose concentration is measured using only the energy obtained by light of a certain wavelength, there is a problem that it is not possible to distinguish whether the energy is derived from glucose or water. Further, even if the water content in the living body is slightly changed due to various factors, the glucose concentration may be erroneously measured.

As one method to solve this problem, a method of measuring the spectral spectrum detected from the target object at multiple wavelengths and estimating the concentration of the substance contained in the measurement target by using multivariate analysis or a neural network is known. (See Non-Patent Document 4).

Japanese Unexamined Patent Publication No. 10-325794 Japanese Unexamined Patent Publication No. 11-216131 Japanese Unexamined Patent Publication No. 2004-147706 Japanese Unexamined Patent Publication No. 2005-37253 Japanese Unexamined Patent Publication No. 2008-191160 JP-A-2009-165634

International Diabetes Federation, International Diabetes Federation, Diabetes atlas 5th edition, 2011 David D. Cunningham, Julie A. Stenken, "In Vivo Glucose Sensing", Wiley, 2010 Nao Wada, Yasutoshi Ishihara, "Basic Study on Measurable Depth by Photoacoustic Spectroscopy", Biomedical Engineering, February 10, 2011, Vol. 49, pp. 220-225 Yukihiro Ozaki, Akifumi Uda, Toshio Akai, "Multivariate Analysis for Chemists", Kodansha, 2002

However, when measuring the spectral spectrum at a plurality of wavelengths as in the method described in Non-Patent Document 4 described above, it is necessary to arrange light sources and detection devices having a plurality of wavelengths, which complicates the device and makes the measurement. There is a problem that it takes time. In particular, the amount of glucose in a living body is very small, and high measurement accuracy is required at all wavelengths for measuring the spectral spectrum. Therefore, when the method described in Non-Patent Document 4 is used, the problems of complication of the apparatus and lengthening of the measurement time appear remarkably.

Therefore, in order to solve these problems, an object of the present invention is to provide a technique capable of measuring the concentration of a target component contained in a measurement target using a simple device.

One aspect of the present invention is a first irradiation unit that irradiates a measurement target having a target component and a non-target component with light having a first wavelength, and light having a second wavelength different from the first wavelength. The second irradiation unit that irradiates the measurement target with light, the first irradiation unit irradiates the measurement target with light of the first wavelength, and the second irradiation unit irradiates the measurement target with light of the second wavelength. When the measurement target is irradiated with intensity, the first acquisition unit that acquires the physical quantity due to the change in the measurement target and the first irradiation unit irradiate the measurement target with light of the first wavelength. When the second irradiation unit irradiates the measurement target with light of the second wavelength at a second intensity different from the first intensity, a second acquisition for acquiring a physical quantity due to a change in the measurement target. A temperature information acquisition unit that acquires temperature information that is information on a temperature change of the measurement target based on the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit, and the temperature information. This is a concentration measuring device including a physical quantity acquired by the first acquisition unit and a concentration acquisition unit for acquiring the concentration of the non-target component based on the physical quantity acquired by the second acquisition unit.

One aspect of the present invention is the above-mentioned concentration measuring device, and the concentration acquisition unit acquires the said concentration by multivariate analysis.

One aspect of the present invention is the concentration measuring device, wherein the concentration acquisition unit is a learning model learned in advance, and the physical quantity acquired by the first acquisition unit and the second acquisition unit acquire the physical quantity. The concentration is acquired based on a learning model that represents the relationship between the physical quantity, the temperature information, and the concentration.

One aspect of the present invention is the above-mentioned concentration measuring device, in which the second wavelength is a wavelength at which the absorbance of the target component is smaller than the absorbance of the non-target component.

One aspect of the present invention is the concentration measuring device, wherein the second wavelength is a wavelength that changes the absorption spectrum of the non-target component to a predetermined magnitude or more.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, and the second wavelength is a wavelength at which the absorbance of the non-target component is maximized.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, in which the second wavelength is a wavelength within ± 70 nanometers centered on the wavelength at which the absorbance of the non-target component is maximum.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, in which the first wavelength is a wavelength within ± 70 nanometers centered on the wavelength at which the absorbance of the target component is maximum.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, and the first wavelength is a wavelength at which the absorbance of the target component is maximized.

One aspect of the present invention is the concentration measuring device, which expresses the influence of the environment on the physical quantity based on the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit. A correction unit that acquires a correction coefficient that is a value and corrects the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit by the acquired correction coefficient is further provided.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, and the influence of the environment is the amount of the non-target component.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, and the influence of the environment is the absorbance of the non-target component with respect to the first wavelength and the absorbance of the non-target component with respect to the second wavelength. ..

One aspect of the present invention is the above-mentioned concentration measuring device, and the influence of the environment is the performance of the light receiving unit that receives the light of the first wavelength.

One aspect of the present invention is the concentration measuring device, in which at least one of the first wavelength light and the second wavelength light is encoded light.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, in which an nth irradiation unit (n is an integer of 3 or more) that irradiates a measurement target having a target component and a non-target component with light having an nth wavelength. Further prepare.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, in which the second wavelength and the third wavelength have a predetermined correlation with respect to the shift of the absorption spectrum of the non-objective component.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, in which the second wavelength and the third wavelength are opposite in sign to each other with the wavelength of the peak of the absorption spectrum of the non-objective component as the origin. The wavelength located at the position.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, in which the second wavelength and the third wavelength are opposite in sign to each other with the wavelength of the inflection point of the absorption spectrum of the non-objective component as the origin. It is a wavelength located at the position of.

One aspect of the present invention is the above-mentioned concentration measuring device, in which the physical quantity is the intensity of transmitted light, scattered light, or reflected light of light irradiated to the measurement target.

One aspect of the present invention is the above-mentioned concentration measuring device, in which the physical quantity is the intensity of transmitted light of the light applied to the measurement target.

One aspect of the present invention is the above-mentioned concentration measuring device, in which the physical quantity is the amplitude of a vibration wave generated in the measuring object by the light applied to the measuring object.

One aspect of the present invention is the above-mentioned concentration measuring device, in which the vibration wave is the amplitude of a heat wave generated in the measurement target by the light applied to the measurement target.

One aspect of the present invention is the above-mentioned concentration measuring device, in which the vibration wave is the amplitude of a sound wave due to a heat wave generated in the measurement target by the light applied to the measurement target.

One aspect of the present invention is the above-mentioned concentration measuring device, wherein a piezoelectric body that generates a voltage proportional to the magnitude of the pressure when a pressure is applied, and the piezoelectric body that applies tension to the piezoelectric body to obtain the piezoelectric body. The first acquisition unit and the second acquisition unit are provided with a holder that is in close contact with the measurement target, and the first acquisition unit and the second acquisition unit acquire the physical quantity based on the voltage generated by the piezoelectric body.

One aspect of the present invention is the above-mentioned concentration measuring apparatus, and the temperature information is a shift amount of an absorption spectrum of the non-target component.

One aspect of the present invention is a first irradiation unit that irradiates a measurement target having a target component and a non-target component with light having a first wavelength, and light having a second wavelength different from the first wavelength. The second irradiation unit that irradiates the measurement target with light, the first irradiation unit irradiates the measurement target with light of the first wavelength, and the second irradiation unit irradiates the measurement target with light of the second wavelength. When the measurement target is irradiated with intensity, the first acquisition unit that acquires the physical quantity due to the change in the measurement target and the first irradiation unit irradiate the measurement target with light of the first wavelength. When the second irradiation unit irradiates the measurement target with light of the second wavelength at a second intensity different from the first intensity, the second acquisition of acquiring the physical quantity due to the change of the measurement target. The temperature information acquisition unit that acquires temperature information that is information on the temperature change of the measurement target based on the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit, and the temperature information. A concentration measuring method performed by a concentration measuring device including a concentration acquisition unit that acquires the concentration of the non-target component based on the physical amount acquired by the first acquisition unit and the physical amount acquired by the second acquisition unit. A first irradiation step of irradiating the measurement target with light of the first wavelength, a second irradiation step of irradiating the measurement target with light of the second wavelength, and the first irradiation unit are described. When the measurement target is irradiated with light of the first wavelength and the second irradiation unit irradiates the measurement target with light of the second wavelength with the first intensity, a physical quantity caused by a change in the measurement target. In the first acquisition step of acquiring the above, the first irradiation unit irradiates the measurement target with light of the first wavelength, and the second irradiation unit uses the light of the second wavelength as the first intensity. When the measurement target is irradiated with a different second intensity, the second acquisition step of acquiring the physical quantity due to the change of the measurement target, the physical quantity acquired by the first acquisition unit, and the acquisition by the second acquisition unit. A temperature information acquisition step for acquiring temperature information which is information on a temperature change of a measurement target based on the physical quantity obtained, a physical quantity acquired by the temperature information, the first acquisition unit, and a physical quantity acquired by the second acquisition unit. Based on the above, the concentration measuring method includes a concentration acquisition step for acquiring the concentration of the non-target component.

One aspect of the present invention is a non-temporary recording medium that stores a program for operating a computer as the concentration measuring device according to claim 1.

According to the present invention, it is possible to measure the concentration of a target component contained in a measurement target using a simple device.

It is a figure which shows an example of the functional structure of the concentration measuring apparatus 1 of 1st Embodiment. It is a figure which shows the relationship between the absorption spectrum of the target component and the absorption spectrum of a non-target component of light of a 1st wavelength and light of a 2nd wavelength in 1st Embodiment. It is a figure which shows an example of the functional structure of the information processing unit 100 in 1st Embodiment. It is a flowchart which shows an example of the flow of the process which the information processing unit 100 acquires the glucose concentration in 1st Embodiment. FIG. 1 is a first diagram showing a simulation result showing the dependence of the absorption spectrum of the living body 9 on the intensity of the second wavelength in the first embodiment. FIG. 2 is a second diagram showing a simulation result showing the dependence of the absorption spectrum of the living body 9 on the intensity of the second wavelength in the first embodiment. It is a figure which shows an example of the functional structure of the concentration measuring apparatus 2 of 2nd Embodiment. It is a figure which shows an example of the structure of the pressure sensitive part 26 in 2nd Embodiment. It is a figure which shows an example of the functional structure of the information processing unit 200 in 2nd Embodiment. It is a flowchart which shows an example of the flow of the process which the information processing unit 200 in 2nd Embodiment acquires the glucose concentration. It is a figure which shows an example of the functional structure of the density measuring apparatus 1a of a modification. It is a figure which shows an example of the functional structure of the information processing unit 100a in the modification. It is a figure which shows an example of the absorption spectrum of water and glucose used in the simulation. FIG. 1 is a first diagram showing an example of a simulation result showing an error from the true value of the glucose concentration obtained by multivariate analysis. FIG. 2 is a second diagram showing an example of a simulation result showing an error from the true value of the glucose concentration obtained by multivariate analysis. It is a figure which shows an example of the error between the concentration of glucose and the true value acquired by the concentration measuring apparatus 1, 2 and 1a based on the learning result of machine learning.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. Hereinafter, as an example of the embodiment of the present invention, an embodiment for measuring the blood glucose level (glucose concentration) in the living body will be taken as an example, and the description will be made assuming that the target component of the measurement is glucose and the non-target component is water. do. However, the present invention can be applied by the same concept even when these target substances are different or the number of non-target components is plural. For example, there are cases where the target component is glucose and the non-target component is water, protein and lipid, and cases where the target component is hemoglobin and the non-target component is protein and lipid.

(Outline of principle)
First, the outline of the principle of the embodiment will be described. Prior to the explanation, I will define some words. Hereinafter, light having a wavelength having a large absorbance of glucose is referred to as target component excitation light. Hereinafter, light having a wavelength having a high absorbance of water is referred to as non-target component excitation light. Hereinafter, transmission of the target component excitation light when the target component excitation light and the non-target component excitation light having an intensity of E1 (hereinafter referred to as “first non-target component excitation light”) are irradiated to the living body to be measured. The light is called the first target component transmitted light. Hereinafter, the transmitted light of the non-objective component excitation light I1 when the target component excitation light and the first non-objective component excitation light are irradiated to the living body to be measured is referred to as the first non-objective component transmitted light. Hereinafter, the target component excitation light when the target component excitation light and the non-target component excitation light having an intensity of the second intensity E2 (hereinafter referred to as “second non-target component excitation light”) are irradiated to the living body to be measured. The transmitted light of is referred to as the second target component transmitted light. The second strength E2 is a value larger than that of the first strength E1. Hereinafter, the transmitted light of the second intensity non-objective component excitation light when the target component excitation light and the second intensity non-objective component excitation light are irradiated to the living body to be measured is referred to as the second non-objective component transmitted light.

Return to the description of the outline of the principle of the embodiment. The invention of the embodiment is the difference between the intensity of the transmitted light of the first target component and the intensity of the transmitted light of the second target component, and the difference between the intensity of the transmitted light of the first non-target component and the intensity of the transmitted light of the second non-target component. Based on, the glucose concentration is obtained.
When the intensity of the non-target component excitation light irradiated to the living body 9 changes, the temperature of water changes, so that the absorption spectrum of water shifts. Therefore, based on the difference between the intensity of the first target component transmitted light and the intensity of the second target component transmitted light, and the difference between the intensity of the first non-target component transmitted light and the intensity of the second non-target component transmitted light. , The amount of shift in the absorption spectrum of water is obtained. The magnitude of the change in the glucose absorption spectrum with respect to the change in the intensity of the non-target component excitation light irradiated to the living body 9 is negligibly small with respect to the magnitude of the change in the water absorption spectrum. This means that the difference between the intensity of the first target component transmitted light and the intensity of the second target component transmitted light is due to the change in the absorption spectrum of water at the wavelength of the target component excitation light. Therefore, the influence of water on the absorbance of the target component excitation light is obtained based on the shift amount of the water absorption spectrum and the difference between the intensity of the first target component transmitted light and the intensity of the second target component transmitted light. Since the effect of water on the absorbance of the target component excitation light is obtained, the effect of glucose on the absorbance of the target component excitation light based on the difference between the intensity of the first target component transmitted light and the intensity of the second target component transmitted light. Is obtained and the concentration of glucose is obtained.
In the invention of the embodiment, it is not always necessary to acquire the transmitted light to acquire the glucose concentration. In the invention of the embodiment, the glucose concentration may be obtained by a physical quantity proportional to the intensity of transmitted light of the light applied to the living body 9, such as the amplitude of a vibration wave. The vibration wave includes an elastic wave and a sound wave generated by a heat wave.
The first intensity E1 may be 0. When the first intensity E1 is 0, it means that the first target component excitation light is not irradiated.
This is the end of the outline of the principle of the embodiment.

(First Embodiment)
FIG. 1 is a diagram showing an example of the functional configuration of the concentration measuring device 1 of the first embodiment.
The concentration measuring device 1 includes a CPU (Central Processing Unit) 11 connected by a bus, a memory 12, an auxiliary storage device 13, and the like, and by executing a program, the input unit 10, the first irradiation unit 14, and the second irradiation unit 1 are executed. 15. It functions as a device including a light receiving unit 16 and an output unit 17. The concentration measuring device 1 controls the operations of the input unit 10, the first irradiation unit 14, the second irradiation unit 15, and the light receiving unit 16 by executing a program, and the object is based on the result received by the light receiving unit 16. Obtain the concentration of the component.

The auxiliary storage device 13 is configured by using a storage device such as a magnetic hard disk device or a semiconductor storage device. The auxiliary storage device 13 stores a program related to the operation of the concentration measuring device 1.
The CPU 11 functions as an information processing unit 100 by executing a program stored in the memory 12 or the auxiliary storage device 13.
The input unit 10 includes an input device such as a mouse, a keyboard, and a touch panel. The input unit 10 may be configured as an interface for connecting these input devices to its own device. The input unit 10 receives input of information to its own device. The input unit 10 outputs the input information to the information processing unit 100.

The first irradiation unit 14 irradiates the living body 9 to be measured with light having a first wavelength. In the present embodiment, the light having the first wavelength is the target component excitation light. The light having the first wavelength is light having a wavelength of 1600 nanometers, which has a maximum absorbance of glucose. The light having the first wavelength does not necessarily have to be the light having the wavelength at which the absorbance of glucose is maximum.
The light having the first wavelength may be, for example, light having a wavelength of 1600 ± 70 nanometers, which is a wavelength near the wavelength at which the absorbance of glucose is substantially maximum. That is, the first wavelength may be a wavelength within the range of ± 70 nanometers centered on the wavelength at which the absorbance of glucose is maximum.
The light having the first wavelength may be, for example, light having a wavelength of 1600 ± 30 nanometers, which has a substantially maximum absorbance of glucose. When the light of the first wavelength is light having a wavelength of 1600 ± 30 nanometers at which the absorbance of glucose is substantially maximum, the light of the first wavelength is light having a wavelength of 1600 ± 70 nanometers. The glucose concentration is measured accurately.
The light having the first wavelength may be, for example, light having a wavelength of 1600 nanometers, which has a substantially maximum absorbance of glucose. When the light of the first wavelength is light having a wavelength of 1600 nanometers where the absorbance of glucose is substantially maximum, it is higher than when the light of the first wavelength is light having a wavelength of 1600 ± 30 nanometers. The glucose concentration is measured accurately.

The first irradiation unit 14 may irradiate light of the first wavelength in any way. The first irradiation unit 14 may include, for example, a laser diode driver or a semiconductor laser, and may irradiate light having a first wavelength with the laser diode driver or the semiconductor laser. The first irradiation unit 14 may be equipped with, for example, a general-purpose inexpensive laser and irradiate light having a wavelength of 1600 ± 70 nanometers. The light emitted by the first irradiation unit 14 is CW (Continuous Wave) light.

Further, the first irradiation unit 14 includes the irradiation direction of the light of the first wavelength, the distance between the first light source which is the light source of the light of the first wavelength and the living body 9, the irradiation angle of the light, and the first. It is provided with a first irradiation unit adjusting mechanism, which is a mechanism for adjusting the radiation intensity of light having a wavelength of 1. The first irradiation unit 14 controls the intensity of the light to be irradiated by the first irradiation unit adjustment mechanism. Since the first irradiation unit 14 includes the first irradiation unit adjustment mechanism, the concentration measuring device 1 measures the glucose concentration with a constant accuracy regardless of the angle or distance between the first light source and the living body 9. Can be done. However, it is not necessary to provide all the adjustment mechanisms for the irradiation distance, angle, and intensity, and an alternative function can be provided as needed, but it can be omitted as appropriate depending on the application and performance.

The second irradiation unit 15 irradiates the living body 9 to be measured with light having a second wavelength in which the absorbance of glucose, which is a target component, is smaller than the absorbance of water, which is a non-target component. The light of the second wavelength is the non-objective component excitation light.

The light of the second wavelength is, for example, 1450 nanometers of light having a wavelength in which the absorbance of glucose is smaller than that of water and the absorbance of water is maximum. The light of the second wavelength does not necessarily have to be the wavelength at which the absorbance of water is maximum.
For example, the light of the second wavelength may be light having a wavelength of 1450 ± 70 nanometers, which is a wavelength near the wavelength at which the absorbance of water is maximum. That is, the second wavelength may be a wavelength within the range of ± 70 nanometers centered on the wavelength at which the absorbance of water is maximum.
The light of the second wavelength may be light having a wavelength of 1450 ± 50 nanometers, which is the wavelength at which the absorbance of water is substantially maximum. When the light of the second wavelength is the light of the wavelength of 1450 ± 50 nanometers, which is the wavelength at which the absorbance of water is substantially maximum, the light of the second wavelength is the light of the wavelength of 1450 ± 70 nanometers. Glucose concentration is measured more accurately than in some cases.
The light of the second wavelength may be light of a wavelength of 1450 nanometers, which is the wavelength at which the absorbance of water is maximum. When the light of the second wavelength is light having a wavelength of 1450 nanometers, which is the wavelength at which the absorbance of water is maximum, the light of the second wavelength is light having a wavelength of 1450 ± 50 nanometers. The glucose concentration is measured accurately.

The second irradiation unit 15 may irradiate light having a second wavelength in any way. The second irradiation unit 15 may include, for example, a laser diode driver or a semiconductor laser, and may irradiate light having a second wavelength with the laser diode driver or the semiconductor laser. The second irradiation unit 15 is provided with, for example, a general-purpose inexpensive laser, and may irradiate light having a wavelength of 1450 ± 70 nanometers with the general-purpose inexpensive laser. The light emitted by the second irradiation unit 15 is CW (Continuous Wave) light.

Further, the second irradiation unit 15 includes the irradiation direction of the light of the second wavelength, the distance between the second light source which is the light source of the light of the second wavelength and the living body 9, the irradiation angle of the light, and the second. It is provided with a second irradiation unit adjusting mechanism, which is a mechanism for adjusting the radiation intensity of light having two wavelengths. The second irradiation unit 15 controls the intensity of the light to be irradiated by the second irradiation unit adjustment mechanism. Since the second irradiation unit 15 includes the second irradiation unit adjustment mechanism, the concentration measuring device 1 measures the glucose concentration with a constant accuracy regardless of the angle or distance between the second light source and the living body 9. Can be done. However, it is not necessary to provide all the adjustment mechanisms for the irradiation distance, angle, and intensity, and an alternative function can be provided as needed, but it can be omitted as appropriate depending on the application and performance.

The light receiving unit 16 includes a detector such as lead sulfide (PbS) having a photoelectric effect and indium gallium arsenide (InGaAs) having a photovoltaic effect. The light receiving unit 16 receives the light emitted by the first irradiation unit 14 and transmitted through the living body 9. The light receiving unit 16 receives the light emitted by the second irradiation unit 15 and transmitted through the living body 9.
The light receiving unit 16 may receive the transmitted light of the light of the first wavelength and the transmitted light of the light of the second wavelength. The light receiving unit 16 is provided with, for example, a bandpass filter that allows only the light of the first wavelength and the light of the second wavelength to pass between the light receiving unit 16 and the living body 9, so that the light of the first wavelength can be transmitted. Only the transmitted light and the transmitted light of the light of the second wavelength may be received.

The output unit 17 outputs the concentration of the target component acquired by the own device. The output unit 17 may be any as long as it can output the concentration of the target component acquired by the own device. The output unit 17 may be configured to include, for example, an interface for connecting the own device to an external device. The output unit 17 may include, for example, a display device such as a CRT (Cathode Ray Tube) display, a liquid crystal display, or an organic EL (Electro-Luminescence) display. The output unit 17 may be configured as, for example, an interface for connecting these display devices to its own device.

FIG. 2 is a diagram showing the relationship between the absorption spectrum of the target component and the absorption spectrum of the non-target component of the light of the first wavelength and the light of the second wavelength in the first embodiment.
The horizontal axis of FIG. 2 represents a wavelength. The vertical axis of FIG. 2 represents the absorbance. In FIG. 2, the target component is glucose. In FIG. 2, the non-target component is water. FIG. 2 shows that the first wavelength is 1600 nanometers, which is the maximum absorption spectrum of glucose. FIG. 2 shows that the second wavelength is 1450 nanometers, where the absorption spectrum of water is approximately maximal.

FIG. 3 is a diagram showing an example of the functional configuration of the information processing unit 100 in the first embodiment.
The information processing unit 100 includes a control unit 110, a first intensity acquisition unit 120, a second intensity acquisition unit 130, a correction unit 140, a temperature information acquisition unit 150, and a concentration acquisition unit 160.

The control unit 110 controls the operations of the first irradiation unit 14, the second irradiation unit 15, and the light receiving unit 16. The control unit 110 controls, for example, the timing at which the first irradiation unit 14 and the second irradiation unit 15 irradiate the living body 9 with light. The control unit 110 can be configured to control the irradiation distance, angle, and intensity of the first irradiation unit 14 and the second irradiation unit 15, for example.

The first intensity acquisition unit 120 acquires the intensity of the light received by the light receiving unit 16 when the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E1. When the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E1, the light received by the light receiving unit 16 is the first target component transmitted light and the first non-target component transmitted light. Is. When the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E1, the temperature of the water is such that the light of the first wavelength and the light of the second wavelength of the intensity E2 are living bodies. It is lower than the temperature of water when it is irradiated to 9. Hereinafter, the state of water when the living body 9 is irradiated with the light of the first wavelength and the light of the first wavelength of the intensity E1 is referred to as a low temperature state. Hereinafter, the light transmitted through the water in the low temperature state and received by the light receiving unit 16 is referred to as the transmitted light in the low temperature state.
The first intensity acquisition unit 120 outputs the acquired intensity of the transmitted light in the low temperature state to the temperature information acquisition unit 150 and the concentration acquisition unit 160.

The second intensity acquisition unit 130 acquires the intensity of the light received by the light receiving unit 16 when the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E2. When the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E2, the light received by the light receiving unit 16 is the second target component transmitted light and the second non-target component transmitted light. Is. Hereinafter, the state of water when the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E2 is referred to as a high temperature state. Hereinafter, the light transmitted through the water in the high temperature state and received by the light receiving unit 16 is referred to as the transmitted light in the high temperature state.
The second intensity acquisition unit 130 outputs the acquired intensity of the transmitted light in the high temperature state to the temperature information acquisition unit 150 and the concentration acquisition unit 160.

The correction unit 140 acquires the first correction coefficient based on the information indicating the intensity of the transmitted light in the low temperature state and the intensity of the transmitted light in the high temperature state (hereinafter referred to as “first measurement result information”). The first correction coefficient is a value for correcting the intensity of the transmitted light in the low temperature state and the intensity of the transmitted light in the high temperature state, which are the measurement results.
The first correction coefficient is a value that changes according to the amount of water. The first correction coefficient is a value that changes according to the wavelength of the light that irradiates the living body 9. The first correction coefficient is a value according to the performance of the light receiving unit 16.
That is, the first correction coefficient is a value representing the influence of the environment. The environmental impact is, for example, the amount of water. Environmental influences are, for example, the absorbance of water for the first wavelength and the absorbance of water for the second wavelength. The influence of the environment is, for example, the performance of the light receiving unit 16.

The correction unit 140 may acquire the amount of water of the living body 9 based on the first measurement result information, and may acquire the first correction coefficient based on the acquired amount of water. The correction unit 140 acquires the amount of water in the living body 9 based on the first measurement result information, and acquires the first correction coefficient based on the acquired amount of water, the first wavelength, and the second wavelength. You may.

The correction unit 140 may acquire the amount of water in any way. The correction unit 140 may acquire the amount of water by, for example, multivariate analysis. The correction unit 140 is based on, for example, a learning model that represents the relationship between the intensity of transmitted light in a low temperature state, the intensity of transmitted light in a high temperature state, and the amount of water, which has been learned in advance by a machine learning method such as a neural network. You may get the amount of water. The correction unit 140 includes, for example, the intensity of transmitted light in a low temperature state, the intensity of transmitted light in a high temperature state, the first wavelength, the second wavelength, and the amount of water, which have been learned in advance by a machine learning method such as a neural network. The amount of water may be obtained based on a learning model that represents the relationship with.

The correction unit 140 corrects the intensity of the transmitted light in the low temperature state and the intensity of the transmitted light in the high temperature state based on the acquired first correction coefficient.
Hereinafter, for the sake of simplicity, the corrected value of the intensity of the transmitted light in the low temperature state acquired by the first intensity acquisition unit 120 is also referred to as the intensity of the transmitted light in the low temperature state. Hereinafter, for the sake of simplicity, the corrected value of the intensity of the transmitted light in the high temperature state acquired by the second intensity acquisition unit 130 is also referred to as the intensity of the transmitted light in the high temperature state.

The temperature information acquisition unit 150 acquires information on the temperature change of the living body 9 at the light irradiation point (hereinafter referred to as “temperature information”) based on the first measurement result information. The light irradiation point is the living body 9. It is a part or all of the part where the light of the first wavelength and the light of the second wavelength are irradiated. The temperature information is the information about the temperature change of the living body 9 at the part where the light is irradiated. Any information may be used, for example, a shift amount of the absorption spectrum of water.
The temperature information acquisition unit 150 may acquire the temperature information by any method as long as the temperature information can be acquired. The temperature information acquisition unit 150 may acquire temperature information by, for example, multivariate analysis. The temperature information acquisition unit 150 may acquire temperature information based on a learning model representing the relationship between the first measurement result information and the temperature information, which has been learned in advance by a machine learning method such as a neural network.

The concentration acquisition unit 160 acquires the glucose concentration by the first concentration acquisition method based on the temperature information acquired by the temperature information acquisition unit 150 and the first measurement result information. The first concentration acquisition method may be any method as long as the glucose concentration can be acquired based on the temperature information and the first measurement result information. The first concentration acquisition method may be, for example, a method of multivariate analysis. The first concentration acquisition method may be a method in which the glucose concentration is acquired based on the first concentration learning model when the first concentration learning model is stored in the auxiliary storage device 13 in advance. The first concentration learning model is a learning model learned by machine learning such as a neural network, and is a learning model that represents the relationship between temperature information and first measurement result information and glucose concentration.

FIG. 4 is a flowchart showing an example of a flow of processing in which the information processing unit 100 acquires the glucose concentration in the first embodiment.
The first irradiation unit 14 irradiates the living body 9 with light having a first wavelength, and the second irradiating unit 15 irradiates the living body 9 with light having a second wavelength of intensity E1. The first intensity acquisition unit 120 acquires the intensity of transmitted light in a low temperature state. The first intensity acquisition unit 120 outputs the acquired intensity of the transmitted light in the low temperature state to the temperature information acquisition unit 150 and the concentration acquisition unit 160 (step S101). The irradiation by the first irradiation unit 14 and the irradiation by the second irradiation unit 15 may be performed at the same time, or may be executed with a predetermined time difference.

The first irradiation unit 14 irradiates the living body 9 with light having a first wavelength, and the second irradiating unit 15 irradiates the living body 9 with light having a second wavelength of intensity E2. The second intensity acquisition unit 130 acquires the intensity of transmitted light in a high temperature state. The second intensity acquisition unit 130 outputs the acquired intensity of the transmitted light in a high temperature state to the temperature information acquisition unit 150 and the concentration acquisition unit 160. (Step S102). The irradiation by the first irradiation unit 14 and the irradiation by the second irradiation unit 15 may be performed at the same time, or may be executed with a predetermined time difference.

The correction unit 140 acquires the first correction coefficient based on the intensity of the transmitted light in the low temperature state and the intensity of the transmitted light in the high temperature state, and the intensity of the transmitted light in the low temperature state and the high temperature state based on the acquired first correction coefficient. The intensity of the transmitted light is corrected (step S103).

The temperature information acquisition unit 150 acquires temperature information based on the first measurement result information (step S104).
The concentration acquisition unit 160 acquires temperature information based on the first measurement result information and temperature information, and acquires the glucose concentration by the first concentration acquisition method based on the temperature information and the first measurement result (step S105).

(Experimental result)
Here, FIGS. 5 and 6 show that the absorption spectrum of the living body 9 is changed by irradiating the living body 9 having the second wavelength in the first embodiment.
FIG. 5 is a diagram showing simulation results showing the dependence of the absorption spectrum of the living body 9 having a wavelength of 1590 nanometers to 1610 nanometers with respect to the intensity of the second wavelength in the first embodiment.
FIG. 5 shows absorption spectra when the intensity of the second wavelength is 0 mW, 10 mW, 15 mW, and 20 mW.
FIG. 5 shows that the absorption spectrum changes due to the change in the intensity of the second wavelength. The amount of change in the absorption spectrum of the living body 9 is substantially the same as the amount of change in the absorption spectrum of water.

FIG. 6 is a diagram showing simulation results showing the dependence of the absorption spectrum of the living body 9 having a wavelength of 1386 nanometers to 1392 nanometers with respect to the intensity of the second wavelength in the first embodiment.
FIG. 6 shows the absorption spectra of the case where the intensity of the second wavelength is 0 mW, the case where the intensity is 10 mW, the case where the intensity is 15 mW, and the case where the intensity is 20 mW.
FIG. 6 shows that the absorption spectrum changes due to the change in the intensity of the second wavelength. The amount of change in the absorption spectrum of the living body 9 is substantially the same as the amount of change in the absorption spectrum of water.

FIG. 5 shows that when the living body 9 is irradiated with a second wavelength of 20 mW, the change in absorbance is 1.4% at a wavelength of 1600 nanometers. FIG. 6 shows that when the living body 9 is irradiated with a second wavelength of 20 mW, the change in absorbance is 1.7% at a wavelength of 1390 nanometers. This means that the temperature of the living body 9 was changed by about 2 degrees by the second wavelength of 20 mW.

As shown in FIGS. 5 and 6, the second wavelength causes a shift in the water absorption spectrum of the living body 9 to the extent that the concentration measuring device 1 of the first embodiment can observe it. Therefore, the concentration measuring device 1 of the first embodiment can detect the shift of the water absorption spectrum of the living body 9, and can measure the glucose concentration based on the change of the water absorption spectrum of the living body 9.

Since the concentration measuring device 1 of the first embodiment configured in this way includes the temperature information acquisition unit 150 and the concentration acquisition unit 160, the glucose concentration of the living body 9 is acquired based on the first measurement result information. Can be done. Therefore, the concentration measuring device 1 of the first embodiment can measure the concentration of the target component contained in the measurement target by using a simple device.

The concentration measuring device 1 does not necessarily have to measure the concentration of the target component by transmitted light. The concentration measuring device 1 may measure the concentration of the target component by reflected light or scattered light.

(Second Embodiment)
FIG. 7 is a diagram showing an example of the functional configuration of the concentration measuring device 2 of the second embodiment. The concentration measuring device 2 of the second embodiment modulates the intensity of the light irradiating the living body 9, and measures the glucose concentration at the target depth of the living body 9 by using photoacoustic spectroscopy. The target depth is the depth of the living body 9 for which the glucose concentration should be measured.
Hereinafter, those having the same functions as the functional units included in the concentration measuring device 1 will be designated by the same reference numerals as those in FIGS. 1 and 3, and the description thereof will be omitted.

The concentration measuring device 2 includes a CPU (Central Processing Unit) 21, a memory 22, an auxiliary storage device 23, and the like connected by a bus, and by executing a program, the input unit 10, the first irradiation unit 14, and the first modulation It functions as a device including a unit 24, a second irradiation unit 15, a second modulation unit 25, a pressure sensitive unit 26, and an output unit 17. The concentration measuring device 2 controls the operations of the input unit 10, the first irradiation unit 14, the first modulation unit 24, the second irradiation unit 15, the second modulation unit 25, and the pressure sensitive unit 26 by executing the program. , The concentration of the target component is acquired based on the result acquired by the pressure sensitive unit 26.

The first modulation unit 24 modulates the intensity of the light emitted by the first irradiation unit 14 at a frequency ω1 (first frequency) and a frequency ω2 (second frequency). The frequency ω1 is a frequency at which the vibration wave generated in the living body 9 at the target depth reaches the pressure sensitive unit 26 without being attenuated when the living body 9 is irradiated with the light of the frequency ω1. Further, the frequency ω2 is a frequency at which when the living body 9 is irradiated with light having a frequency ω2, the vibration wave generated in the living body 9 at the target depth is attenuated by the time it reaches the pressure sensitive portion 26. That is, the vibration wave generated in the living body 9 by the light modulated at the frequency ω1 reflects the vibration wave generated from the living body water existing in the vicinity of the dermis and the vibration wave from the mixed substance of the glucose in the blood vessel bed. On the other hand, the oscillating wave generated in the living body 9 by the light modulated at the frequency ω2 mainly reflects the oscillating wave generated from the living water existing in the vicinity of the dermis. The intensity of the oscillating wave is inversely proportional to the frequency and the depth. The frequency ω2 is a frequency higher than the frequency ω1.

The second modulation unit 25 modulates the intensity of the light emitted by the second irradiation unit 15 at a frequency ω3 which is a frequency different from the frequencies ω1 and ω2. The concentration measuring device 2 does not necessarily have to include only one second modulation unit 25. The concentration measuring device 2 may include two or more second modulation units 25.

FIG. 8 is a diagram showing an example of the structure of the pressure sensitive portion 26 in the second embodiment.
The pressure-sensitive unit 26 detects a vibration wave generated in the living body 9 by the light irradiated by the first irradiation unit 14. The pressure-sensitive unit 26 includes a piezoelectric film 261 formed of a piezoelectric material such as polyvinylidene fluoride, and a holder 262 that holds the piezoelectric film 261 while applying tension to the piezoelectric film 261. When a pressure is applied, the piezoelectric material generates a voltage proportional to the magnitude of the applied pressure. The piezoelectric material may be any piezoelectric material that generates a voltage proportional to the magnitude of the applied pressure when a pressure is applied. The piezoelectric body may be, for example, a microphone.
The holder 262 is formed of an elastic body such as silicon rubber, covers one side of the piezoelectric film 261 and is connected to the outer edge of the piezoelectric film 261. The holder 262 is formed so as not to come into contact with the piezoelectric film 261 except at the outer edge.
As a result, by applying the piezoelectric film 261 to the living body 9 and pressing the holder 262 against the living body 9, an elastic force of the holder 262 is generated in the outward direction with respect to the outer edge of the piezoelectric film 261, and the piezoelectric film 261 is tensioned. Is given. As an example of the shape of the holder 262, as shown in FIG. 8, a shape in which the inner surface and the outer surface facing the piezoelectric film 261 are formed in a hemispherical shape can be mentioned.
The holder 262 may include an acoustic tube. An acoustic tube is a device that enhances the vibration of sound waves generated by heat waves.
In this way, when the piezoelectric film 261 and the living body 9 are in contact with each other, the piezoelectric film 261 and the living body 9 can be brought into close contact with each other by applying tension to the piezoelectric film 261.

FIG. 9 is a diagram showing an example of the functional configuration of the information processing unit 200 in the second embodiment.
The information processing unit 200 includes a control unit 210, a first amplitude acquisition unit 220, a second amplitude acquisition unit 230, a correction unit 240, a temperature information acquisition unit 250, and a concentration acquisition unit 260.

The control unit 210 controls the operations of the first irradiation unit 14, the first modulation unit 24, the second irradiation unit 15, the second modulation unit 25, and the pressure sensitive unit 26. The control unit 210 controls, for example, the timing at which the first irradiation unit 14 and the second irradiation unit 15 irradiate the living body 9 with light. The control unit 210 controls, for example, the modulation frequency of the first modulation unit 24 and the modulation frequency of the second modulation unit 25.

The first amplitude acquisition unit 220 is the amplitude of the vibration wave detected by the pressure sensitive unit 26 when the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E1 (hereinafter, “low temperature”). The amplitude of the state ") is acquired. More specifically, the first amplitude acquisition unit 220 acquires the amplitude in the low temperature state based on the voltage generated by the piezoelectric body included in the pressure sensitive unit 26. The amplitude of the vibration wave is proportional to the intensity of the transmitted light of the light applied to the living body 9.

The second amplitude acquisition unit 230 is the amplitude of the vibration wave detected by the pressure sensitive unit 26 when the living body 9 is irradiated with the light of the first wavelength and the light of the second wavelength of the intensity E2 (hereinafter, “high temperature state”). ”) Is acquired. More specifically, the second amplitude acquisition unit 230 acquires the amplitude in the high temperature state based on the voltage generated by the piezoelectric body included in the pressure sensitive unit 26. The second amplitude acquisition unit 230 outputs the acquired amplitude of the vibration wave to the correction unit 240.

The correction unit 240 acquires the second correction coefficient based on the information indicating the amplitude in the low temperature state and the amplitude in the high temperature state (hereinafter referred to as “second measurement result information”).
The second correction coefficient is a value for correcting the amplitude in the low temperature state and the amplitude in the high temperature state, which are the measurement results. The second correction coefficient is a value that changes according to the amount of water. The second correction coefficient is a value that changes according to the wavelength of the light that irradiates the living body 9. The second correction coefficient is a value according to the performance of the pressure sensitive unit 26.
That is, the second correction coefficient is a value representing the influence of the environment. The environmental effect is, for example, the amount of water, and the environmental effect is, for example, the absorbance of water with respect to the first wavelength and the absorbance of water with respect to the second wavelength. The influence of the environment is, for example, the performance of the pressure sensitive unit 26.

The correction unit 240 acquires the amount of water in the living body 9 based on the second measurement result information, and acquires the second correction coefficient based on the acquired amount of water. The correction unit 240 acquires the amount of water in the living body 9 based on the amplitude in the low temperature state and the amplitude in the high temperature state, and the correction unit 240 obtains the amount of water and the first wavelength and the second wavelength based on the acquired amount of water. 2 The correction coefficient may be acquired.

The correction unit 240 may acquire the amount of water in any way. The correction unit 240 may acquire the amount of water by, for example, multivariate analysis. The correction unit 240 acquires the amount of water based on a learning model representing the relationship between the amplitude in the low temperature state, the amplitude in the high temperature state, and the amount of water, which has been learned in advance by a machine learning method such as a neural network. You may. The correction unit 240 is, for example, a learning that represents the relationship between the amplitude in the low temperature state, the amplitude in the high temperature state, the first wavelength, the second wavelength, and the amount of water, which has been learned in advance by a machine learning method such as a neural network. The amount of water may be obtained based on the model.

The correction unit 240 corrects the amplitude in the low temperature state and the amplitude in the high temperature state based on the acquired second correction coefficient.
Hereinafter, for the sake of simplicity, the corrected value of the amplitude of the vibration wave acquired by the first amplitude acquisition unit 220 is also referred to as the amplitude in the low temperature state. Hereinafter, for the sake of simplicity, the corrected value of the amplitude of the vibration wave acquired by the second amplitude acquisition unit 230 is also referred to as the amplitude in the high temperature state.

The temperature information acquisition unit 250 acquires temperature information based on the second measurement result information. The temperature information acquisition unit 250 may acquire the temperature information by any method as long as the temperature information can be acquired. The temperature information acquisition unit 250 may acquire temperature information by, for example, multivariate analysis. The temperature information acquisition unit 250 may acquire temperature information based on a learning model representing the relationship between the second measurement result information and the temperature information, which has been learned in advance by a machine learning method such as a neural network.

The concentration acquisition unit 260 acquires the glucose concentration in the living body 9 by the second concentration acquisition method based on the second measurement result information and the temperature information. The second concentration acquisition method may be any method as long as the glucose concentration can be acquired based on the second measurement result information and the temperature information. The second concentration acquisition method may be, for example, a method of multivariate analysis. The second concentration acquisition method may be a method in which the glucose concentration is acquired based on the second concentration learning model when the second concentration learning model is stored in the auxiliary storage device 23 in advance. The second concentration learning model is a learning model learned by machine learning such as a neural network, and is a learning model that represents the relationship between temperature information and second measurement result information and glucose concentration.

FIG. 10 is a flowchart showing an example of a flow of processing in which the information processing unit 200 in the second embodiment acquires the glucose concentration.
The first irradiation unit 14 irradiates the living body 9 with light of the first wavelength, and the second irradiation unit 15 irradiates the living body 9 with light of the second wavelength of intensity E1. Based on the vibration wave detected by the pressure sensitive unit 26, the first amplitude acquisition unit 220 acquires the amplitude in the low temperature state. The first amplitude acquisition unit 220 outputs the acquired amplitude in the low temperature state to the correction unit 240 (step S201). The irradiation by the first irradiation unit 14 and the irradiation by the second irradiation unit 15 may be performed at the same time, or may be executed with a predetermined time difference.

The first irradiation unit 14 irradiates the living body 9 with light having a first wavelength, and the second irradiating unit 15 irradiates the living body 9 with light having a second wavelength of intensity E2. Based on the vibration wave detected by the pressure sensitive unit 26, the second amplitude acquisition unit 230 acquires the amplitude in the high temperature state. The second amplitude acquisition unit 230 outputs the acquired amplitude in the high temperature state to the correction unit 240 (step S202). The irradiation by the first irradiation unit 14 and the irradiation by the second irradiation unit 15 may be performed at the same time, or may be executed with a predetermined time difference.

The correction unit 240 acquires a second correction coefficient based on the amplitude in the low temperature state and the amplitude in the high temperature state, and corrects the amplitude in the low temperature state and the amplitude in the high temperature state based on the acquired second correction coefficient (step S203). ).

The temperature information acquisition unit 250 acquires temperature information based on the second measurement result information (step S204).
The concentration acquisition unit 260 acquires the glucose concentration by the second concentration acquisition method based on the temperature information and the second measurement result information (step S205).

Since the concentration measuring device 2 of the second embodiment configured in this way includes the concentration acquisition unit 260, the glucose concentration of the living body 9 can be acquired based on the second measurement result information. Therefore, the concentration measuring device 2 of the second embodiment can measure the concentration of the target component contained in the measurement target by using a simple device.

The pressure-sensitive unit 26 in the second embodiment is not limited to the pressure-sensitive unit 26 shown in FIG. For example, the pressure sensitive portion 26 is formed only of the piezoelectric film 261 and may be attached to or wrapped around the surface of a living body. Further, the pressure sensitive unit 26 may be a system that detects minute fluctuations by applying an element such as a microphone or a piezoelectric element or a laser beam instead of the piezoelectric film 261.

(Modification example)
The concentration measuring device 1 of the first embodiment and the concentration measuring device 2 of the second embodiment are irradiated with excitation light under different conditions a plurality of times to increase the glucose concentration of the living body 9. You may measure.
In this way, the concentration measuring device 1 and the concentration measuring device 2 measure the glucose concentration based on the measurement results of the irradiation of a plurality of excitation lights under different conditions, so that the concentration measuring devices 1 and 2 have the glucose concentration. The measurement accuracy can be improved.

The correction unit 140 does not necessarily have to acquire the first correction coefficient based on the first measurement result information. The correction unit 140 may acquire a value calculated in advance as the first correction coefficient by performing an experiment of irradiating water with light having a wavelength of 1600 nanometers and light having a wavelength of 1450 nanometers.
The correction unit 240 does not necessarily have to acquire the second correction coefficient based on the second measurement result information. The correction unit 240 may acquire a value calculated in advance as the second correction coefficient by performing an experiment of irradiating water with light having a wavelength of 1600 nanometers and light having a wavelength of 1450 nanometers.

In the concentration measuring device 1, the light applied to the living body 9 does not necessarily have to be CW light. The light applied to the living body 9 has a predetermined pattern and may be coded light. The light irradiated to the living body 9 may be encoded by the electric power of the light, the irradiation time, and the observation wavelength.
By irradiating the encoded light as the light irradiating the living body 9 in this way, the measurement accuracy of the glucose concentration by the concentration measuring device 1 is higher than that in the case where the light radiating the living body 9 is CW light. Is improved.
The concentration measuring device 1 includes, for example, a first modulation unit 24 and a second modulation unit 25, and by controlling the operation of the first modulation unit 24 and the second modulation unit 25 by the control unit 110, the living body 9 can be used. The light to be irradiated may be encoded.
Similarly to the concentration measuring device 1, the concentration measuring device 1a may irradiate the living body 9 with coded light having a predetermined irradiation pattern.

The second wavelength is a wavelength in which the absorbance of glucose, which is a target component, is smaller than the absorbance of water, which is a non-target component, and any wavelength that changes the absorption spectrum of water to a predetermined magnitude or more. Wavelength may be.
The second wavelength is any wavelength that shifts the absorption spectrum of the non-target component so that the shift amount of the absorption spectrum of the non-target component can be measured by the concentration measuring device 1. The wavelength may be such that. The light of the second wavelength may be, for example, a terahertz wave or an ultraviolet ray.
The second wavelength may be the wavelength at the position of the inflection point of the absorption spectrum of the non-objective component.

The concentration measuring devices 1 and 2 do not necessarily have to include only one second irradiation unit 15. The concentration measuring device 1 and the concentration measuring device 2 may include two or more second irradiation units 15.
Hereinafter, for the sake of simplicity, the case where the concentration measuring device 1 includes two or more second irradiation units 15 will be described, but in the following description, the concentration measuring device 2 includes two or more second irradiation units 15. The same applies to the case except that the concentration of glucose is obtained based on the amplitude of the vibration wave instead of the concentration of glucose obtained based on the intensity of the transmitted light.
Hereinafter, the concentration measuring device 1 including one or more second irradiation units 15 is referred to as a concentration measuring device 1a. Hereinafter, the second irradiation unit 15 included in the concentration measuring device 1a is referred to as the nth irradiation unit 15- (n-1) (n is an integer of 2 or more and N or less, and N is an integer of 2 or more). The second irradiation unit 15-1 is, for example, the second irradiation unit 15 in the first embodiment. The second irradiation unit 15 in which n = 3 is, for example, the third irradiation unit 15-2.

FIG. 11 is a diagram showing an example of the functional configuration of the concentration measuring device 1a of the modified example. Hereinafter, those having the same functions as the functional units included in the concentration measuring device 1 will be designated by the same reference numerals as those in FIGS. 1, 3, 7, and 9, and the description thereof will be omitted.

The concentration measuring device 1a is provided with the nth irradiation unit 15- (n-1) in place of the second irradiation unit 15, a point in which the light receiving unit 16a is provided in place of the light receiving unit 16, and a point in which the information processing unit 100 is replaced. It differs from the concentration measuring device 1 in that the information processing unit 100a is provided.
The second irradiation unit 15-1 is the same as the second irradiation unit 15 in the first embodiment. The nth irradiation unit 15- (n-1) irradiates light having the nth wavelength. The nth irradiation unit 15- (n-1) is the same as the second irradiation unit 15 except that the wavelength of the light to be irradiated is the nth wavelength. The nth wavelength is the non-objective component excitation light.

The light receiving unit 16a not only receives the light emitted by the first irradiation unit 14 and transmitted through the living body 9 and the light irradiated by the second irradiation unit 15 and transmitted through the living body 9. It differs from the light receiving unit 16 in that it also receives the light emitted by the nth irradiation unit 15- (n-1) and transmitted through the living body 9.

In the information processing unit 100a, instead of the result of the first irradiation unit 14 and the second irradiation unit 15 irradiating the living body 9, N of the first irradiation unit 14 and the nth irradiation unit 15- (n-1) are used. It differs from the information processing unit 100 in that the irradiation unit acquires the glucose concentration based on the result of irradiating the living body 9.

FIG. 12 is a diagram showing an example of the functional configuration of the information processing unit 100a in the modified example.
The information processing unit 100a includes a control unit 110a instead of the control unit 110, a first strength acquisition unit 120a instead of the first strength acquisition unit 120, and a second strength acquisition unit 130 instead of the second strength acquisition unit 130. 2 It differs from the information processing unit 100a in that it includes a strength acquisition unit 130a.

The control unit 110a controls the operations of the first irradiation unit 14, the nth irradiation unit 15- (n-1), and the light receiving unit 16a. The control unit 110a controls, for example, the timing at which the first irradiation unit 14 and the nth irradiation unit 15- (n-1) irradiate the living body 9 with light.

The first intensity acquisition unit 120a acquires the intensity of transmitted light in a low temperature state and outputs it to the temperature information acquisition unit 150 and the concentration acquisition unit 160. The low temperature state in the concentration measuring device 1a is a state of water when the living body 9 is irradiated with the light of the first wavelength and the light of the nth wavelength of the intensity E1_n. The transmitted light in the low temperature state in the concentration measuring device 1a is the light transmitted through the water in the low temperature state and received by the light receiving unit 16a.

The second intensity acquisition unit 130a acquires the intensity of the transmitted light in a high temperature state and outputs it to the temperature information acquisition unit 150 and the concentration acquisition unit 160. The high temperature state in the concentration measuring device 1a is a state of water when the living body 9 is irradiated with the light of the nth wavelength and the light of the nth wavelength of the intensity E2_n. The intensity E2_n is a value larger than the intensity E1_n. The transmitted light in the high temperature state in the concentration measuring device 1a is the light transmitted through the water in the high temperature state and received by the light receiving unit 16a.

Since the concentration measuring device 1a of the modified example configured in this way acquires the concentration of glucose based on the result of irradiating the living body 9 with a plurality of non-objective component excitation lights, the data used for acquiring the concentration of glucose The number is larger than that of the concentration measuring device 1. Therefore, the concentration measuring device 1a can measure the glucose concentration with an accuracy higher than the measurement accuracy of the glucose concentration by the concentration measuring device 1a.

In the concentration measuring device 1a of the modified example, the second wavelength and the third wavelength may be any wavelength as long as it has a predetermined correlation with respect to the shift of the absorption spectrum of the non-objective component. good. The wavelength having a predetermined correlation is a wavelength that changes in a correlation with each other due to a shift in the absorption spectrum of the non-target component.
The wavelengths having a predetermined correlation may be, for example, two wavelengths located at positions where the signs are opposite to each other with the peak wavelength of the absorption spectrum of the non-objective component as the origin. The two wavelengths located at positions where the signs are opposite to each other with the peak wavelength of the absorption spectrum of the non-target component as the origin are, for example, 1450 + 70 nanometer wavelength and 1450 when the non-target component is water. It may have two wavelengths, one with a wavelength of −70 nanometers. The two wavelengths located at positions where the signs are opposite to each other with the peak wavelength of the absorption spectrum of the non-target component as the origin are, for example, 1450 + 20 nanometer wavelength and 1450 when the non-target component is water. It may have two wavelengths, one with a wavelength of -50 nanometers. The two wavelengths located at positions where the wavelengths of the peaks of the absorption spectrum of the non-objective component are opposite to each other with the wavelength of the peak of the absorption spectrum of the non-objective component as the origin are the turning points whose signs are opposite to each other with the wavelength of the peak of the absorption spectrum of the non-objective component as the origin. It may be a wavelength located at the position of.

The wavelengths having a predetermined correlation may be, for example, two wavelengths located at positions where the signs are opposite to each other with the wavelength of the inflection point of the absorption spectrum of the non-objective component as the origin. The two wavelengths located at positions where the signs are opposite to each other with the wavelength of the bending point of the absorption spectrum of the non-objective component as the origin are, for example, two wavelengths of H + 10 nanometer and H-10 nanometer. It may be one wavelength. H is the wavelength of the inflection point of the absorption spectrum of the non-target component. The two wavelengths located at positions where the signs are opposite to each other with the wavelength of the bending point of the absorption spectrum of the non-objective component as the origin are, for example, two wavelengths of H + 7 nanometer and H-5 nanometer. It may be one wavelength.

When the concentration measuring device 1a of the modified example has three or more irradiation units for irradiating the non-target component excitation light, the wavelength of each non-target component excitation light is a wavelength having a predetermined correlation. be. A predetermined correlation between three or more non-objective component excitation lights is, for example, that approximately half of the wavelengths are located on the positive side with the peak wavelength of the absorption spectrum of the non-objective component as the origin, and the remaining non-objective components. The relationship may be such that the wavelength of the component excitation light is located on the negative side.
Up to this point, the description of the concentration measuring device 1a of the modified example shown in FIG. 11 is completed.

The information processing units 100 and 100a may acquire the amount of water based on the first measurement result information. The information processing units 100 and 100a may acquire the amount of water in any way. The information processing units 100 and 100a may acquire the amount of water by, for example, multivariate analysis. The information processing units 100 and 100a are learning models that have been learned in advance by a machine learning method such as a neural network, and include the intensity of transmitted light in a low temperature state, the intensity of transmitted light in a high temperature state, and the amount of water. The amount of water may be obtained based on a learning model that represents the relationship.

When the first wavelength belongs to a wavelength band in which the change in the absorbance of water with respect to the temperature change is linear, the concentration measuring device 1 and the concentration measuring device 2 are machine-learned by a method of multivariate analysis. The glucose concentration can be measured with an accuracy equal to or higher than the measurement accuracy of the glucose concentration measured by the method.

On the other hand, when the first wavelength belongs to a wavelength band in which the change in the absorbance of water with respect to the temperature change is non-linear, the concentration measuring device 1 and the concentration measuring device 2 are increased by a machine learning method. The glucose concentration can be measured with an accuracy higher than the measurement accuracy of the glucose concentration measured by the method of variable wavelength analysis.
When the concentration measuring device 1 and the concentration measuring device 2 measure the concentration by the method of multivariate analysis, it is better that there is a correlation between the wavelengths with respect to the change occurring in the living body 9 for each wavelength irradiated to the living body 9. The accuracy of measurement is improved. On the other hand, when the concentration measuring device 1 and the concentration measuring device 2 measure the concentration by a machine learning method, there may not necessarily be a correlation with respect to the change occurring in the living body 9 for each wavelength irradiated to the living body 9.

The results of simulating the error between the glucose concentration and the true value acquired by the multivariate analysis by the concentration measuring devices 1, 2 and 1a will be described with reference to FIGS. 13 to 15.
FIG. 13 is a diagram showing an example of the absorption spectra of water and glucose used in the simulation.
The water used in the simulation is a spectrum with a maximum value at 1450 nanometers. The glucose used in the simulation is a spectrum having a maximum value at 1600 nanometers. In FIG. 13, the analysis wavelength point shows a candidate for the second wavelength in the simulation.

FIG. 14 shows an error from the true value of the glucose concentration acquired by the concentration measuring devices 1, 2 and 1a by the multivariate analysis when only the light of the second wavelength is irradiated as the non-target component excitation light. It is a figure which shows an example of the simulation result.
The simulation is an absorption spectrum of the living body 9 when the temperature of the living body 9 is 28 ° C., and the glucose concentration is 0%, 0.05%, 0.1%, 0.15%, and 0.2%, respectively. The absorption spectrum of the living body 9 and the absorption spectrum of the living body 9 when the temperature of the living body 9 is 30 ° C., and the glucose concentration is 0%, 0.05%, 0.1%, 0.15%, 0.2%. The absorption spectrum of the living body 9 in each case and the absorption spectrum of the living body 9 when the temperature of the living body 9 is 32 ° C., and the glucose concentration is 0%, 0.05%, 0.1%, 0.15%, 0. A total of 15 spectra were performed as known, with an absorption spectrum of living organism 9 in each case of .2%.
The simulation was performed assuming a true value of 31 ° C. and a glucose concentration of 0.07%.

The horizontal axis of FIG. 14 represents a wavelength. The vertical axis of FIG. 14 represents the error. In FIG. 14, the water estimation error is an error calculated by Michelet and represents an error between the amount of water acquired by the concentration measuring devices 1, 2 and 1a and the true value. In FIG. 14, the Glc estimation error is an error calculated by Michelet and represents an error between the glucose concentration acquired by the concentration measuring devices 1, 2 and 1a and the true value. In FIG. 14, the temperature estimation error is an error calculated by Michelet and represents an error between the temperature of water acquired by the concentration measuring devices 1, 2 and 1a and the true value.
In FIG. 14, the concentration of glucose acquired by the concentration measuring devices 1, 2 and 1a by the multivariate analysis when only the light of the second wavelength is irradiated as the non-target component excitation light has an error of 20 from the true value. Indicates a percentage to 25%.

FIG. 15 shows the concentration of glucose acquired by the concentration measuring devices 1, 2 and 1a by the multivariate analysis when the light of the second wavelength and the light of the third wavelength are irradiated as the non-objective component excitation light. It is a figure which shows an example of the simulation result which shows the error from a true value.
The simulation was performed assuming that the same information as in FIG. 14 is known. That is, also in FIG. 15, in the simulation, the absorption spectrum of the living body 9 at a temperature of the living body 9 of 28 ° C., and the glucose concentration is 0%, 0.05%, 0.1%, 0.15%, 0. The absorption spectrum of the living body 9 in each case of 2% and the absorption spectrum of the living body 9 when the temperature of the living body 9 is 30 ° C., and the glucose concentration is 0%, 0.05%, 0.1%, 0.15. The absorption spectrum of the living body 9 in each case of% and 0.2% and the absorption spectrum of the living body 9 when the temperature of the living body 9 is 32 ° C. and the glucose concentration is 0%, 0.05% and 0.1%. , 0.15% and 0.2%, respectively, and a total of 15 spectra with the absorption spectra of the living body 9 were carried out as known.
Also, as in FIG. 14, the simulation was performed assuming a true value of 31 ° C. and a glucose concentration of 0.07%.

The horizontal axis of FIG. 15 represents the wavelength. The vertical axis of FIG. 15 represents the error. In FIG. 15, when the light of the second wavelength and the light of the third wavelength longer than 1450 nanometers are irradiated as the non-objective component excitation light, the concentration measuring devices 1, 2 and 1a are subjected to multivariate analysis. The acquired glucose concentration indicates that the error from the true value is 5% to 10%.
Further, in FIG. 15, when the light of the second wavelength and the light of the third wavelength of 1450 nanometers or less are irradiated as the non-target component excitation light, the concentration measuring devices 1, 2 and 1a are multivariate. The concentration of glucose obtained by analysis indicates that the error from the true value is 20% to 25%.
When the light of the second wavelength and the light of the third wavelength of 1450 nanometers or less are irradiated as the non-objective component excitation light, the concentration measuring devices 1, 2 and 1a are based on the learning result of machine learning. It is desirable to obtain the concentration of glucose.

FIG. 16 is a diagram showing an example of an error between the glucose concentration and the true value acquired by the concentration measuring devices 1, 2 and 1a based on the learning result of machine learning.
Machine learning teacher data to obtain the results of FIG. 16 vary the true value of glucose concentration from 0.08 to 0.17% in 0.01% increments and temperature from 35 ° C to 37 ° C. It is the concentration of the glucose concentration acquired by the concentration measuring devices 1, 2 and 1a when the temperature is changed in steps of 0.2 ° C.
FIG. 16 shows the concentration measurement when the concentration measuring devices 1, 2 and 1a acquire the concentration of glucose having a true value of 0.085 to 0.165% at a temperature of 36 ° C. based on the trained model. The error between the concentration of glucose acquired by the devices 1, 2 and 1a and the true value is shown.
FIG. 16 also shows the error between the temperature acquired by the concentration measuring devices 1, 2 and 1a and the true value.
FIG. 16 shows that the error between the glucose concentration acquired by the concentration measuring devices 1, 2 and 1a and the true value is 2% or less based on the trained model.

All or part of the functions of the concentration measuring devices 1, 2 and 1a are realized by using hardware such as ASIC (Application Specific Integrated Circuit), PLD (Programmable Logic Device) and FPGA (Field Programmable Gate Array). May be done. The program may be recorded on a computer-readable recording medium. The computer-readable recording medium is, for example, a flexible disk, a magneto-optical disk, a portable medium such as a ROM or a CD-ROM, or a storage device such as a hard disk built in a computer system. The program may be transmitted over a telecommunication line.

The information processing units 100, 200, and 100a may be implemented by using a plurality of information processing devices that are communicably connected via a network. Further, the information processing units 100, 200 and 100a may output the measurement result. Further, the information processing units 100, 200 and 100a may be provided with a display device for displaying the measurement result. In this case, each of the functional units included in the information processing units 100, 200, and 100a may be distributed and mounted in a plurality of information processing devices. For example, the control unit 110, the first intensity acquisition unit 120 and the second intensity acquisition unit 130, the correction unit 140, the temperature information acquisition unit 150, and the concentration acquisition unit 160 may be mounted on different information processing devices. ..

The concentration measuring devices 1, 2 and 1a may be mounted by using a plurality of devices that are communicably connected via a network.
In this case, the concentration measuring device 1 includes, for example, a light measuring device including a control unit 110, a first irradiation unit 14, a second irradiation unit 15, and a light receiving unit 16, a first intensity acquisition unit 120, and a second intensity acquisition unit 130. , A processing device including a correction unit 140, a temperature information acquisition unit 150, and a concentration acquisition unit 160.

The strength E2 does not necessarily have to be stronger than the strength E1 as long as the strength is different from the strength E1. The intensity of transmitted light and the amplitude of vibration waves are physical quantities whose squared dimension is proportional to energy. The intensity of the transmitted light and the amplitude of the vibration wave are examples of physical quantities caused by changes in the measurement target. The first strength acquisition unit 120 and the first amplitude acquisition unit 220 are examples of the first acquisition unit. The second strength acquisition unit 130 and the second amplitude acquisition unit 230 are examples of the second acquisition unit. The strength E1 is an example of the first strength. The strength E2 is an example of the second strength. The third irradiation unit 15-2 to the Nth irradiation unit 15- (N-1) are examples of M irradiation units. Note that M is an integer of 1 or more. The shift amount of the absorption spectrum is an example of a change in the absorption spectrum. The change in the absorption spectrum may be not only a change in the shift amount but also a change in the shape of the absorption spectrum.

Although the embodiments of the present invention have been described in detail with reference to the drawings, the specific configuration is not limited to this embodiment, and includes designs and the like within a range that does not deviate from the gist of the present invention.

1, 2, 1a ... Concentration measuring device, 11, 21 ... CPU, 12, 22 ... Memory, 13, 23 ... Auxiliary storage device, 14 ... First irradiation unit, 15 ... Second irradiation unit, 16, 16a ... Light receiving unit , 100, 100a ... Information processing unit, 110, 210 ... Control unit, 120 ... First intensity acquisition unit, 130 ... Second intensity acquisition unit, 140, 240 ... Correction unit, 150, 250 ... Temperature information acquisition unit, 160, 260 ... concentration acquisition unit, 24 ... first modulation unit, 25 ... second modulation unit, 26 ... pressure sensitive unit, 220 ... first amplitude acquisition unit, 230 ... second amplitude acquisition unit

Claims (27)

A first irradiation unit that irradiates a measurement target having a target component and a non-target component with light having a first wavelength,
A second irradiation unit that irradiates the measurement target with light having a second wavelength that is different from the first wavelength.
When the first irradiation unit irradiates the measurement target with light of the first wavelength and the second irradiation unit irradiates the measurement target with light of the second wavelength with a first intensity, the measurement is performed. The first acquisition unit that acquires the physical quantity caused by the change of the target,
The first irradiation unit irradiates the measurement target with light having the first wavelength, and the second irradiation unit irradiates the measurement target with light having the second wavelength at a second intensity different from the first intensity. The second acquisition unit that acquires the physical quantity caused by the change in the measurement target when the light is irradiated to
A temperature information acquisition unit that acquires temperature information that is information on a temperature change of the measurement target based on the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit.
A concentration acquisition unit that acquires the concentration of the non-target component based on the temperature information, the physical quantity acquired by the first acquisition unit, and the physical quantity acquired by the second acquisition unit.
Concentration measuring device. The concentration acquisition unit acquires the concentration by multivariate analysis.
The concentration measuring device according to claim 1. The concentration acquisition unit is a learning model learned in advance, and is a learning model representing the relationship between the physical quantity acquired by the first acquisition unit, the physical quantity acquired by the second acquisition unit, the temperature information, and the concentration. Based on, the concentration is obtained,
The concentration measuring device according to claim 1. The second wavelength is a wavelength at which the absorbance of the target component is smaller than the absorbance of the non-target component.
The concentration measuring device according to claim 1. The second wavelength is a wavelength that changes the absorption spectrum of the non-target component to a predetermined magnitude or more.
The concentration measuring device according to claim 4. The second wavelength is a wavelength at which the absorbance of the non-target component is maximized.
The concentration measuring device according to claim 5. The second wavelength is a wavelength within the range of ± 70 nanometers centered on the wavelength at which the absorbance of the non-target component is maximum.
The concentration measuring device according to claim 5. The first wavelength is a wavelength within the range of ± 70 nanometers centered on the wavelength at which the absorbance of the target component is maximum.
The concentration measuring device according to claim 1. The first wavelength is a wavelength at which the absorbance of the target component is maximized.
The concentration measuring device according to claim 2. Based on the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit, a correction coefficient which is a value representing the influence of the environment on the physical quantity is acquired, and the acquired correction coefficient is used. A correction unit that corrects the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit.
The concentration measuring device according to claim 1, further comprising. The environmental effect is the amount of the non-target component.
The concentration measuring device according to claim 10. The influence of the environment is the absorbance of the non-target component with respect to the first wavelength and the absorbance of the non-target component with respect to the second wavelength.
The concentration measuring device according to claim 10. The influence of the environment is the performance of the light receiving unit that receives the light of the first wavelength.
The concentration measuring device according to claim 10. At least one of the first wavelength light and the second wavelength light is encoded light.
The concentration measuring device according to claim 1. Further provided with M (M is an integer of 1 or more) irradiation units for irradiating a measurement target having a target component and a non-target component with light.
The concentration measuring device according to claim 1. The wavelength of the light emitted by at least one of the M irradiation units is defined as a third wavelength.
The second wavelength and the third wavelength are wavelengths having a predetermined correlation with respect to the shift of the absorption spectrum of the non-target component.
The concentration measuring device according to claim 15. The second wavelength and the third wavelength are wavelengths located at positions where the signs are opposite to each other with the peak wavelength of the absorption spectrum of the non-objective component as the origin.
The concentration measuring device according to claim 16. The second wavelength and the third wavelength are wavelengths located at positions where the signs are opposite to each other with the wavelength of the inflection point of the absorption spectrum of the non-objective component as the origin.
The concentration measuring device according to claim 16. The physical quantity is the intensity of transmitted light, scattered light, or reflected light of the light applied to the measurement target.
The concentration measuring device according to claim 1. The physical quantity is the intensity of transmitted light of the light applied to the measurement target.
The concentration measuring device according to claim 19. The physical quantity is the amplitude of the vibration wave generated in the measurement target by the light applied to the measurement target.
The concentration measuring device according to claim 1. The vibration wave is the amplitude of an elastic wave generated in the measurement target by the light applied to the measurement target.
The concentration measuring device according to claim 21. The vibration wave is the amplitude of the heat wave generated in the measurement target by the light applied to the measurement target.
The concentration measuring device according to claim 21. A piezoelectric material that generates a voltage proportional to the magnitude of the pressure when pressure is applied,
A holder for applying tension to the piezoelectric body to bring the piezoelectric body into close contact with the measurement target is provided.
The first acquisition unit and the second acquisition unit acquire the physical quantity based on the voltage generated by the piezoelectric body.
The concentration measuring device according to claim 21. The temperature information is a shift amount of the absorption spectrum of the non-target component.
The concentration measuring device according to claim 1. A first irradiation unit that irradiates a measurement target having a target component and a non-target component with light having a first wavelength, and a second irradiation unit having a wavelength different from the first wavelength are irradiated to the measurement target. The second irradiation unit and the first irradiation unit irradiate the measurement target with light of the first wavelength, and the second irradiation unit irradiates the measurement target with light of the second wavelength with a first intensity. In this case, the first acquisition unit that acquires the physical quantity due to the change in the measurement target, the first irradiation unit irradiates the measurement target with light of the first wavelength, and the second irradiation unit performs the measurement. When the measurement target is irradiated with light of a second wavelength at a second intensity different from the first intensity, a second acquisition unit that acquires a physical quantity due to a change in the measurement target, and the first acquisition unit. The temperature information acquisition unit that acquires temperature information that is information on the temperature change of the measurement target based on the physical quantity acquired by the unit and the physical quantity acquired by the second acquisition unit, and the temperature information and the first acquisition unit A concentration measurement method performed by a concentration measuring device including a concentration acquisition unit for acquiring the concentration of the non-target component based on the acquired physical amount and the physical amount acquired by the second acquisition unit.
The first irradiation step of irradiating the measurement target with light of the first wavelength,
A second irradiation step of irradiating the measurement target with light of the second wavelength,
When the first irradiation unit irradiates the measurement target with light of the first wavelength and the second irradiation unit irradiates the measurement target with light of the second wavelength with a first intensity, the measurement is performed. The first acquisition step to acquire the physical quantity caused by the change of the object,
The first irradiation unit irradiates the measurement target with light having the first wavelength, and the second irradiation unit irradiates the measurement target with light having the second wavelength at a second intensity different from the first intensity. The second acquisition step of acquiring the physical quantity caused by the change of the measurement target when the light is irradiated to
A temperature information acquisition step of acquiring temperature information which is information on a temperature change of the measurement target based on the physical quantity acquired by the first acquisition unit and the physical quantity acquired by the second acquisition unit.
A concentration acquisition step for acquiring the concentration of the non-target component based on the temperature information, the physical quantity acquired by the first acquisition unit, and the physical quantity acquired by the second acquisition unit.
Concentration measurement method having. A non-temporary recording medium for storing a program for operating a computer as the concentration measuring device according to claim 1.

Images