WO2020017028A1

WO2020017028A1 - Nondestructive inspection device

Info

Publication number: WO2020017028A1
Application number: PCT/JP2018/027299
Authority: WO
Inventors: 木暮一也
Original assignee: 桐生電子開発合同会社
Priority date: 2018-07-20
Filing date: 2018-07-20
Publication date: 2020-01-23
Also published as: CN112351735B; CN112351735A

Abstract

[Problem] To develop a device that uses light to accurately measure the amount of temporal increase/decrease and the amount of change over time of a substance which changes temporally, and that displays the results thereof. [Solution] The present invention irradiates a sample including a substance to be measured with light from at least two light sources, and measures fluctuations relative to components other than the substance to be measured with light from at least one light source and measures fluctuations of the substance to be measured with light for measuring the substance to be measured. In order to accurately measure the amount of change of the substance to be measured, the fluctuation amount of the components other than the substance to be measured is set as a correction value. Measurement is conducted three times at certain intervals therebetween, and the difference between the first measurement value and the third measurement value is calculated, a temporal differential value of the difference between the first and second measurement values is computed, and a final result is found using the difference value between the first and third measurement values and the temporal differential value between the first and second measurement values.

Description

Non-destructive inspection equipment

The present invention relates to a nondestructive measuring device for measuring, calculating and displaying a relative change amount of a rise and fall amount and a temporal differential value of a change amount from a time when a substance to be measured is a non-destructive reference.

It is desirable to measure nondestructively when measuring the amount of a substance accompanying a time change included in a sample with time, especially when the time change is important. One of the non-destructive means for measurement is a light measurement method such as spectroscopic analysis. One of the indications is a non-invasive blood glucose measurement technique. This is to identify the blood glucose level by the amount of change in physical properties such as light absorbance and polarization, depending on the concentration of the blood glucose level. As a typical technique, a plurality of methods based on near-infrared spectroscopy as shown in FIG. 1 have been reported in the past. This method measures the mass (concentration) of a substance to be measured based on the intensity distribution of the spectral spectrum. In order to identify the substance to be measured from the spectrum intensity distribution, a calibration method showing the basic spectral spectrum intensity distribution is used. A method called a curve is required, and a method of efficiently creating the calibration curve by utilizing a simulation technique or the like has been proposed. However, analysis of a large amount of measurement data is required.

Furthermore, this analysis method is generally applied under specific conditions, and when applied to a plurality of unspecified samples, there is a very difficult problem. That is, the components other than the substance to be measured differ from individual to individual. It is almost impossible to adapt and use the measurement widely due to physical variation and individual differences. The method based on the spectroscopic analysis is basically a method for measuring the absorbance of light, but the same can be said for other methods using polarized light. After all, if the problems in the case of measuring a substance which changes with time by light with time are determined and sorted out, it will result in the problems of reproducibility and measurement accuracy due to generation of a calibration curve, physical variation and the like. It is difficult to realize a destructible measurement device that measures the amount of a substance that changes with time by light with time.

Patent No. 3692751

The problem to be solved is that, although it is understood that the measured value changes with time due to light, the mass (concentration) of the substance to be measured is measured because the accuracy of the calibration curve and the measurement accuracy are reduced due to physical variation. However, it is difficult to implement a destructible measurement device using light.

The present invention changes the way of thinking about the measurement of a substance by light, does not create a calibration curve, and measures and calculates the relative change and the temporal change of the substance to be measured from a certain time to a certain time. The main feature is a method of using the light emitting portion as an action point for applying pressure to a measurement site, and adjusting the optical axis for measurement in real time to perform measurement.

Although the destructive measuring device of the present invention does not directly measure the amount (concentration) of the substance to be measured, it can perform destructive measurement using light with good reproducibility as an index instead of the mass (concentration) of the substance to be measured. become.

It becomes possible to detect a state in which the mass (concentration) of the substance to be measured suddenly increases, which cannot be found by discrete measurement until now, by being destroyed.

Configuration example of non-destructive measurement device using spectroscopic analysis Examples of changes in diet and blood sugar Actuator Lens Shift operation and Tilt operation Optical configuration when using transmitted light Optical configuration when using reflected light Configuration with built-in optical unit in Clip mechanism Electrical circuit block diagram of the measuring device centering on the analog circuit Adjustment period by LD1 and measurement period by LD2 Electric circuit block diagram when digital processing by MPU is centered Example of dds value Graph to display the final measurement result from the measurement value

Next, a case where the present invention is applied to measurement of a blood glucose level will be described as one embodiment of the present invention with reference to the drawings. Of course, it is also possible to measure not only the blood sugar level but also a change in the photosynthesis of a plant, for example, in which it is important to measure the temporal change of the substance to be measured.

Various methods have been proposed for measuring blood glucose levels non-destructively (hereinafter referred to as non-invasive in measuring blood glucose levels) using light. Here, identification is based on light absorbance and diffusion degree. I have. It is known that the degree of diffusion is proportional to the blood glucose concentration, so a Photo Device (hereinafter referred to as PD) is used to measure the amount of light. Depending on the size (area) of the PD, the sensitivity is Differently, the size is equal to or larger than the light diameter of the light to be used (the size is determined from the range of the assumed diffusion degree). In this case, the amount of light detected by the PD is reduced by absorption by blood sugar, and at the same time, is diffused by tissue (diffuser) and blood sugar. Therefore, the amount of light detected by the PD expands the absorbance by the degree of diffusion, and the amount measured by the PD increases the sensitivity of detecting a change in blood glucose level. The measured value obtained by superimposing the absorbance and the diffusivity is used as a basic detection amount. The absorbance is determined from the detected amount. In addition, since the light absorption changes depending on the temperature, the temperature of the measurement site is measured and corrected by the temperature value to obtain the final light absorption.

First, the nature of the blood sugar level will be confirmed here. Blood sugar is one of blood components, but there are a plurality of substances other than blood sugar that have light absorption properties near a wavelength called near infrared. If you eat a meal, your blood level will rise about 20 to 40 minutes after the meal for a certain period of time, usually as a response change of the human body, and about 2 hours after the meal due to the action of insulin etc., about the same as before the meal It is estimated that only blood glucose and water are the only components that change rapidly in the blood due to this eating action. The reason is that substances other than blood sugar level are components generated from each organ or components generated by reaction, and it is very slow compared to changes in blood sugar level before appearing as changes in blood components It is. Therefore, it is considered that a factor in which the absorbance and the diffusivity change in a short time of about 2 hours can be almost identified as a blood glucose level. It is possible to separate blood by measuring the absorbance of a light source at a wavelength different from the absorption spectrum wavelength of blood glucose. In other words, it indicates that the change amount of the blood sugar level can be corrected based on the absorbance sensitivity characteristic due to the moisture and the difference in the blood sugar level absorbance. However, it is necessary that the two light sources be observed coaxially. Originally, a blood glucose level cannot be identified unless a calibration curve based on a large amount of data is created for identification of non-blood glucose.However, a calibration curve is not required for such a change in blood glucose level. become. As described above, the present apparatus is basically characterized in that the amount of increase or decrease in blood sugar level is measured. Further, when measuring the amount of increase or decrease in blood sugar level as in this measurement, errors due to individual variations such as skin pigments and skin conditions can be offset, so that measurement accuracy and reproducibility can be improved.

In a healthy state, the blood sugar level in a living body becomes almost the same as that before a meal about 2 hours after a meal. However, in glucose metabolism in so-called diabetes, it is known that the amount of change is characteristic. FIG. 2 shows a general example of a temporal change of the blood sugar level.

Therefore, three measurements are performed before and after the meal, about 30 minutes after the meal, and about 2 hours, and the judgment is made. This is similar to a glucose tolerance test in a clinical diagnosis method of diabetes. In the case of severe (12c), the blood glucose level before meals, 30 minutes, and 2 hours may not change. Therefore, a temporal change amount and a time differential value of the measured value are calculated, and a composite judgment of the change amount and the time differential value in real time is performed.

Usually, the measurement of a blood sugar level performed in a health check or the like is a so-called fasting blood sugar level. Even if the value is measured somewhat high, it is possible to overlook the severity. The response called "hidden diabetes" is also a rapid rise in blood glucose level after eating, and this time differential value can detect this symptom.

Next, a solution to the physical variation will be described.

In the case of measurement using light, a change in the optical path length causes an error and a reduction in accuracy. Therefore, the optical path length must be constrained at a fixed position so as not to change, which is extremely inconvenient. Considering convenience, the method of measuring with reflected light is excellent, but if the part to which light is actually applied changes, the subcutaneous tissue at the measurement part may change, With a decrease in In addition, accuracy is also reduced by the light incident state, vibration, and the like. Therefore, as a structure of the measuring device, first, a structure for limiting a part to be measured is adopted. This is, for example, a structure of being sandwiched between ear tabs and fingers (FIG. 6). In this case, the measurement is performed at a substantially constant site. Also, the ear tabs and the area between the fingers may be less susceptible to the change in pigment. In addition, it is known that the absorbance changes when the temperature changes, and it can be expected that a portion that can be sandwiched does not involve a large temperature change.

The sandwiching structure allows the optical path length to be kept constant, and also allows a constant pressure to be applied to the measurement site, which can suppress changes in blood flow. Become. When measuring by light, the most influential thing is hemoglobin of blood, and a change in this decreases measurement accuracy. In particular, the change in blood flow is large, such as after a meal. Even if the part to be measured is limited to some extent, blood vessels are present in the subcutaneous tissue, and if blood vessels on the optical path are included, accuracy is expected to decrease. Therefore, using a Actuator (same structure as an optical pickup such as a CD or DVD, etc., not shown) to reduce the light beam, provide a mechanism to adjust the irradiation position at the site and to adjust the detection light to the maximum. . In addition, this mechanism is provided with a mechanism that suppresses the movement of the blind muscles and adjusts the incident state in real time to ensure accuracy. FIG. 3 is a diagram for explaining measurement by moving the Actuator. However, there are physical mutations that cannot be corrected by this adjustment mechanism. For this purpose, the blood glucose level is corrected by a light source that is arranged coaxially with the beam that measures the blood glucose level and has the same optical path and has a different wavelength, and at the same time, corrects the physical variation and correction. Physical variation is possible because it is considered to vary in the same way as variation in wavelength by measuring blood glucose levels.

FIG. 4 shows an optical basic configuration. As a feature, a near-infrared light source (a semiconductor laser diode is used in this configuration) uses a plurality of different wavelengths, and the plurality of light sources are emitted coaxially. As a wavelength, a light source exhibiting large absorption in Glucose, for example, a light source near 1500 nm (measurement light: 23a), a second wavelength light source (hereinafter, LD2) and a 1300 nm light source (reference light: 23b), a first wavelength light source (hereinafter, LD1)
Use Laser light is desirable as the light source. The reason is that the emission wavelength range is very narrow and can be treated as a single wavelength. Of course, a light source having a light emission characteristic with a deviation of about 10 nm as a range considered as a single wavelength may be used.
The reason for choosing a wavelength around 1300 nm is that, while showing high absorbance for moisture, Glucose is a light source with a wavelength that does not show large absorption, and combining that light source, from the change in the absorbance, The detection amount is corrected by the measurement light as the change amount of the water content and the physical change amount. This correction method may be a method of obtaining a difference or a method of obtaining a ratio. In addition, the detection amount by the reference light is used as a control amount for correcting the vibration of the measurement site and the incident light state and avoiding an obstacle on the optical path, so that the amount of light detected by this wavelength is maximized. , And electrically controls an Actuator described later. FIG. 4 shows a configuration in which transmitted light is used for a measurement site, and FIG. 5 shows a configuration for detecting diffuse reflection light. Both configurations are detected in a state where irradiated light passes through the inside of the measurement site. The light from the light sources (23a, 23b) is condensed to a small beam by the lenses (24a, 24b) to become collimation light (14). (The reason for narrowing the beam to a small diameter is that it is possible to secure the brightness without using a light source with a large output, to reduce the power consumption and to suppress the cost. This is because it can be avoided when there is a blood vessel (13) .Beam becomes coaxial light by PBS (25a, 25b) etc. However, two light sources emit light at the same time. After that, it has a function to correct the irradiation position on the measurement site (21) by Actuator Lens (22) .The operation of this Actuator can be Shift (16) and Tilt (15), see The adjustment is performed in real time so that the value detected by light is maximized, and the response speed of the Actuator for this adjustment does not need to be fast, and the characteristics may be covered as well as the so-called inactive muscle movement. The part (20a, 20b) that actually touches the measurement site is reflected directly from the surface Also has a function to eliminate the effects. In addition, also functions as a working point for applying a constant pressure (18) with respect to the measurement site.

As a mechanism for holding this optical structure, a structure like a clip is used. The reason is, as described above, the limitation of the measurement site and the limitation of blood flow. FIG. 6 shows the structure, and incorporates the structure of the optical structure shown in FIGS. In FIG. 6, the light from the light source (14) is guided by the mirror (29) in the housing (27). However, a configuration in which the light is guided to Actuator Lens by a fiber or the like is also possible (not shown). FIG. 6 shows the configuration of transmitted light, but the same mechanism is used for diffuse reflection, and the optical structure shown in FIG. 5 is incorporated. In this case, the converging objective lens (20b) arranged on the PD side in the structure using transmitted light becomes the measured object support component (26).

FIG. 7 is a basic electric circuit block diagram. Although FIG. 7 shows a configuration using transmitted light, the same configuration is used in an electric circuit when diffuse reflection light is used. OSC1 (30a) (not shown) is a signal used for measurement, for example, a signal for AC-modulating the optical output at 1 Khz. The measured value is the amplitude at which the signal obtained by absorbing and diffusing the signal by the OSC1 (30a) by the measurement site is detected by the PD (17). OSC2 (30b) switches between light source 1 (23a) (hereinafter LD1) and light source 2 (23b) (hereinafter LD2). When LD1 emits light, LD2 stops, and when LD2 emits light, LD1 stops. The light emission is alternately switched by the light source changeover switch circuit (31) as described above. For example, when the output of OSC2 (30b) is H, LD1 emits light, and when it is L, LD2 emits light. LD1 is the reference light, and LD2 is the measurement light. The output of the PD (17) (shared with the reference light and the measurement light) is IV-converted (35) and amplified by the synchronous AMP (36). The light source drive circuits 1 and 2 (hereinafter LDD 1 and 2) (32a and 32b) have a high-frequency superimposing function (34) on the laser diode, and in order to avoid instability of laser emission due to reflected light, switch from single mode to multi The optical output is kept constant by an APC circuit (not shown) such as Front Monitor and Back Monitor Diode used in -Mode oscillation. In addition, a temperature sensor (34) is arranged to correct for changes due to temperature. The RMS circuit (37) outputs the effective value of the detected signal and inputs it to Servo @ AMP (38, 40). The circuit (41b) that holds the output of the RMS circuit (37) when the LD1 emits light and the reference voltage (39) (corresponding to the reference light amount) are input to the LD1 Servo AMP and the difference is calculated to automatically calculate the light emission amount of the LD1. Form Servo Loop to control. With this operation, the light amount of the reference light received by the PD (17) becomes constant without the influence of the basic transmission amount. The LD1 Servo AMP (38) calculates and obtains the input amount of LDD1 (32a). If this output is large, it indicates that the amount of light attenuation in the DUT (21) is large. This is the reference value for LD2. This reference value means that the optical power necessary for basically measuring the object under measurement (21) is automatically obtained. Using the detected amount of LD1 as a reference of the LD2 measurement light is equivalent to correcting the physical displacement of the measured object (21) and the displacement of the water content. Since the physical displacement (systematic variation of the DUT (21)) is considered to have the same attenuation characteristics (does not affect the light absorption characteristics and diffusivity characteristics) for both LD1 and LD2, the amount detected by LD1 is physical. This reflects the amount of displacement and the amount of correction of the absorbance due to moisture that may vary with time. Also, the difference between the output of the circuit (41c) that holds the output of the RMS circuit (37) when the LD2 emits light and the output value of the circuit (41a) that holds the control amount of the LD1 is calculated, and the control of the LD2 is performed. By using the output, the output of LD2 can be kept constant. (The optimal value of the ratio between the light emission amount of LD1 and the light emission amount of LD2 is determined in advance, and the gain of the LDD is determined according to the ratio.) Circuit (41a) for holding LD1 control amount (OSC2 (30b) For example, when the output is H, the output from the RMS circuit (37) from LD1 is held by the LD1 detection value hold circuit (41b), and when the output is L, the LD2 detection hold circuit (41c) is held) and the control amount of LD2 The output of the measurement value correction circuit (42) that calculates the difference between the two is finally a measurement value obtained by correcting the physical displacement and the water displacement from the LD2 detection amount. In this apparatus, the measurement is performed three times with a time lag. A method of obtaining a final result by these three measurements will be described later.

Actuator @ Lens (22) adjusts according to the light emission period (49) of LD1. When the light is emitted for the first time, the difference between the outputs (17s, 17b) of the Side SUB-PDs of the Main @ PD (17) is calculated (43), and it is possible to detect which side the Beam center is on. Accordingly, the center of the intensity of light detected by the PD becomes the center of the PD. In the configuration shown in FIG. 7, when the output of S (35 s) is large, the light intensity distribution detection circuit produces an output on the (+) side from the reference voltage, and the Shift Drive circuit (44b) is driven in a direction in which this output becomes smaller. When the output (35b) is large, an output of (-) appears from the reference voltage, so that the Shift Drive circuit (44b) is driven in reverse to the S (35s) signal so that this output becomes small. Driving LD1 for measurement and this Shift Drive mechanism (47) are performed at the same time, and the amount of LD1 detected is determined. Then, LD2 is detected during the emission period (50) of LD2, and the final measured value is calculated. obtain. FIG. 8 shows switching between LD1 and LD2. In addition, in order to improve the SNR of the measured value, the average value (superimposed value) is used. In this example, the signal is a continuous signal as the modulated signal (30c). If the Actuator Lens has a Tilt function, the control output of the reference light by the LD1 is measured a plurality of times using the LD1 emission period (49) before starting the measurement, and the Tilt Drive reference voltage generation circuit (46) is used each time. ) (This uses a very small MPU, etc.) to change the output, drive the Tilt Drive mechanism (48), find the state that minimizes the LD1 control amount, and then adjust with the Shit Drive mechanism. Enter the measurement cycle. The new Tilt-Drive mechanism (48) and Shift-Drive mechanism (47) provide real-time adjustments to eliminate the influence of the tissue structure of the measurement site and to correct for deviations due to vibration and the like.

In FIG. 7, the configuration of an analog Servo-Loop is shown as an electric circuit, but it is naturally possible to realize the digital circuit by using an MPU (52) or the like. In addition, because of the analog-like Servo-Loop, the light emission of LD1 and LD2 is considered to emit light with a waveform (30c) from the oscillator as shown in FIG. 9, but this light emission is considered to be a short pulse light emission (30d), for example, 10 ns or less. This can be realized by performing pulse emission of about 30 ns, and this pulse emission also makes it possible to avoid a rise in the temperature of the measurement site due to light energy. By suppressing the temperature rise, improvement in measurement accuracy can be expected. In the case of a blood glucose level, the skin is measured on the human body at the measurement site. Therefore, when extremely intense light is continuously irradiated, it is possible to avoid the possibility of burning due to the light. The safety zone for the human body with respect to the light intensity (energy amount) is determined based on internationally standardized safety standards. The synchronous AMP (36) is also realized by digital signal processing. The control amount of LD1 and LD2 of Servo Loop itself becomes a detection amount corresponding to the absorbance and the diffusion degree as a result. FIG. 9 shows a configuration diagram in that case. First, the value (36a) at the time of light emission of LD1 (light emission control amount is a predetermined amount) is input to AD several times, and the drive amount of the Tilt drive circuit (45b) is changed so that the detection amount of LD1 is minimized. The signal (35s, 35b) from the Sub-PD is AD-input to the MPU (52) for adjustment by the Shift-Drive mechanism (47) with the optimal drive amount detected and determined as the optimal state of Tilt. In (17), calculation (operation corresponding to the light intensity distribution detection circuit (43)) is performed in the MPU (52) so as to be at the center of Beam, and the Shift 駆動 Drive circuit (44b) is driven. This series of Tilt control and Shift control are performed before the measurement by LD1 and LD2. When driving LD1 and LD2, LD1PUON / OFF signal (32d) and LD2ON / OFF signal (32e) drive LD1 and LD2 from MPU (52), but correspond to modulation by OSC1 (30a). Control. First, the output from the MPU is adjusted by a certain amount in the LD1 emission control amount (32c), and the value input from the AD (36a) becomes a predetermined value (corresponding to the LD1 reference voltage generation circuit (39)). The detection amount is determined so as to be the detection value of LD1. Subsequently, similarly, the LD2 emission control amount (32f) is adjusted so that the value input (36a) to the MPU by the AD becomes a constant amount based on the amount detected by the LD1. At this time, the LD2 emission control amount (32f) is a detection amount by LD2. Next, the detection amount of LD1 is subtracted from the detection amount of LD2 by the MPU (52), and corrected by the signal (33a) from the temperature correction sensor (33). (The correction amount is based on the value obtained from the absorbance characteristics with temperature.) (Determined experimentally) is the final measured value. With this configuration, it is assumed that the measured blood sugar level is in the range of 50 mg / dl to 200 mg / dl. SMBG actually used for the treatment of diabetes requires a range of about 0 mg / dl to 900 mg / dl. If this Range is assumed, a considerably large Laser output may be required, but by reducing the Range, low power consumption and Cost Down can be realized.

Next, the handling of three measured values and the output of the final result, which are the features of the present apparatus, will be described based on the specific operation of the apparatus. First, the pre-meal operation switch (54a) is operated to measure the pre-meal value. The measured value at this time is (t1, S1). Next, when about 30 minutes have passed after the meal, the post-meal operation switch (54b) is operated to perform measurement. The measured value at this time is (t2, S2). Further, when about two hours have elapsed, the after-meal operation switch is operated to perform measurement. The measured value at this time is (t3, S3). (Judgment after 30 minutes, 2 hours, etc. is made by the clock (55) inside the apparatus.) From this measurement value, ds = S3-S1 is obtained. This value is the basic measurand of this device. Next, it is determined as dts = (s2-s1) / (t2-t1). This value is a time differential value indicating how much the value has changed in a short time, and as a device, the result determined from the value of ds and the value of dts is displayed on the display (53). This value indicates the rising speed of the blood sugar level. Blood sugar levels are greatly changed depending on the state of metabolism, how to eat, and the contents, and even if the fasting blood sugar levels are normal, they may rise sharply by eating. This increased blood sugar level is called a blood sugar spike, and the fact that the value of this spike is large is also called so-called hidden diabetes. If the current time derivative is large, it is estimated that there is a large blood glucose spike. When detecting this blood sugar level spike in normal blood sugar level measurement, it is necessary to continuously measure the blood sugar level and measure the maximum value. In this method, the measurement is equivalent to the measurement of the blood glucose spike even if the measurement is not performed continuously. Also. In the present measurement method, the difference between the measured values and the rate of change are completed and calculated within a short period of time, so that the deviation from the accuracy is canceled out, and the measurement accuracy and reproducibility are improved.

Graph in FIG. 10 is a graph for obtaining a final judgment value. The horizontal axis represents the value of ds (56), and the vertical axis represents the final measurement result dds (57). A plurality of curves in this space correspond to dts (58). The ds, dts, and dds characteristics indicate that dds (57) increases when the dts (57) value is high even when the ds (56) value is low. Which dts (58) curve is selected is selected, for example, by a value obtained by normalizing the dts value to about 20. (How to draw this dts curve is determined as a product specification based on medical test standards for actual blood glucose levels.)

When the ds value (56) and dts (58) correspond to the area shown in FIG. 10 (59), the measured value may be abnormal or may be an abnormal measurement result. In such a case, the dds (57) value is displayed on the display (53) and flashes at the same time, indicating that the measured value result needs attention. For example, when glucose metabolism is abnormal (severe), the ds value may be small. Also, the dts value can be small. This state corresponds to a case where the blood sugar level is extremely high before the meal and the blood sugar level does not rise further by the meal. Further, the setting of the area shown in (59) assumes breakfast, lunch, and dinner, and prepares three types of graphs, and selects which graph is selected depending on the time zone of the measurement. For example, if the clock (55) is in the morning, it is possible that a considerable amount of time has passed since the previous day's meal, and in this case, the blood sugar level may have dropped accordingly. Use the Graph that works from time to time. Although the finally obtained dds value will be displayed on the display, this measurement device does not display a numerical value. Use Color Gradation instead. For example, “blue” is set based on the case where the dds value is 0, and the numerical value vs. Color is mapped (60) so that the maximum value is set to “red”, for example.

It can be used as an index for the purpose of new health management instead of blood sugar level, and can be applied as a diagnostic device for early detection of so-called hidden diabetes, which has not been able to measure and detect fasting blood sugar level until now. In addition, by using a method of measuring the state of change, for example, by measuring a change in sugars generated by photosynthesis of a plant, the method can be applied to an agricultural control device.

1 light source
2 Aperture
3a Objective lens (for coupling)
3b Objective lens (for focusing)
4 Fiber 5 DUT 6 Shutter
7 Analysis grid 8 Mirror
9 Photo Array
10 AD converter
11 processor
12a Example of normal blood glucose level over time
12b Examples of temporal changes in abnormal glucose metabolism
Example of temporal change in 12c glucose metabolism disorder (severe)
13 Blood vessels, etc.
14 luminous flux
15 Tilt Actuator Lens by Tilt
Actuator Lens moved by 16 Shit
17 PD (Photo Device)
18 Light Path
19 Pressurization
20a Objective lens for light emission
20b Focusing Lens
21 DUT
22 Actuator Lens
23a Light source 1
23b Light source 2
24a Collimation Lens1
24b Collimation Lens2
25a PBS (for synthesis)
25b PBS (for reflected light separation)
26 DUT support parts
27 Equipment housing
28 fulcrum
29 mirror
17s PD Side Sub-PD (s)
17b PD Side Sub-PD (b)
30a OSC1 (signal oscillator)
30b OSC2 (light source switching signal generator)
30c OSC1 output (light source modulation output)
30d LD1, LD2 pulse emission waveform
31 Light source switch
32a Light source drive circuit 1 (LDD1)
32b Love reduction drive circuit 2 (LDD2)
33 Temperature compensation sensor
34 Multi-emission oscillator
35 I / V conversion circuit
36 Synchronous amplification circuit
37 RMS (RMS circuit)
38 LD1 Servo AMP
39 LD1 reference voltage generator
40 LD2 Servo AMP
41a LD1 Control amount Hold circuit
41b LD1 Emission detection value Hold circuit
41c LD2 emission detection value Hold circuit
42 Measured value correction circuit
43 Light intensity distribution detection circuit
44a Shit Drive Buffer circuit
44b Shift Drive circuit
45a Tilt Drive Buffer circuit
45b Tilt Drive circuit
46 Tilt Drive reference voltage generation circuit
47 Shit Drive mechanism
48 Tilt Drive mechanism
30 OSC1 output (light source modulation output)
49 LD1 emission period, Actuator Lens adjustment organization
50 LD2 emission period (measurement period)
51 OSC2 output
32c LD1 emission amount control amount signal
32d LD1 ON / OFF control signal
32e LD2 ON / OFF control signal
32f LD2 emission amount control amount signal
33a Temperature sensor signal
36a PD Side Sub-PD signal input
36b PD Side Sub-PD signal input
52 MPU
53 Display device
54a Operation switch (before meal)
54b Operation switch (after meal)
55 clock
56 ds calculated
57 dds final measurement result
58 dts curve
59 Flashing display Yanagi value
60 dds Display color Mapping

Claims

A measurement device having a light-emitting unit, a light-receiving unit, and a control unit, an optical measurement unit that measures the concentration of an internal substance in a measurement target site, a display unit that displays the measurement result, and a communication device that has a communication function of outputting to the outside. ,
The light emitting unit individually outputs light emitted at a single wavelength of the first wavelength and the second wavelength to the measurement site, respectively,
The light receiving unit detects light from the light source that has passed through the inside of the measurement site at the measurement site, respectively.
The control unit includes an arithmetic processing unit, and the arithmetic processing unit converts the light from the light source that has passed through the inside of the measurement part into the first wavelength and the light from the light source that has passed through the inside of the measurement part having the second wavelength. The first absorbance and the second absorbance, which are the proportions of the substance to be measured inside the part to be measured, are converted into the first and second absorbances, and the second absorbance is corrected using the first absorbance. Is held as a first measurement value by the control unit, the same measurement is performed again after a lapse of a certain time, and this is held as a second measurement value by the control unit. 3 control values are stored in the control unit.
The difference between the first measurement value and the third measurement value is calculated by the control unit as a change in the concentration of the measurement substance at the measurement site, and the difference between the first measurement value and the second measurement value is calculated from the measurement time of the first measurement value. Calculating the time change rate based on the elapsed time length until the second measurement value is measured and outputting the density change amount data and the time change rate data to the display unit to the display unit; A non-destructive measuring device characterized by having a function of transmitting a signal.
A non-destructive measuring device in which a substance to be measured at a measurement site of the concentration change amount data and the time change ratio data according to claim 1 is a blood glucose level in the body.
A nondestructive measurement device having a function of displaying the concentration change amount data and the time change rate data according to claim 1.
A nondestructive measurement device having a communication function for outputting the concentration change amount data and the time change rate data according to claim 1 to an external device.
3. The non-destructive measuring device according to claim 1, wherein a measured value is obtained by subtracting the first absorbance from the second absorbance in claim 1 as a correction operation.
The nondestructive measurement apparatus according to claim 1 or 2, wherein a measured value is obtained by dividing the second absorbance and the first absorbance in claim 1 as a correction operation. apparatus.
A two-dimensional data table having axes of the density change data value shown in claim 1 and the time change data value shown in claim 1 as axes, wherein a measured density change data value and a measured time change rate data data table are provided. 7. The non-display device according to claim 1, further comprising a function of performing an operation of converting a value set in advance into a color and displaying the color on a display unit according to claim 1. Destructive inspection equipment.
The nondestructive inspection apparatus according to any one of claims 1 to 7, further comprising a mechanism for correcting an irradiation position and an angle of light to be irradiated on the measured part.
A structure in which the light emitting part is used as an application point for applying a constant pressure to the measurement site including the substance to be measured, and a constant pressure is applied to the measurement site, and a constant pressure is applied to the measurement site 9. The nondestructive inspection apparatus according to claim 1, wherein the non-destructive inspection apparatus has a structure for measuring a substance to be measured inside a part to be measured.