JP2007236732A - Calibrator, biological component concentration measuring apparatus using it, and its calibration method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a calibrator capable of easily confirming whether or not a biological component concentration measuring apparatus is in a normal state by calibrating the biological component concentration measuring apparatus before measuring infrared light emitted from the ear drum using the biological component concentration measuring apparatus; and also to provide the biological component concentration measuring apparatus using it, and its calibration method. <P>SOLUTION: The calibrator is used for calibrating the biological component concentration measuring apparatus comprising an infrared ray detector for detecting the infrared light radiated from the ear drum present inside an earhole, an insertion probe to be inserted into the earhole for leading the infrared light to the infrared ray detector and a biological component concentration computing part for converting the output of the infrared ray detector to the concentration of biological components. The calibrator is provided with an infrared ray emitter which emits the infrared light and a support part for supporting the infrared ray emitter to be fitted with the insertion probe. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to a calibrator used for calibrating a biological component concentration measuring device that measures a concentration of a biological component, for example, a glucose concentration noninvasively without blood collection or the like, and a biological component concentration measuring device using the same And a calibration method thereof.

Conventionally, as a biological information measuring device, a noninvasive blood glucose meter has been proposed that measures the emitted light from the eardrum and calculates the glucose concentration (see, for example, Patent Documents 1, 2, or 3). For example, Patent Document 1 includes a mirror that is large enough to fit in the ear canal. Through the mirror, the eardrum is irradiated with near-infrared rays or heat rays, and light reflected from the eardrum is detected. A non-invasive blood glucose meter for calculating the value is disclosed. Patent Document 2 includes a probe that is inserted into the ear canal, and detects infrared rays generated from the inner ear and emitted from the eardrum through the probe in a state where the eardrum and the ear canal are cooled. A non-invasive blood glucose meter that obtains a glucose concentration by spectroscopic analysis is disclosed. Further, Patent Document 3 includes a reflecting mirror inserted into the ear canal, detects the emitted light from the eardrum using the reflecting mirror, and obtains the glucose concentration by spectroscopic analysis of the detected emitted light. An invasive blood glucose meter is disclosed.
JP 05-506171 JP-T-2002-513604 JP-T-2001-503999

  However, in the conventional noninvasive blood glucose meter, when measurement is performed in a state where the tip of the mirror or probe inserted into the ear canal is dirty, the component causing the contamination is also measured, and the measurement accuracy is deteriorated.

  Also, when the spectral element and infrared detector provided in the non-invasive blood glucose meter deteriorate, the transmittance and wavelength characteristics of the spectral element change or the sensitivity of the infrared detector decreases. , Measurement accuracy will deteriorate.

  In the conventional non-invasive blood glucose meter, since it is difficult to determine whether or not the state of the apparatus is normal in this way, there is a possibility that the measurement accuracy may be deteriorated by performing the measurement while the apparatus is not normal. .

  In view of the above-mentioned conventional problems, the present invention calibrates the biological component concentration measuring device before measuring the infrared light emitted from the eardrum using the biological component concentration measuring device, thereby It is an object of the present invention to provide a calibrator capable of easily confirming whether or not a measuring device is in a normal state, a biological component concentration measuring device using the same, and a calibration method thereof.

  In order to solve the conventional problem, a calibrator according to the present invention includes an infrared detector that detects infrared light emitted from an eardrum in an ear canal, and an infrared detector that is inserted into the ear canal. A calibrator for use in calibration of a biological component concentration measuring apparatus comprising an insertion probe for leading to an infrared detector and a biological component concentration calculation unit that converts the output of the infrared detector into a biological component concentration, An infrared radiator, and a support portion that supports the infrared radiator and engages with the insertion probe.

  The biological component concentration measuring apparatus of the present invention includes an infrared detector that detects infrared light emitted from the eardrum in the ear canal and an insertion that is inserted into the ear canal and guides the infrared light to the infrared detector. A probe, a biological component concentration calculator that converts the output of the infrared detector into a biological component concentration, and the calibrator attached to the insertion probe.

Moreover, the calibration method of the biological component concentration measuring apparatus of the present invention uses the above calibrator,
(A) measuring the intensity of the infrared light emitted from the infrared emitter of the calibrator attached to the insertion probe;
(B) comparing the intensity of the infrared light measured in the step A with a preset allowable range;
(C) based on the comparison in the step B, determining whether or not the biological component concentration measuring device is normal.

  According to the calibrator of the present invention, the biological component concentration measuring apparatus using the same, or the calibration method thereof, the biological component concentration measurement is performed before the infrared light emitted from the eardrum is measured using the biological component concentration measuring apparatus. By calibrating the apparatus, it is possible to easily confirm whether or not the biological component concentration measuring apparatus is in a normal state.

  The calibrator of the present invention includes an infrared detector that detects infrared light emitted from the eardrum in the ear canal, an insertion probe that is inserted into the ear canal and guides the infrared light to the infrared detector, A calibrator for use in calibration of a biological component concentration measuring device comprising a biological component concentration calculation unit for converting an output of an infrared detector into a biological component concentration, an infrared emitter that emits infrared light, and the infrared ray A support for supporting the radiator and fitting with the insertion probe;

  With this configuration, in the calibrator attached to the insertion probe so that the support portion fits the distal end portion of the insertion probe before measuring the infrared light emitted from the eardrum using the biological component concentration measurement device. It is possible to easily confirm whether or not the biological component concentration measuring device is in a normal state by calibrating the biological component concentration measuring device using infrared light emitted from the infrared radiator.

  The infrared radiator has a function of emitting calibration infrared rays. The infrared radiator is preferably one that can radiate as much heat energy as possible, and preferably has an emissivity of 0.9 or more. As a material of the infrared radiator, for example, a black body tape made by TASCO JAPAN can be used. Moreover, you may form the layer of a black body paint about 20-30 micrometers in thickness by apply | coating the black body spray made from TASCO JAPAN to the surface of a support part.

  The support portion is preferably made of a thermoplastic material that has elasticity and is easy to mold. For example, polycarbonate, polystyrene, polyethylene, polypropylene, polyethylene terephthalate resin, or the like can be used. The support portion functions as a lid that covers the insertion probe when the calibrator is attached to the insertion probe. In this state, it is preferable to have a function of shielding external light from entering the insertion probe from outside the calibrator. The light shielding property can be easily realized by applying a black paint or mixing a black pigment to the support portion. When the calibrator is attached to the insertion probe, the infrared radiation that is provided inside the support that functions as a lid faces the insertion probe so that infrared light is emitted from the infrared radiation toward the insertion probe. Is done.

  The infrared detector is not particularly limited as long as it can detect light having a wavelength in the infrared region. For example, a pyroelectric sensor, a thermopile, a bolometer, an HgCdTe (MCT) detector, a Golay cell, or the like can be used.

  As the biological component concentration calculation unit, for example, a microcomputer such as a CPU (Central Processing Unit) can be used.

  The insertion probe may be any probe that can guide infrared rays. For example, a hollow tube or an optical fiber that transmits infrared rays can be used. When using a hollow tube, it is preferable to have a gold layer on the inner surface of the hollow tube. This gold layer can be formed by performing gold plating on the inner surface of the hollow tube or by depositing gold.

  When using an optical fiber, it is preferable that the material be transparent from visible light to infrared wavelengths in the mid-infrared region. An example of such a material is an AgCl-AgBr solid solution. When using an optical fiber, it is preferable to use a bundle fiber obtained by bundling a plurality of optical fibers and bonding and polishing the end portions of the optical fibers. In this case, since the number of optical fibers is increased, the eardrum can be imaged with a resolution corresponding to the number of optical fibers when the eardrum is imaged by the imaging device.

  The support part preferably further includes a protrusion. With this configuration, after the calibration is completed, the user pulls the protrusion, whereby a tensile stress is applied to the protrusion and the calibrator can be removed from the insertion probe. The protrusion may have a shape of a ridge protruding from the peripheral portion of the support portion that functions as a lid that covers the insertion probe. As the material of the protrusion, the same material as that of the support can be used.

  The support portion further includes a hinge portion, and it is preferable that the hinge portion is deformed by applying a tensile stress to the protrusion portion of the support portion attached to the insertion probe so as to be fitted to the insertion probe. With this configuration, after the calibration is completed, when the user pulls the protrusion, and a tensile stress is applied to the protrusion, the hinge part is deformed, so that the calibrator can be easily detached from the insertion probe. As the material of the hinge part, the same material as that of the support part can be used. The wall thickness of the hinge part is preferably thinner than other parts of the support part.

  The calibrator is preferably stored in a package made of a plastic material or a package in which aluminum is vapor-deposited on the inner surface of the plastic so that the emissivity of the infrared radiator does not change with time.

  The support unit may further include a cover for protecting the insertion probe at a position covering the infrared emitter.

  With this configuration, after the configuration is completed, the tip of the insertion probe is protected by the cover during measurement by leaving the cover attached when removing the calibrator from the insertion probe. Since dust or the like does not enter the insertion probe, accurate measurement can be performed without being disturbed by dust or the like.

  Also, after the measurement is completed, leave the cover attached to the tip of the insertion probe, and immediately before the next measurement, the user removes the used cover from the tip of the insertion probe, and then installs a new calibrator. It is preferable to attach. In this way, since the distal end portion of the insertion probe is always protected by the cover while the biological component concentration measuring apparatus is stored, dust or the like is not mixed into the insertion probe even during storage.

  The support unit may further include an optical path changing element for changing the optical path of the infrared light at a position covering the infrared radiator.

  With this configuration, the optical path changing element is attached to the tip of the insertion probe at the time of measurement by leaving the optical path changing element attached when removing the calibrator from the insertion probe after the configuration is completed. Infrared light emitted from the eardrum is inserted even when the ear canal is bent halfway by bending the infrared light emitted from the eardrum at an optical path changing element attached to the tip of the insertion probe Can be transmitted within.

  As a material for the optical path changing element, a material having elasticity and transparent in the infrared region is preferable. For example, polycarbonate, polypropylene, polyethylene or the like can be used.

  The optical path changing element preferably has a projection having a triangular or trapezoidal cross section, and a reflecting mirror is preferably provided to reflect infrared light on one side of the projection. The reflecting mirror can be formed by coating a material such as gold or aluminum after the optical path changing element is formed by resin formation.

  The biological component concentration measuring apparatus of the present invention includes an infrared detector that detects infrared light emitted from the eardrum in the ear canal and an insertion that is inserted into the ear canal and guides the infrared light to the infrared detector. A probe, a biological component concentration calculator that converts the output of the infrared detector into a biological component concentration, and the calibrator attached to the insertion probe.

Moreover, the calibration method of the biological component concentration measuring apparatus of the present invention uses the above calibrator,
(A) measuring the intensity of the infrared light emitted from the infrared emitter of the calibrator attached to the insertion probe;
(B) comparing the intensity of the infrared light measured in the step A with a preset allowable range;
(C) based on the comparison in the step B, determining whether or not the biological component concentration measuring device is normal.

  Thereby, as a result of the comparison in the process B, when the intensity of the infrared light measured in the process A is within the allowable range, it can be determined that the biological component concentration measuring apparatus is normal. On the other hand, when the intensity of the infrared light measured in the process A exceeds the allowable range, it can be determined that the biological component concentration measuring apparatus is not normal but abnormal.

  The biological component concentration measuring apparatus according to the present invention includes a light source that emits light for illuminating the inside of the ear canal, an image sensor that images the light emitted from the light source and reflected in the ear canal, and the image sensor. From the obtained imaging information, an imaging information detection unit that detects imaging information of the eardrum, and infrared light emitted from the eardrum is selected based on the imaging information of the eardrum detected by the imaging information detection unit And an optical path control element that controls the optical path so as to transmit light.

  With this configuration, infrared light emitted from the eardrum passes through the optical path control element and reaches the infrared detector, and infrared light emitted from the ear canal is blocked by the optical path control element and does not reach the infrared detector. Can be removed, and highly accurate measurement can be performed.

  As the light source, for example, a visible light laser such as a red laser, a white LED, or the like can be used. Among these, a white LED is preferable because it generates less heat when it emits light than a halogen lamp, and thus has little influence on the temperature of the eardrum or ear canal.

  As the image pickup element, for example, an image element such as a CMOS or a CCD can be used.

  As the optical path control element, a liquid crystal shutter, a mechanical shutter, or the like can be used. As the liquid crystal shutter, for example, it is preferable that the liquid crystal shutter includes a TFT, and can control infrared light in a specific region or can be shielded by controlling using a TFT (Thin Film Transistor).

  As the mechanical shutter, for example, a digital mirror device (hereinafter abbreviated as DMD) in which micro mirror surfaces (micro mirrors) are arranged in a plane can be used. The DMD can be manufactured using a known MEMS (Micro Electro Mechanical System) technique. Each micromirror can be controlled to two states, ON and OFF, by driving an electrode provided in the lower part of the mirror surface. When the micromirror is ON, the infrared light emitted from the eardrum is reflected and projected toward the infrared detector. When the micromirror is OFF, the infrared light is reflected toward the absorber provided inside the DMD. However, it is not projected toward the infrared detector. Therefore, by individually driving each micromirror, it is possible to control the projection of infrared light for each minute region.

  As the imaging information detection unit, for example, a microcomputer such as a CPU (Central Processing Unit) can be used.

  As a method for the imaging information detection unit to detect imaging information of the eardrum from imaging information obtained by the imaging device, image processing of the imaging information obtained by the imaging device is performed, and a color difference between the eardrum and the ear canal is calculated. A method for recognizing an image of the eardrum by using it is mentioned.

  The biological component concentration measuring apparatus of the present invention may further include a light splitting element that transmits one of the light reflected in the ear canal and the infrared light emitted from the eardrum and reflects the other. .

  Here, the spectroscopic element may be arranged between the infrared detector and the light splitting element.

In the present invention, as the light splitting element, for example, a half mirror having a function of transmitting one of visible light and infrared light and reflecting the other can be used. In the case of reflecting visible light and transmitting infrared light, for example, ZnSe, CaF ₂ , Si, Ge, or the like can be used as the material of the half mirror. Moreover, you may use what provided the layer which consists of aluminum and gold | metal | money of several nanometers thickness on resin transparent with respect to infrared rays. Examples of the resin that is transparent to infrared rays include polycarbonate.

  Any spectroscopic element may be used as long as it can divide infrared rays by wavelength. For example, an optical filter that transmits infrared rays in a specific wavelength region, a Michelson interferometer, a diffraction grating, or the like can be used.

  The imaging information detection unit calculates a ratio of the imaging information of the eardrum in the imaging information obtained by the imaging element, and the biological component concentration calculation unit uses the ratio to output the output of the infrared detector. It is preferable to correct. The intensity of infrared light emitted from a living body depends on the area of the portion where infrared light is emitted. Therefore, even when the area of the eardrum imaged by the image sensor varies, this correction reduces the variation in the measurement result and enables more accurate measurement.

  The biological component concentration measuring apparatus of the present invention preferably further includes a warning output unit that outputs a warning when the ratio is equal to or less than a threshold value. With this configuration, it is possible to notify the user that the position of the biological component concentration measuring device is inappropriate.

  Here, examples of the warning output unit include a display that displays a warning, a speaker that outputs a warning by voice, and a buzzer that generates a warning sound.

  The biological component concentration measuring apparatus of the present invention may further include an audio output unit that outputs audio when imaging information of the eardrum is detected by the imaging element. Here, it is preferable that the sound output unit changes the frequency or intensity of the sound in accordance with the size of the area of the eardrum imaged by the image sensor.

  The biological component concentration measuring apparatus of the present invention includes a storage unit that stores correlation data indicating the correlation between the output signal of the infrared detector and the biological component concentration, and a display that displays the concentration of the biological component converted by the biological component concentration calculation unit. And a power source for supplying power for operating the biological component concentration measuring apparatus.

  The biological component concentration calculation unit may convert the output signal of the infrared detector into the concentration of the biological component by reading the correlation data from the storage unit and referring to the correlation data.

  The correlation data indicating the correlation between the output signal of the infrared detector and the biological component concentration is obtained by measuring the output signal of the infrared detector for a patient having a known biological component concentration (for example, blood glucose level), for example. It can be obtained by analyzing the correlation between the output signal of the detector and the concentration of the biological component.

  In the present invention, for example, a memory such as a RAM or a ROM can be used as the storage unit.

  As the display unit, for example, a display such as a liquid crystal can be used.

  As the power source, for example, a battery or the like can be used.

  Examples of the biological component concentration measured by the biological component concentration measuring apparatus of the present invention include glucose concentration (blood glucose level), hemoglobin concentration, cholesterol concentration, and neutral fat concentration.

  By measuring infrared light emitted from a living body, biological information, for example, blood glucose level can be measured. Radiant energy W of infrared radiation from a living body is expressed by the following mathematical formula.

here,
W: radiant energy of infrared radiation from a living body,
ε (λ): emissivity of a living body at wavelength λ,
W ₀ (λ, T): wavelength λ, blackbody radiation intensity density at temperature T,
h: Planck's constant (h = 6.625 × 10 ⁻³⁴ (W · S ² )),
c: speed of light (c = 2.998 × 10 ¹⁰ (cm / s)),
λ ₁ , λ ₂ : wavelength of infrared radiation from the living body (μm),
T: temperature of living body (K),
S: Detection area (cm ² )
k: Boltzmann constant,
It is.

  As can be seen from (Equation 1), when the detection area S is constant, the radiation energy W of the infrared radiation from the living body depends on the emissivity ε (λ) of the living body at the wavelength λ. From Kirchhoff's law of radiation, the emissivity and absorptivity at the same temperature and wavelength are the same.

here,
α (λ): Absorption rate of living body at wavelength λ,
It is.

  Therefore, it can be seen that the absorptance should be considered when considering the emissivity. From the law of conservation of energy, the following relationship holds for the absorptance, transmittance, and reflectance.

here,
r (λ): Biological reflectance at wavelength λ t (λ): Biological transmittance at wavelength λ Therefore, emissivity is calculated using transmittance and reflectance.

It is expressed.

  The transmittance is represented by the ratio between the incident light amount and the transmitted light amount when it passes through the measurement object. The amount of incident light and the amount of light transmitted through the object to be measured are expressed by the Lambert-Beer law.

here,
I _t: the amount of transmitted light,
I ₀ : incident light quantity,
d: thickness of the living body,
k (λ): extinction coefficient of living body at wavelength λ,
It is. The extinction coefficient of a living body is a coefficient representing light absorption by the living body.

  Therefore, the transmittance is

It is expressed.

  Next, the reflectance will be described. As the reflectance, it is necessary to calculate an average reflectance in all directions, but here, for simplicity, the reflectance with respect to normal incidence is considered. The reflectivity for normal incidence is 1 for the refractive index of air.

It is expressed.

here,
n (λ): refractive index of the living body at wavelength λ,
It is.

  From the above, the emissivity is

It is expressed.

  When the concentration of the component in the living body changes, the refractive index and extinction coefficient of the living body change. The reflectance is usually as small as about 0.03 in the infrared region, and, as can be seen from (Equation 8), does not depend much on the refractive index and the extinction coefficient. Therefore, even if the refractive index and extinction coefficient change due to changes in the concentration of components in the living body, the change in reflectance is small.

  On the other hand, the transmittance greatly depends on the extinction coefficient, as can be seen from (Equation 7). Therefore, the transmittance changes when the extinction coefficient of the living body, that is, the degree of light absorption by the living body, changes due to the change in the concentration of the components in the living body.

  From the above, it can be seen that the radiant energy of infrared radiation from a living body depends on the concentration of components in the living body. Therefore, the concentration of the component in the living body can be obtained from the radiant energy intensity of the infrared radiation from the living body.

  Further, as can be seen from (Equation 7), the transmittance depends on the thickness of the living body. The thinner the living body is, the greater the degree of change in the transmittance with respect to the change in the extinction coefficient of the living body, making it easier to detect changes in the concentration of components in the living body. Since the eardrum is as thin as about 60 to 100 μm, it is suitable for measuring the concentration of components in the living body using infrared radiation.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.

(Embodiment 1)
FIG. 1 is a perspective view showing the external appearance of the calibrator 105 and the biological component concentration measuring apparatus 100 according to the first embodiment.

  The biological component concentration measuring apparatus 100 includes a main body 102 and an insertion probe 104 provided on a side surface of the main body 102, and the calibrator 105 is used in a state of being attached to the distal end of the insertion probe 104. The main body 102 has a display 114 for displaying the measurement result of the concentration of the biological component, a power switch 101 for turning on / off the biological component concentration measuring apparatus 100, a measurement start switch 103 for starting the measurement, In addition, a calibration switch 107 for starting calibration of the biological component concentration measuring apparatus 100 is provided.

  Here, the display 114 corresponds to a display unit in the present invention.

  Next, the internal structure of the main body of the biological component concentration measuring apparatus 100 will be described with reference to FIGS. FIG. 2 is a diagram showing a configuration of the biological component concentration measuring apparatus 100 according to the first embodiment, and FIG. 3 is a perspective view showing the optical filter wheel 106 in the biological component concentration measuring apparatus 100 according to the first embodiment. is there.

  Inside the main body of the biological component concentration measuring apparatus 100 are a chopper 118, a liquid crystal shutter 120, an optical filter wheel 106, an infrared detector 108, a preamplifier 130, a band filter 132, a synchronous demodulator 134, a low pass filter 136, and analog / digital. Converter (hereinafter abbreviated as A / D converter) 138, microcomputer 110, memory 112, display 114, power supply 116, light source 140, first half mirror 142, second half mirror 144, condenser lens 146, imaging An element 148, an actuator 150, a lens frame 152, a position sensor 154, a timer 156, and a buzzer 158 are provided.

  Here, the microcomputer 110 corresponds to an imaging information detection unit and a biological component concentration calculation unit in the present invention.

  The power source 116 supplies AC or DC power to the microcomputer 110. A battery is preferably used as the power source 116.

  The chopper 118 radiates from the eardrum 202, is guided into the main body 102 by the insertion probe 104, and then chops the infrared light transmitted through the second half mirror 144 to convert the infrared light into a high-frequency infrared signal. Has a function to convert. The operation of the chopper 118 is controlled based on a control signal from the microcomputer 110.

  The infrared light chopped by the chopper 118 reaches the optical filter wheel 106.

  As shown in FIG. 3, the optical filter wheel 106 has a first optical filter 122 and a second optical filter 124 fitted in a ring 123. In the example shown in FIG. 3, the first optical filter 122 and the second optical filter 124 that are both semicircular are fitted into the ring 123 to form a disk-shaped member. A shaft 125 is provided at the center. By rotating the shaft 125 as shown by the arrow in FIG. 3, the optical filter through which the infrared light chopped by the chopper 118 passes is switched between the first optical filter 122 and the second optical filter 124. be able to. The rotation of the shaft 125 is controlled by a control signal from the microcomputer 110. The rotation of the shaft 125 is preferably synchronized with the rotation of the chopper 118 and controlled to rotate the shaft 125 180 degrees while the chopper 118 is closed. In this way, when the chopper 118 is opened next, the optical filter through which the infrared light chopped by the chopper 118 passes can be switched to another optical filter. The optical filter wheel 106 corresponds to the spectroscopic element in the present invention.

As a method for producing the optical filter, a known technique can be used without any particular limitation. For example, a vacuum deposition method can be used. The optical filter can be manufactured by stacking ZnS, MgF ₂ , PbTe, or the like on the substrate by vacuum deposition using Si or Ge as the substrate.

  Here, an optical filter having a desired wavelength characteristic is manufactured by controlling the light interference in the laminated thin film by adjusting the film thickness of each layer laminated on the substrate, the order of lamination, the number of laminations, and the like. can do.

  The infrared light transmitted through the first optical filter 122 or the second optical filter 124 reaches the infrared detector 108 including the detection region 126. The infrared light reaching the infrared detector 108 enters the detection region 126 and is converted into an electrical signal corresponding to the intensity of the incident infrared light.

  The electrical signal output from the infrared detector 108 is amplified by the preamplifier 130. From the amplified electrical signal, signals other than the frequency band having the chopping frequency as the center frequency are removed by the band filter 132. Thereby, noise resulting from statistical fluctuations such as thermal noise can be minimized.

  The electric signal filtered by the band filter 132 is demodulated into a DC signal by synchronizing and integrating the chopping frequency of the chopper 118 and the electric signal filtered by the band filter 132 by the synchronous demodulator 134.

  The low-frequency band signal is removed from the electrical signal demodulated by the synchronous demodulator 134 by the low-pass filter 136. Thereby, noise can be further removed.

  The electrical signal filtered by the low-pass filter 136 is converted into a digital signal by the A / D converter 138 and then input to the microcomputer 110. Here, the electrical signal from the infrared detector 108 corresponding to each optical filter is an electrical signal corresponding to the infrared light transmitted through which optical filter by using the control signal of the shaft 125 as a trigger. Can be identified. The period from when the microcomputer outputs a control signal for the shaft 125 to when the next shaft control signal is output is an electrical signal corresponding to the same optical filter. Since the noise is further reduced by calculating the average value after integrating the electrical signals corresponding to the respective optical filters on the memory 112, it is preferable to integrate the measurements.

  In the memory 112, the electrical signal corresponding to the intensity of the infrared light transmitted through the first optical filter 122, the electrical signal corresponding to the intensity of the infrared light transmitted through the second optical filter 124, and the concentration of the biological component are stored. Correlation data indicating the correlation is stored. The microcomputer 110 reads the correlation data from the memory 112, refers to the correlation data, and converts the digital signal per unit time calculated from the digital signal stored in the memory 112 into the concentration of the biological component. The memory 112 corresponds to the storage unit of the present invention.

  The concentration of the biological component converted in the microcomputer 110 is output to the display 114 and displayed.

  The first optical filter 122 has, for example, a spectral characteristic that transmits infrared light in a wavelength band (hereinafter, abbreviated as a measurement wavelength band) including a wavelength that is absorbed by a biological component to be measured. On the other hand, the second optical filter 124 has a spectral characteristic different from that of the first optical filter 122. The second optical filter 124 is, for example, a wavelength band (hereinafter referred to as a reference wavelength) that includes a wavelength that is not absorbed by a biological component that is a measurement target and that is absorbed by another biological component that interferes with the measurement of the target component. It has a spectral characteristic that transmits infrared light (abbreviated as a band). Here, as such other biological components, those having a large amount of components in the living body other than the biological component to be measured may be selected.

  For example, glucose shows an infrared absorption spectrum having an absorption peak near 9.6 μm. Therefore, when the biological component to be measured is glucose, it is preferable that the first optical filter 122 has a spectral characteristic that transmits infrared light in a wavelength band including 9.6 μm.

  On the other hand, proteins that are abundant in the living body absorb infrared light around 8.5 micrometers, and glucose does not absorb infrared light around 8.5 μm. Therefore, it is preferable that the second optical filter 124 has a spectral characteristic that transmits infrared light in a wavelength band including 8.5 μm.

  The electrical signal corresponding to the intensity of the infrared light transmitted through the first optical filter 122 and the electrical signal corresponding to the intensity of the infrared light transmitted through the second optical filter 324 and the biological component stored in the memory 112 Correlation data indicating the correlation with the concentration of can be obtained, for example, by the following procedure.

  First, infrared light emitted from the eardrum is measured for a patient having a known biological component concentration (for example, blood glucose level). At this time, an electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the first optical filter 122 and an electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the second optical filter 124 Ask for. By performing this measurement for a plurality of patients having different biological component concentrations, the electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the first optical filter 122 and the second optical filter 124 are transmitted. It is possible to obtain a data set including an electrical signal corresponding to the intensity of infrared light in the wavelength band and a corresponding biological component concentration.

  Next, the data set thus obtained is analyzed to obtain correlation data. For example, an electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the first optical filter 122, and an electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the second optical filter 124; Wavelengths transmitted by the first optical filter 122 by performing multivariate analysis using a multiple regression analysis method such as a PLS (Partial Least Squares Regression) method, a neural network method, or the like with respect to biological component concentrations corresponding to them. A function indicating the correlation between the electrical signal corresponding to the intensity of infrared light in the band and the electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the second optical filter 124 and the corresponding biological component concentration Can be requested.

  The first optical filter 122 has spectral characteristics that allow infrared light in the measurement wavelength band to pass therethrough, and the second optical filter 124 has spectral characteristics that allow infrared light in the reference wavelength band to pass therethrough. , The electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the first optical filter 122 and the electrical signal corresponding to the intensity of infrared light in the wavelength band transmitted by the first optical filter 324 And correlation data indicating the correlation between the difference and the corresponding biological component concentration may be obtained. For example, it can be obtained by performing a linear regression analysis such as a least square method.

  Next, a configuration for imaging the eardrum 202 will be described.

  The light source 140 emits visible light for illuminating the eardrum 202. Visible light emitted from the light source 140 and reflected by the first half mirror 142 is reflected by the second half mirror 144 and then guided through the insertion probe 104 into the ear canal 204 to illuminate the eardrum 202. .

  As the light source 140, for example, a visible light laser such as a red laser, a white LED, or the like can be used. Among these, a white LED is preferable because it generates less heat when it emits light than a halogen lamp, and thus has little influence on the temperature of the eardrum 202 and the ear canal 204.

  The first half mirror 142 has a function of reflecting part of visible light and transmitting the rest.

The second half mirror 144 reflects visible light and transmits infrared light. The material of the second half mirror 144 is preferably a material that does not absorb infrared light, transmits it, and reflects visible light. As a material of the second half mirror 144, for example, ZnSe, CaF ₂ , Si, Ge, or the like can be used. Here, the second half mirror 144 corresponds to the light splitting element in the present invention.

  On the other hand, visible light that has entered the insertion probe 104 from the eardrum 202 through the ear canal 204 is reflected by the second half mirror 144, and part of the visible light passes through the first half mirror 142. The visible light that has passed through the first half mirror 142 is collected by the condenser lens 146 held by the lens frame 152 and reaches the image sensor 148.

  As the image sensor 148, for example, an image element such as a CMOS or a CCD is used.

  The biological component concentration measuring apparatus 100 detects the distance from the image sensor 148 to the eardrum 202, drives the condenser lens 146 held by the lens frame 152, and correctly forms an optical image on the image sensor 148. Provide mechanism.

  The actuator 150 is driven by a control signal from the microcomputer 110, and can move the condenser lens 146 in the direction of the optical axis (the direction of the arrow in FIG. 2). At this time, the position sensor 154 detects the position of the condenser lens 146 and outputs it to the microcomputer 110.

  On the other hand, the microcomputer 110 extracts a high-frequency component of a signal from a pixel included in a focusing area near the center of the image sensor 148 using a bandpass filter, and contrasts the extracted component from the magnitude of the extracted component. Detect the amount. The microcomputer 110 controls the actuator 150 so that the condenser lens 146 moves to a position where the contrast amount is maximized.

  In this way, even if the distance to the eardrum 202 changes, an optical image of the eardrum 202 can be correctly formed on the image sensor 148. In this mechanism, the distance to the eardrum 202 is not directly measured, but the distance to the eardrum 202 is indirectly measured from the positional information of the condenser lens 146.

  As the actuator 150 and the position sensor 154, those similar to those used in an autofocus device mounted on a known video camera or digital still camera can be used. For example, the actuator 150 can be composed of a coil provided on the lens frame 152, a yoke fixed to the main body 102 side, and a driving magnet attached to the yoke. When the lens frame 152 is supported by two guide poles so as to be movable in the optical axis direction, and a current is supplied to a coil provided in the lens frame 152, a magnetic circuit formed by a yoke and a driving magnet. A magnetic driving force in the optical axis direction is generated with respect to the coil inside, and the lens frame 152 moves in the optical axis direction. The positive / negative direction of the driving force can be controlled by the direction of the current supplied to the coil.

  The position sensor 154 includes, for example, a sensor magnet that is magnetized at a constant pitch and attached to the lens frame 152, and a magnetoresistive sensor (hereinafter abbreviated as an MR sensor) fixed to the main body 102 side. Can do. The position of the condenser lens 146 can be detected by detecting the position of the sensor magnet attached to the lens frame 152 by the MR sensor fixed on the main body 102 side.

  Next, a method for recognizing the position of the eardrum 202 from an image photographed by the image sensor 148 will be described.

  FIG. 4 is an image diagram showing an image when the inside of the ear canal 200 is observed using the image sensor 148. Although there are individual differences in the shape of the ear canal, it is often bent. FIG. 4 shows an example of imaging the eardrum of a person whose outer ear canal is bent. The left side of the image is the eardrum 202, and the right ear is the ear canal 204. The position and size at which the eardrum 202 is visible vary depending on the individual, but also varies depending on the insertion position of the insertion probe 104.

  The ear canal color is skin color, and the eardrum color is white or colorless and transparent. By recognizing the color difference between the ear canal and the eardrum by the imaging information detection unit, the two can be distinguished and recognized. The image information obtained by the image sensor 148 is subjected to image processing in the microcomputer 110 to extract the region of the eardrum 202 from the image information. As the image processing, for example, the following region extraction technique using threshold processing and labeling processing can be used.

  First, threshold processing is performed on image information. Each pixel of the image has an RGB value, and the average value of the RGB values is the brightness of each pixel. A constant reference value (threshold value) is set for the brightness of the pixel, and the process of converting the brightness of each pixel into two values of black and white by the threshold value is performed. For example, if the brightness of the pixel is equal to or higher than the set threshold, white is set for the pixel, and black is set for the pixel in other cases. Since the pixel of the portion corresponding to the eardrum 202 is brighter than the pixel of the portion corresponding to the ear canal 204, the threshold value is set between the brightness of the pixel corresponding to the eardrum and the brightness of the pixel corresponding to the ear canal. Then, the pixel corresponding to the eardrum 202 is set to white and the pixel corresponding to the ear canal 204 is set to black by the above processing.

  Next, a labeling process is performed on the image information subjected to the above threshold process. For example, all pixels in the threshold-processed image information are scanned, and the same label is added as an attribute to the pixels set to white.

  Through the above processing, the region corresponding to the pixel to which the label is added can be recognized as the eardrum 202. The ratio of the region of the eardrum 202 in the captured image can be obtained by calculating the ratio of the number of pixels with labels to the total number of pixels by the microcomputer 110.

  The liquid crystal shutter 120 has a structure in which a plurality of liquid crystal cells are arranged in a matrix, and each liquid crystal cell is individually divided into a state where light is transmitted and a state where light is blocked by a voltage applied to each liquid crystal cell. Can be controlled. When the microcomputer 110 recognizes an image corresponding to the eardrum 202 from the image information captured by the image sensor 148 by the image processing described above, the microcomputer 110 controls the voltage applied to each liquid crystal cell of the liquid crystal shutter 120 to The liquid crystal cell in which the infrared light is incident is set in a state in which the light is transmitted, and the liquid crystal cell in which the infrared light from other than the eardrum 202 is incident is set in a state in which the light is blocked.

  Thereby, the infrared light emitted from the eardrum 202 can be selectively incident on the infrared detector 108. Here, the liquid crystal shutter 120 corresponds to an optical path control element in the present invention.

  Next, the configuration of the calibrator 105 used when calibrating the biological component concentration measuring apparatus 100 will be described with reference to FIG. FIG. 5 is a diagram showing a configuration of the calibrator 105 according to the present embodiment. FIG. 5 (a) is a front view of the calibrator 105, FIG. 5 (b) is a cross-sectional view, and FIG. FIG.

  The calibrator 105 includes an infrared radiator 501 and a support portion 502 that supports it.

  The infrared radiator 501 has a function of emitting calibration infrared rays. The infrared radiator 501 is preferably one that can radiate as much heat energy as possible, and preferably has an emissivity of 0.9 or more. As the infrared radiator 501, for example, a black body tape made by TASCO JAPAN can be used. Moreover, you may form the layer of a black body paint about 20-30 micrometers in thickness by apply | coating the black body spray made from TASCO JAPAN to the surface of a support part.

  The infrared radiator 501 can be produced by molding the above material into a disk shape.

  The support portion 502 has a function of supporting the infrared radiator 501 so that at least a part of the infrared radiator 501 is exposed. The support portion 502 has a disk shape with a circular recess, holds the infrared emitter 501 in the recess, and has a shape that fits the insertion probe 104 in the recess. The support portion 502 supports the infrared emitter 501 so that the exposed portion of the infrared emitter 501 faces the tip of the insert probe 104 when the support portion 502 is attached to the insert probe 104, and is inserted from outside the calibrator 105. The probe 104 has a function of shielding external light from entering.

  The support portion 502 is preferably made of a thermoplastic material that has elasticity and is easy to mold. For example, polycarbonate, polystyrene, polyethylene, polypropylene, polyethylene terephthalate resin, or the like can be used.

  The support portion 502 can be manufactured by resin molding using a mold, for example.

  The support 502 having a disc shape is provided with a protrusion 503 protruding in the diameter direction from the peripheral edge thereof. After the calibration is completed, the calibrator 105 can be detached from the insertion probe 104 by pulling the protrusion 503 by the user.

  Further, the support portion 502 is provided with a hinge portion 504. The hinge portion 504 is thinner than the other portions of the support portion 502 so as to be deformed when the user pulls the projection portion 502 after the calibration is completed.

  The calibrator 105 can be manufactured by attaching one surface of the disk-shaped infrared radiator 501 and the bottom surface of the concave portion of the support portion 502. The calibrator 105 is preferably stored in a package made of a plastic material, a package in which aluminum is vapor-deposited on the inner surface of the plastic material, or the like so that the emissivity of the infrared radiator 501 does not change over time.

  Next, a calibration method and operation of the biological component concentration measuring apparatus 100 according to the present embodiment will be described with reference to FIGS. 6 to 9 are cross-sectional views of the insertion probe 104 and the calibrator 105.

  First, the user removes the calibrator 105 from the package, and inserts the calibrator 105 into the insertion probe 104 so that the infrared radiator 501 is exposed toward the tip of the insertion probe 104 as shown in FIG. The insertion probe 104 is provided with a stepped portion 601 so as to be fitted to the peripheral portion of the support portion 502 provided in the calibrator 105, and by tightening the insertion probe 104 using the elastic force of the support portion 502. As shown in FIG. 7, the calibrator 105 is held at the tip of the insertion probe 104.

  First, when the user presses the power switch 101 of the biological component concentration measuring apparatus 100, the power supply in the main body 102 is turned on, and the biological component concentration measuring apparatus 100 is in a measurement preparation state.

  Subsequently, when the user presses the calibration switch 104, calibration of the biological component concentration measuring apparatus 100 is started.

  First, in the state where the light source 140 is OFF, the imaging device 148 is used to image the infrared radiator 501 installed in the calibrator 105. At this time, if the support portion 502 provided in the calibrator 105 is not sufficiently fitted into the insertion probe 104, external light is incident on the insertion probe 104, so that the calibration switch 104 is not pushed. The luminance signal from the image sensor 148 changes. When the microcomputer 110 detects a change in the luminance signal from the image sensor 148, the microcomputer 110 determines that external light has entered the insertion probe 104 and displays an error message on the display unit 114. When an error is displayed, the user can recalibrate the biological component concentration measurement apparatus 100 by pressing the calibration switch 104 after reinserting the calibrator 105.

  Next, the microcomputer 110 controls the chopper 118 in the open state, and then rotates the optical filter wheel 106 to measure the output value from the A / D converter 138. The memory 112 includes an allowable range of electrical signals corresponding to the intensity of infrared light emitted from the infrared radiator 501 and transmitted through the first optical filter 122 (hereinafter referred to as a first allowable range) and an infrared radiator. The permissible range of an electrical signal corresponding to the intensity of infrared light emitted from 501 and transmitted through the second optical filter 124 (hereinafter referred to as a second permissible range) is stored. The microcomputer 110 reads the first allowable range and the second allowable range from the memory 112 and compares them with the measured output value from the A / D converter 138. As a result of comparison, if the output value from the A / D converter 138 exceeds the first allowable range and the second allowable range, it is determined that the biological component concentration measuring apparatus 100 is not normal, and the subsequent measurement Is stopped and an error message is displayed on the display unit 114. As a result of comparison, if the output value from the A / D converter 138 is within the first allowable range and the second allowable range, it is determined that the biological component concentration measuring apparatus 100 is normal, and the calibration is completed. A message to that effect is displayed on the display unit 114.

  Next, the user confirms that a message indicating that the calibration has been completed is displayed on the display unit 114, and pulls the projection 503 as shown in FIG. As shown in FIG. 9, the distal end portion of the insertion probe 104 is exposed.

  Next, the user holds the main body 102 and inserts the insertion probe 104 into the ear hole 200. Since the insertion probe 104 is a conical hollow tube whose diameter increases from the distal end portion of the insertion probe 104 toward the connection portion with the main body 102, the outer diameter of the insertion probe 104 is equal to the inner diameter of the ear hole 200. The insertion probe 104 is not inserted beyond a certain position.

  Next, when the user presses the measurement start switch 103 of the biological component concentration measuring apparatus 100 while holding the biological component concentration measuring apparatus 100 at a position where the outer diameter of the insertion probe 104 is equal to the inner diameter of the ear hole 200, the main body The light source 140 in 102 is turned on, and imaging by the imaging element 148 is started.

  Next, the step of recognizing the position of the eardrum 202 from the image photographed by the image sensor 148 is performed by the above method. As a result of the image recognition, if the microcomputer 110 determines that there is no image corresponding to the eardrum 202 in the image taken by the image sensor 148, a message indicating that the insertion direction of the insertion probe 104 is deviated from the eardrum 202. Is displayed on the display 114, the buzzer 158 is sounded, or the sound is output from a speaker (not shown) to notify the user of an error. Here, when the ratio of the eardrum region in the captured image calculated by the microcomputer 110 is equal to or less than the threshold, the user may be notified of an error. When an error indicating that the position of the eardrum 202 cannot be recognized is notified, the user may adjust the insertion direction of the insertion probe 104 by moving the biological component concentration measuring apparatus 100.

  Here, the display 114, the buzzer 158, and the speaker each correspond to a warning output unit in the present invention.

  When the microcomputer 110 determines that the position of the eardrum 202 has been recognized in the image captured by the image sensor 148 as a result of the image recognition, a message indicating that the position of the eardrum 202 has been recognized is displayed. The information is displayed on the screen 114, the buzzer 158 is sounded, or the sound is output from a speaker (not shown) to notify the user. When the position of the eardrum 202 is recognized, measurement of infrared rays emitted from the eardrum 202 is automatically started. By notifying the user that the position of the eardrum 202 has been recognized, the user can grasp that the measurement has been started. Can be recognized as good.

  Here, the speaker corresponds to an audio output unit in the present invention.

  When the microcomputer 110 determines that the position of the eardrum 202 has been recognized in the image captured by the image sensor 148, the voltage applied to each liquid crystal cell of the liquid crystal shutter 120 is controlled to detect red from the eardrum 202. The liquid crystal cell in which external light is incident is set in a state where light is transmitted, and the liquid crystal cell in which infrared light from other than the eardrum 202 is incident is set in a state where light is blocked. Further, when the microcomputer 110 starts the operation of the chopper 118, measurement of infrared light emitted from the eardrum 202 is started.

  Even after the measurement of infrared light is started, the process for recognizing the position of the eardrum in the image photographed by the image sensor 148 is continued. If the user removes the insertion probe 104 from the ear canal 200 or moves the direction of the insertion probe 104 greatly during measurement, the microcomputer 110 captures an image captured by the image sensor 148. When it is determined that there is no image corresponding to the eardrum 202, an erroneous operation of the user is detected. Along with this detection, the microcomputer 110 displays a message on the display 114 that the insertion direction of the insertion probe 104 is deviated from the eardrum 202, sounds a buzzer 158, and outputs sound from a speaker (not shown). To notify the user of an error. Further, the microcomputer 110 automatically stops the measurement by controlling the chopper 118 to block infrared light reaching the optical filter wheel 106. Here, when the ratio of the eardrum region in the captured image calculated by the microcomputer 110 is equal to or less than the threshold, the user may be notified of an error.

  When an error indicating that the position of the eardrum 202 cannot be recognized is notified, the user moves the biological component concentration measuring apparatus 100 to reinsert the insertion probe 104 into the ear canal 200 or change the insertion direction of the insertion probe 104. After the adjustment, the measurement is started again by pressing the measurement start switch 103.

  When the microcomputer 110 determines that a certain time has elapsed from the start of measurement based on the time signal from the timer 156, the microcomputer 110 controls the chopper 118 to block infrared light reaching the optical filter wheel 106. As a result, the measurement automatically ends. At this time, the microcomputer 110 controls the display 114 and the buzzer 158 to display a message indicating that the measurement is completed on the display 114, to sound the buzzer 158, and to output the sound from a speaker (not shown). To notify the user that the measurement is completed. As a result, the user can confirm that the measurement has been completed, so the insertion probe 104 is taken out of the ear canal 200.

  The electric signal output from the A / D converter 138 is corrected by the microcomputer 110 using the proportion of the eardrum region in the captured image obtained by the above method. The microcomputer 110 transmits an electrical signal corresponding to the intensity of the infrared light transmitted through the first optical filter 122 and an electrical signal corresponding to the intensity of the infrared light transmitted through the second optical filter 124 from the memory 112 and the living body. Correlation data indicating the correlation with the component concentration is read, and the corrected electrical signal is converted into the concentration of the biological component with reference to the correlation data. The obtained concentration of the biological component is displayed on the display 114.

  The method of correcting the electrical signal based on the proportion of the eardrum region in the captured image can be selected according to the content of the electrical signal in the correlation data stored in the memory 112. For example, if the electrical signal in the correlation data stored in the memory 112 is a signal per unit area, the measured electrical signal per unit area is calculated using the ratio of the tympanic region in the captured image. What is necessary is just to correct | amend to a signal. In this way, the measured signal can be corrected by the area of the eardrum from which the measured infrared light has been emitted.

  As described above, according to the biological component concentration measuring apparatus 100 according to the present embodiment, the biological component is measured using the calibrator 105 attached to the insertion probe 104 before measuring the infrared light emitted from the eardrum 202. By calibrating the concentration measuring apparatus 100, it is possible to confirm whether or not the biological component concentration measuring apparatus 100 is in a normal state, so that the measurement accuracy can be improved.

  Moreover, according to the biological component concentration measuring apparatus 100 according to the present embodiment, the infrared light emitted from the eardrum 202 is selected by blocking the infrared light emitted from other than the eardrum 202 using the liquid crystal shutter 120. Therefore, the influence of the external auditory canal 204 can be removed, and highly accurate measurement can be performed. Further, the measurement accuracy can be further improved by correcting the measured signal by the area of the eardrum from which the measured infrared light is emitted.

(Embodiment 2)
Next, the calibrator 700 according to the second embodiment will be described. 10A and 10B are diagrams showing the configuration of the calibrator 700 according to the present embodiment. FIG. 10A is a front view of the calibrator 700, FIG. 10B is a cross-sectional view, and FIG. FIG.

  The calibrator 105 according to the first embodiment is different from the calibrator 105 in that a cover 705 for protecting the distal end portion of the insertion probe 104 is integrated with the calibrator 700.

  The cover 705 is held on the support portion 502 by the elastic force of the support portion 502. As a material for the cover 705, a material having elasticity and transparent in the infrared region is preferable. For example, polycarbonate, polypropylene, polyethylene, or the like can be used.

  Next, a calibration method and operation of the biological component concentration measuring apparatus 100 according to the present embodiment will be described with reference to FIGS. 11 to 14 are sectional views of the insertion probe 104 and the calibrator 700.

  First, the user removes the calibrator 700 from the package, and inserts the calibrator 700 into the insertion probe 104 so that the cover 705 faces the tip of the insertion probe 104 as shown in FIG. The insertion probe 104 is provided with a stepped portion 601 so as to be fitted to the peripheral portion of the cover 705 provided in the calibrator 700, and the insertion probe 104 is tightened by using the elastic force of the cover 705. 12, the calibrator 700 is held at the distal end of the insertion probe 104.

  Next, the biological component concentration measuring apparatus 100 is calibrated by the same procedure as in the first embodiment.

  Next, the user confirms that the message indicating that the calibration is completed is displayed on the display unit 114, and pulls the projection 503 as shown in FIG. 502 and the infrared emitter 501 are removed from the insertion probe 104. At this time, unlike the first embodiment, as shown in FIG. 14, the distal end portion of the insertion probe 104 remains attached to the distal end portion of the insertion probe 104 to protect the distal end portion of the insertion probe 104.

  Next, after the user holds the main body 102 and inserts the insertion probe 104 into the ear hole 200, the measurement start switch 103 is pressed, and the measurement is performed as in the first embodiment.

  As described above, according to the biological component concentration measuring apparatus 100 according to the present embodiment, it is attached to the insertion probe 104 before measuring the infrared light emitted from the eardrum 202, as in the first embodiment. By calibrating the biological component concentration measuring apparatus 100 using the calibrator 700, it can be confirmed whether or not the biological component concentration measuring apparatus 100 is in a normal state, so that the measurement accuracy can be improved. .

  Further, according to the biological component concentration measuring apparatus 100 according to the present embodiment, since the distal end portion of the insertion probe 104 is protected by the cover 705 at the time of measurement, dust or the like is mixed in the insertion probe 104 during measurement. Therefore, accurate measurement can be performed without being disturbed by foreign matters such as dust.

  Further, after the measurement is finished, the cover 705 is left attached to the distal end portion of the insertion probe 104, and the user removes the used cover 705 from the distal end portion of the insertion probe 104 immediately before the next measurement. A new calibrator 700 is preferably installed. In this way, since the distal end portion of the insertion probe 104 is always protected by the cover 705 while the biological component concentration measuring apparatus 100 is stored, foreign matter such as dust is mixed in the insertion probe 104 even during storage. There is no longer to do.

(Embodiment 3)
Next, a calibrator 800 according to Embodiment 3 will be described. 15A and 15B are diagrams showing the configuration of the calibrator 800 according to the present embodiment. FIG. 15A is a front view of the calibrator 800, FIG. 15B is a cross-sectional view, and FIG. FIG.

  The calibrator 700 according to the second embodiment is different from the calibrator 700 in that an optical path changing element 805 attached to the distal end portion of the insertion probe 104 at the time of measurement is integrated with the support portion 502.

  An example of the optical path changing element will be described with reference to FIG. FIG. 16A is a cross-sectional view of the optical path changing element 805, and FIG. 16B is a front view.

  The optical path changing element 805 is held on the support portion 502 by the elastic force of the support portion 502. As a material for the optical path changing element 805, a material having elasticity and transparent in the infrared region is preferable. For example, polycarbonate, polypropylene, polyethylene, or the like can be used.

  The optical path changing element 805 has five protrusions having a triangular cross section. The optical path changing element 805 can be manufactured by a known resin molding technique using a mold.

  A reflecting mirror 806 is provided on one side of the protrusion having a triangular cross section to reflect infrared light. Any material can be used for the reflecting mirror 806 as long as it reflects infrared light and has no toxicity. For example, the reflecting mirror 806 can be formed by coating a material such as gold or aluminum after the optical path changing element 805 is formed by resin formation.

  Although FIG. 16 illustrates an example in which five protrusions are formed, the number of protrusions is not particularly limited, and may be one. The cross-sectional shape of the protrusion may be a trapezoidal shape.

  The Japanese average of the angle formed by the ear canal near the ear canal 200 and the ear canal 204 near the eardrum 204 is 146 degrees, and therefore, by setting the apex angle of the triangle in the cross section of the protrusion to about 46 degrees, the reflector 806 It is preferable to reflect infrared light at 17 degrees. Further, the apex angle of the triangle in the cross section of the protrusion may be optimized for each individual according to the degree of bending of the user's external auditory canal 204.

  Next, a method for forming the reflecting mirror 806 on the optical path changing element 805 will be described with reference to FIG. FIG. 17 is a cross-sectional view showing the structure of a vacuum vapor deposition apparatus 900 used when forming the reflecting mirror 806 on the optical path changing element 805.

  The optical path changing element 805 produced by resin formation is placed in a holder 902 provided in the bell jar 901 of the vacuum vapor deposition machine 900 so that one side of the projection faces downward, and the inside of the bell jar 901 is decompressed by the vacuum pump 905. To.

  Next, by irradiating a crucible 903 filled with a metal such as gold or aluminum with an electron beam generated from the electron gun 903, the metal in the crucible 903 is melted and evaporated, and the projection of the optical path changing element 805 is formed. A reflecting mirror 806 is formed on one surface.

  Since the calibration method and operation of biological component concentration measuring apparatus 100 in the present embodiment are the same as those in the second embodiment, description thereof will be omitted.

  FIG. 18 shows a state in which the insertion probe 104 of the biological component concentration measuring apparatus 100 according to the present embodiment is inserted into the external auditory canal 204 bent halfway.

  As described above, according to the biological component concentration measuring apparatus 100 according to the present embodiment, it is attached to the insertion probe 104 before measuring the infrared light emitted from the eardrum 202, as in the first embodiment. By calibrating the biological component concentration measuring apparatus 100 using the calibrator 800, it can be confirmed whether or not the biological component concentration measuring apparatus 100 is in a normal state, so that the measurement accuracy can be improved. .

  Moreover, according to the biological component concentration measuring apparatus 100 according to the present embodiment, as shown in FIG. 18, the infrared light emitted from the eardrum 202 is bent by the optical path changing element 805 attached to the distal end of the insertion probe 104. As a result, infrared light emitted from the eardrum 202 can be transmitted into the insertion probe 104 even when the ear canal 204 is bent halfway.

  The present invention is useful for non-invasive measurement of biological component concentration, for example, measuring glucose concentration without collecting blood.

The perspective view which shows the external appearance of the biological component density | concentration measuring apparatus in one embodiment of this invention The figure which shows the structure of the same biological component concentration measuring apparatus The perspective view which shows the optical filter wheel in the same biological component density | concentration measuring apparatus The image figure which shows the image when the inside of an ear canal is observed using the living body component concentration measuring device The figure which shows the structure of the calibrator in one embodiment of this invention Process diagram showing one process in the method of attaching the calibrator to the insertion probe Process diagram showing other steps in the method of attaching the calibrator to the insertion probe Process diagram showing further steps in the method of attaching the calibrator to the insertion probe Process diagram showing further steps in the method of attaching the calibrator to the insertion probe The figure which shows the structure of the calibrator in other embodiment of this invention. Process diagram showing one process in the method of attaching the calibrator to the insertion probe Process diagram showing other steps in the method of attaching the calibrator to the insertion probe Process diagram showing further steps in the method of attaching the calibrator to the insertion probe Process diagram showing further steps in the method of attaching the calibrator to the insertion probe The figure which shows the structure of the calibrator in other embodiment of this invention. The figure which shows the structure of the optical path changing element used for the same calibrator Sectional drawing which shows the structure of the vacuum evaporation machine used when forming a reflective mirror in the same optical path changing element The figure which shows the state which inserted the insertion probe of the biological component density | concentration measuring apparatus which attached the same optical path changing element in the bent ear canal

Explanation of symbols

DESCRIPTION OF SYMBOLS 100 Biological component concentration measuring apparatus 101 Power switch 102 Main body 103 Measurement start switch 104 Insertion probe 105,700,800 Calibrator 106 Optical filter wheel 107 Calibration switch 108 Infrared detector 110 Microcomputer 112 Memory 114 Display 116 Power supply 118 Chopper 120 Liquid crystal shutter 122 first optical filter 123 ring 124 second optical filter 125 shaft 126 detection region 130 preamplifier 132 band filter 134 synchronous demodulator 136 low-pass filter 138 A / D converter 140 light source 142 first half mirror 144 second Half mirror 146 Condensing lens 148 Image sensor 150 Actuator 152 Lens frame 154 Position sensor 156 Timer 58 buzzer 200 ear canal 202 tympanic membrane 204 ear canal 501 infrared radiator 502 supporting portion 503 protruding portion 504 hinge 601 stepped portions 705 cover 805 optical path changing device 900 vacuum deposition machine 901 bell jar 902 holder 903 a crucible 904 electron gun 905 vacuum pump

Claims (7)

An infrared detector that detects infrared light emitted from the eardrum in the ear canal;
An insertion probe inserted into the ear canal and guiding the infrared light to the infrared detector;
A calibrator used for calibration of a biological component concentration measuring device comprising a biological component concentration calculating unit that converts an output of the infrared detector into a biological component concentration,
An infrared emitter that emits infrared light; and
A calibrator comprising a support portion that supports the infrared emitter and fits with the insertion probe. The calibrator according to claim 1, wherein the emissivity of the infrared radiator is 0.9 or more. The support part is
A protrusion,
With a hinge part,
The calibrator according to claim 1 or 2, wherein the hinge portion is deformed by applying a tensile stress to the protrusion portion of the support portion attached to the insertion probe so as to be fitted to the insertion probe. . The support further comprises:
The calibrator according to any one of claims 1 to 3, further comprising a cover for protecting the insertion probe at a position covering the infrared radiator. The support further comprises:
The calibrator according to any one of claims 1 to 3, further comprising an optical path changing element for changing an optical path of the infrared light at a position covering the infrared radiator. An infrared detector for detecting infrared light emitted from the eardrum in the ear canal;
An insertion probe inserted into the ear canal and guiding the infrared light to the infrared detector;
A biological component concentration calculator that converts the output of the infrared detector into the concentration of biological components;
A biological component concentration measuring apparatus comprising the calibrator according to claim 1 attached to the insertion probe. Using the calibrator according to any one of claims 1 to 5,
(A) measuring the intensity of the infrared light emitted from the infrared emitter of the calibrator attached to the insertion probe;
(B) comparing the intensity of the infrared light measured in the step A with a preset allowable range;
(C) A method for calibrating a biological component concentration measuring apparatus, including a step of determining whether or not the biological component concentration measuring apparatus is normal based on the comparison in the step B.

Images