JPH07294519A - Measurement of component in urine - Google Patents

Abstract

PURPOSE:To simultaneously determine many components without using a reagent, a test paper piece and enzyme by irradiating a urine sample with visible light or near infrared rays and measuring absorbancy at a selected specific wavelength. CONSTITUTION:A wavelength wherein the absolute value of the correlation coefficient between the concn. and absorbancy within the visible or near infrared wavelength region of an aq. soln. of the single component among respective components to be measured in urine is 0.5 or more, pref. 0.9 or more is selected as the measuring wavelength inherent to the single component. The cell having a urine sample received therein of a sample arranging part 2 is irradiated with visible light or near infrared rays from a light source part 8 and the absorbancies of the respective components to be measured in urine are measured at respectively selected measuring wavelengths in a detection part 12. A computer 6 quantitatively analyzes the respective components in urine from the obtained measured values at the same time according to multivariate regression analysis.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a method for simultaneously measuring the concentrations of urinary components such as glucose, hemoglobin, protein, bilirubin, urobilinogen, ketone bodies and nitrite in the field of clinical examination.

[0002]

2. Description of the Related Art Methods for measuring urinary components include a reagent method, a test strip method, a chemiluminescence method, an immunoassay method, an enzyme method and a chromatography method. In the reagent method, sugars and proteins are measured using reagents.

The test paper used in the test paper method is often one in which a reaction part of cellulose containing a reaction reagent is fixed to a plastic support piece with an adhesive or the like and dried. When the reaction part contains moisture, a reaction occurs between the reagents, and it also deteriorates due to high temperature and light, and the sensitivity often decreases,
The container for storing the test paper should be tightly sealed and stored at high temperature.
It is necessary to use it within the expiration date. Test paper method is p
Items such as H, protein, glucose, ketone bodies, bilirubin, occult blood, urobilinogen, nitrite, and bacterial infection can be measured within 1 minute, but the reaction of the reagent part is not limited to endogenous promoters and inhibitors. However, it is also affected by the reaction temperature and the conditions of the test paper, and only a semi-quantitative amount can be obtained.

The enzymatic method is used for measuring sugar. GOD-
A method of measuring the color development associated with redox reaction with a POD dye system using a reflectometer, or a method of amperometrically measuring the anodic oxidation current with a GOD-immobilized enzyme electrode and converting the current value to a concentration (biosensor, etc.) ) Is done. The method using glucose oxidase is highly specific to glucose and is simple, but the GOD reaction is a redox reaction, and the reaction is suppressed by various endogenous and exogenous oxidation and reduction substances. There is also a risk of false negatives and false positives. The chromatographic method uses expensive equipment such as a gas chromatogram and a liquid chromatogram.

[0005]

[Problems to be Solved by the Invention] The reagent method, test strip method and enzyme method require reagents, test strips or enzymes, which are consumables, and the storage stability of the reagent before use and the disposal after use. There is also the problem of. Furthermore, the operation is complicated, and errors such as the amount of reagent or sample added may occur due to mistakes during the operation, and there is also a drawback that it is interfered by other components such as ascorbic acid which are not intended for measurement. Although the reagent method and the enzyme method can perform quantification, they cannot measure multiple components at one time, and the test strip method allows simultaneous measurement of multiple components, but has the disadvantage that only semi-quantification is possible. The chromatographic method requires an expensive apparatus, and when the column performance deteriorates, the column must be replaced, which causes a problem of high cost.

The present invention eliminates the need for consumables such as reagents, test strips, and enzymes, and further, the storage safety of these consumables before use, the problem of disposal after use, and troublesome operation and other errors. It is an object of the present invention to provide a method for quantitatively measuring multiple components at the same time by eliminating problems such as interference by the components.

[0007]

In the present invention, for each urinary component to be measured, the absolute value of the correlation coefficient between the concentration and the absorbance in the visible or near infrared wavelength region of the single-component aqueous solution. Of 0.5 or more, preferably 0.9 or more is selected as a measurement wavelength specific to the component, and a plurality of urinary components to be measured by irradiating a urine sample with visible light or near-infrared light For each of the above, the absorbance at the measurement wavelength selected under the above conditions is measured, and the plurality of urinary components are simultaneously quantitatively analyzed by the multivariate regression analysis method. The correlation coefficient Rj between the absorbance A and the concentration at a wavelength λj for a certain component is given by the following equation.

[0008]

[Equation 1]

In the above equation, Aij is the absorbance of the component at the wavelength λj in the i-th sample, and Ci is the concentration of the component in the i-th sample. Avoid the wavelength range that has strong absorption for water as the measurement wavelength of each urine component,
Selecting from the wave number region of high transmittance 25000～5280Cm ^-1 or 4980～4000Cm ^-1 to water.
The preferred measurement wavelength of each component is represented by wave number, and is 11380-9720 cm ^-1 , 9430 for glucose.
~ 9400 cm ^-1 , 9340-9320 cm ^-1 , 926
0-6560 cm ^-1 , 6510-5540 cm ^-1 , 55
30-5280 cm ^-1 , 4980-4850 cm ^-1 , 4
830-4480 cm ^-1 , 4440-4330 cm ^-1 or 4300-4010 cm ^-1 and for hemoglobin 25000-7250 cm ^-1 , 7220-6
430 cm ^-1 , 6190-5690 cm ^-1 , 5660-
5280 cm ^-1 or 4900-4080 cm ^-1 and for albumin 7280-6350 cm ^-1 ,
5910-5880 cm ^-1 , 5790-5740c
m ^-1 , 5630-5300 cm ^-1 , 4900-4720
cm ^-1, 4670~4280cm ^-1 or 4230-40
70 cm ^−1, and for lithium acetoacetate 8490-6360 cm ⁻¹ , 6040-5610 c
m ^-1 , 5430-5300 cm ^-1 , 4900-4760
cm ^-1, 4680~4510cm ^-1 or 4470-43
Choose from 20 cm ^-1 and 72 for ascorbic acid
70-6520 cm ^-1 , 6430-5290 cm ^-1 , 4
950-4860 cm ^-1 or 4810-4090 cm ^-1
9370-587 for creatinine
0 cm- ¹ , 5810-5280 cm ^{- 1} , 4980-47
30cm ^-1, 4690~4320cm ^-1 or 4290～
4090 cm ^-1 , selected from sodium chloride 7640-5280 cm ^-1 or 4980-4080 cm
^-1 selected, 8680 ~ for sodium nitrite
5300 cm ^-1 , 4980-4210 cm ^-1 or 416
Select from ⁰ to 4100 cm ^-1 .

[0010]

When the sample is irradiated with light and the absorbance is measured, the transmitted light intensity Itj at the wavelength j is expressed by the following equation according to the LAMBERT-BEER law. Itj = Ioj exp (-Σαkj Ck L) = Ioj Tj (1) where Itj is the transmitted light intensity at the wavelength j and Ioj is the wavelength j.
Intensity of incident light at, αkj is the extinction coefficient of the k component at wavelength j, Ck is the concentration of the k component in the solution, k = 1, 2, ... K
Where K is the number of components in the solution, Tj is the transmittance at the wavelength j, and L
Is the cell length. The absorbance Aj at the wavelength j is represented by Aj = -log Tj = -log (Itj / Ioj) = L.SIGMA. (. Alpha.kj Ck) (2), ignoring the reflection at the interface between the cell and the solution.

From equation (2), the unknown variable is Ck (k = 1,
2, ... K), it is possible to calculate the concentration of each component by measuring the absorbance at K independent wavelengths and solving the simultaneous equations. The concentration can be obtained with higher accuracy by performing data analysis using a multivariate regression analysis method such as a principal component regression analysis method (PCR method) or a partial least squares method (PLS method).

In the multivariate regression analysis method, since regression analysis can be performed using a large amount of absorbance information at one time, quantitative analysis can be performed with higher accuracy than single regression analysis. The multiple regression analysis is most frequently used, but a large number of samples are required, and when the correlation between the absorbance values at each wavelength is high, the accuracy of the quantitative analysis becomes very low. On the other hand, the principal component regression analysis method, which is a multivariate regression analysis method, can aggregate the multi-wavelength absorbance information into principal components that are uncorrelated with each other, and can also eliminate unnecessary noise data, thus achieving high quantification. Analytical accuracy can be obtained. Further, since the partial least squares method can also use the data of the sample concentration when extracting the main component, it is possible to obtain a high quantitative analysis accuracy as in the principal component regression analysis method.

[0013]

DESCRIPTION OF THE PREFERRED EMBODIMENTS FIG. 1 shows the outline of a measuring device used in the present invention. The sample setting unit 2 has a cell in which a urine sample is placed. Whether or not the sample is contained in the cell is monitored by the optical monitoring mechanism 4. The monitoring mechanism 4 is controlled by the computer 6.

The light source section 8 is provided with a laser diode array for generating laser light of a wavelength to be measured, a laser device having a variable oscillation wavelength, a lamp light source for generating light of continuous wavelength, and the like. A drive unit 10 is provided to switch the wavelength of the light source unit 8. The drive unit 10 is also controlled by the computer 6.

In order to detect the measuring light transmitted through the sample in the sample setting section 2, a detecting section 12 is provided, and the detecting section 1 is provided.
2 is an array light receiving element composed of CCD as a detector,
A light receiving element array or a single light receiving element is provided. The signal detected by the detector 12 is converted into absorbance by the signal processing interface 14, and is taken into the computer 6 as a digital signal.

When a variable wavelength laser device or a continuous wavelength lamp is used as the light source in the light source section 8, there is only one optical path from the light source, so an optical system for mixing the light is not necessary, but a plurality of optical systems are required. When using the laser diode of, in order to arrange the measuring light of the selected wavelength in the measuring optical path,
The light source unit 8 requires an optical system as shown in FIG. FIG. 2A shows a moving mirror type optical system. With respect to the plurality of laser diodes LD _{1 to} LDm that generate laser beams having different wavelengths λ _{1 to} λm, mirrors 16-1 to 16-m are provided to reflect the respective laser beams and advance them on a common optical axis 18. Each of the mirrors 16-1 to 16-m is arranged so as to be movable between a position on the optical axis 18 and a position deviated from the position. By placing only the mirror corresponding to the laser beam of the selected wavelength on the optical axis 18 and removing the other mirrors from the optical axis, the selected laser beam is advanced on the optical axis 18.

FIG. 2B shows a method using a diffraction grating 19 as another method of advancing the laser beams from the laser diodes of a plurality of wavelengths onto the optical axis 18. Each wavelength λ _{1 to} λ
The diffracted light of the m laser beam is incident on the diffraction grating 19 at an incident angle corresponding to each wavelength so that the diffracted light is on the common optical axis 18.

The cell used in the sample setting section 2 is shown in FIG.
The optical path length as shown in (A) is not limited to one type of cell 62, and may have different optical path lengths continuously or stepwise. An example of a cell having such a plurality of optical path lengths is shown in FIGS. 3B and 3C. The cell 64 of FIG. 3B has four types of optical path lengths L _{1 to} L ₄ ,
The cell 66 of (C) has an optical path length that continuously changes. It has been found by the present inventors that the light quantity measurement sensitivity depends on the optical path length and the wavelength (Japanese Patent Application No. 5-1741).
56). When measuring multiple urinary components, the measurement wavelength is selected according to each component.
When the cell of (C) is used, it is possible to select the optical path length with the highest light quantity measurement sensitivity according to the measurement wavelength. Figure 3
When the measurement is performed using the cells of (B) and (C), the luminous flux cross-sectional area of the measurement light of the selected wavelength from the light source is enlarged by the optical system and incident on the cell as parallel light 68 having a wide cross-sectional area. Then, a plurality of measurement lights that have transmitted different optical path lengths may be simultaneously detected by an array detector such as a CCD array. After that, the component concentration is calculated by using the detection signal of the optical path length most suitable for the measurement wavelength corresponding to the component to be measured, so that the measurement with a large S / N ratio can be performed.

Various detectors as shown in FIG. 4 can be used as the detector in the detector 12. (A) is an array-shaped detection element 70 composed of a CCD, (B) is a light-receiving element array 74 in which light-receiving elements 72 such as photodiodes are arranged in an array, and (C) is a single light-receiving element 76.

When a lamp light source that generates a continuous wavelength is used as the light source of the light source section 8, it is necessary to perform spectral analysis for each wavelength selected for each urinary component before entering the sample or after passing through the sample. is there. FIG. 5 shows an example of the spectroscopic unit. FIG. 5A shows a filter switching mechanism 20 in which a plurality of filters are arranged on the circumference, and the wavelength is selected by switching the filters. In B), the wavelength is selected using the spectroscope 22.

FIG. 6 shows an example in which a wavelength tunable laser is used as a light source. Variable wavelength laser device 24
The laser light from the laser beam is collimated by the condensing lenses 26 and 28 into the spatially parallel light 3
0 is made incident on the cell 32 of the sample setting unit 2, and the measurement light transmitted through the cell 32 is detected by the single light receiving element 34.

To measure with the measuring device of FIG. 6, the wavelength of the laser beam generated from the laser 24 is changed from j = 1 to n while the cell 32 is in an empty state, and the transmitted light amount Ioj ( Measure j = 1, 2, ... N). Next, a urine sample is put into the cell 32, the wavelength of the laser beam generated from the laser 24 is changed from j = 1 to n, and the transmitted light intensity Itj (j) at each wavelength transmitted through the cell 32 is changed.
= 1, 2, ... N) is measured. Data analysis is performed based on these Ioj and Itj, and each component concentration Ck (k = 1, 2, ...
… K) is calculated.

FIG. 7 shows a measuring device in the case where a lamp light source 40 which generates continuous light in a wide wavelength range is used as a light source. Light from the lamp light source 40 is passed through the lens 42
Is transmitted through the filter of the wavelength selection mechanism 20 as spatially parallel light. The measurement light of which wavelength is selected after passing through the filter is incident on the cell 44 of the sample installation portion, and the light passing through the cell 44 is received by the single light receiving element 46.

In the measuring apparatus of FIG. 7, first, the wavelength selection mechanism 20 is rotated with the cell 44 emptied to change the wavelength of the measurement light incident on the cell 44 from j = 1 to n. The incident light intensity Ioj of is measured. afterwards,
A urine sample is put in the cell 32, and the wavelength selection mechanism 20 is similarly rotated to change the wavelength of the measurement light from j = 1 to n, and the transmitted light intensity Itj at each wavelength transmitted through the cell 44 is measured. Data analysis is performed on the basis of these Ioj and Itj to obtain each component concentration Ck (k = 1, 2, ... K).

FIG. 8 shows an example in which a lamp light source 40 for generating light in a wide wavelength range is used as in FIG. 7, but in FIG. 8 an optical system in which the measuring light is dispersed by a spectroscope after passing through the cell 44. It is an example of a system. The measurement light, which is made into the spatially parallel light by the lens 42, is incident on the cell 44, and the transmitted light of the cell 44 is the spectroscope 4
It is separated by 8 and guided to the light receiving element.

In the case of FIG. 8 as well, in the measurement, first, the cell 44 is emptied and dispersed by the spectroscope 48 from the wavelengths j = 1 to n to measure Ioj. Itj is measured by changing the wavelength from j = 1 to n by the spectroscope 48. Then, data analysis is performed based on Ioj and Itj to obtain each component concentration Ck (k = 1, 2, ... K).

The results of individually measuring some components contained in urine are shown below. 9 to 11 show the measurement results of the glucose aqueous solution. FIG. 9 shows spectra of a plurality of samples having different concentrations.
The area around m ^-1 where the indication is shaken off is the water absorption area. Since a plurality of substances having different concentrations are measured, a plurality of spectra are displayed in an overlapping manner. The result of obtaining the wavelength distribution chart of the correlation coefficient (absorbance-concentration) from this spectrum is shown in FIG. The spectrum of Figure 9 is
The spectrum is corrected on the basis of the absorbance values in the reference wavelength regions having a correlation coefficient of 0.1 or less.

When glucose is included in the measurement components of the urine sample, the wavelength region in which the absolute value of the correlation coefficient is 0.5 or more is set as the measurement wavelength region. From FIG. 10, when expressed in wave numbers, the measurement wavelengths are 11380 to 9720 cm ⁻¹ , 9430 to 94.
00 cm ^-1 , 9340-9320 cm ^-1 , 9260-6
560 cm ^-1 , 6510-5540 cm ^-1 , 5530-
5280 cm ^-1 , 4980-4850 cm ^-1 , 4830
~ 4480 cm ^-1 , 4440-4330 cm ^-1 or 43
It is preferable to select from 00 to 4010 cm ^-1 .

FIG. 11 is a calibration curve showing the relationship between glucose concentration and absorbance measured at 4398 cm ^-1 . From this result, it can be seen that quantitative analysis is possible by using a wavelength range having a large correlation coefficient. The slope of the straight line in FIG. 11 is obtained by the least squares method, and the slope of the straight line is the absorption coefficient αjk of the equation (1).

FIGS. 12 to 15 show the results of measurement of hemoglobin in the same manner. 12 to 13 are spectra of various concentrations of the hemoglobin aqueous solution, FIG. 14 is a wavelength distribution chart of the correlation coefficient (absorbance-concentration), and FIG. 15 is a calibration curve at 10500 cm ⁻¹ . From FIG. 14, the measurement wavelength is 2500 for hemoglobin.
0-7250 cm ^-1 , 7220-6430 cm ^-1 , 61
It is preferable to select from 90 to 5690 cm ^-1 , 5660 to 5280 cm ^-1 or 4900 to 4080 cm ^-1 .

16 to 18 show the results of measurement of albumin in the same manner. FIG. 16 is a spectrum of various concentrations of the albumin aqueous solution, FIG. 17 is a wavelength distribution chart of its correlation coefficient (absorbance-concentration), and FIG. 18 is 4371 cm.
^It shows the calibration curve at ^-1 . 177, etc., the measurement wavelength is 7280-6350c for albumin.
m ^-1 , 5910-5880 cm ^-1 , 5790-5740
cm ^-1, 5630~5300cm ^-1, 4900~472
0cm ^-1, 4670~4280cm ^-1 or 4230-4
It is preferable to select from 070 cm ^-1 .

FIGS. 19 to 21 show the results of the same measurement for lithium acetoacetate. FIG. 19 shows spectra of various concentrations of the aqueous lithium acetoacetate solution, and FIG.
Is a wavelength distribution chart of the correlation coefficient (absorbance-concentration), FIG.
Represents the calibration curve at 5780 cm ^-1 . From FIG. 20, the measurement wavelength is 8 for lithium acetoacetate.
490 to 6360 cm ^-1 , 6040 to 5610 cm ^-1 ,
5430-5300 cm ^-1 , 4900-4760c
m ^-1 , 4680-4510 cm ^-1 or 4470-432
It is preferable to select from 0 cm ^-1 .

22 to 24 show the results of the same measurement for ascorbic acid. 22 is a spectrum of various concentrations of the ascorbic acid aqueous solution, FIG. 23 is a wavelength distribution chart of its correlation coefficient (absorbance-concentration), and FIG. 24 is 440.
It shows a calibration curve at 4 cm ^-1 . From FIG. 23, the measurement wavelength is 7270 to 6 for ascorbic acid.
520cm ^-1, 6430~5290cm ^-1, 4950~
It is preferably selected from 4860 cm ⁻¹ or 4810 to 4090 cm ⁻¹ .

FIG. 25 to FIG. 27 show the results of similar measurement for creatinine. FIG. 25 shows spectra of various concentrations of the creatinine aqueous solution, FIG. 26 shows a correlation coefficient between the absorbance and the concentration, and FIG. 27 shows a calibration curve at 4370 cm ⁻¹ . From FIG. 26, the measurement wavelengths for creatinine are 9370-5870 cm ⁻¹ and 581.
0-5280 cm ^-1 , 4980-4730 cm ^-1 , 46
It is preferable to select from 90 to 4320 cm ^-1 or 4290 to 4090 cm ^-1 .

28 to 30 show the results of the same measurement for sodium chloride. 28 shows spectra of various concentrations of the aqueous sodium chloride solution, FIG. 29 shows a correlation coefficient between the absorbance and the concentration, and FIG. 30 shows a calibration curve at 6645 cm ⁻¹ . From Figure 29, the measurement wavelength for sodium chloride is preferably selected from 7640～5280Cm ^-1 or 4980~4080cm ^-1.

31 to 33 show the results of the same measurement for sodium nitrite. FIG. 31 is a spectrum of various concentrations of the sodium nitrite aqueous solution, FIG. 32 is a correlation coefficient between the absorbance and the concentration, and FIG. 33 is 6766 cm ^−1.
It shows the calibration curve in. From FIG. 32, the measurement wavelength is 8680 to 5300c for sodium nitrite.
m ^-1 , 4980-4210 cm ^-1 or 4160-410
It is preferable to select from 0 cm ^-1 .

[0037]

INDUSTRIAL APPLICABILITY In the present invention, a urine sample is irradiated with visible light or near-infrared light, and the absolute value of the correlation coefficient between the concentration and the absorbance of each of a plurality of urinary components to be measured is 0. Since the absorbance was measured by selecting a wavelength of 0.5 or more, preferably 0.9 or more as a measurement wavelength, and multiple urinary components were quantitatively analyzed simultaneously by the multivariate regression method, the multicomponents of the urine sample were analyzed. At the same time, quantitative measurement is possible, consumables such as reagents and test strips are not required, and there is no problem of disposal of such consumables after use.

[Brief description of drawings]

FIG. 1 is a block diagram showing an outline of a measuring device used in the present invention.

FIG. 2 is a schematic configuration diagram showing an optical system in which a plurality of light beams are placed on a single optical axis in a light source section, FIG.
(B) represents an optical grating system.

FIG. 3 is a diagram showing an example of a cell used in the present invention,
(A) is a schematic front view of a cell having a single optical path length, and (B) is 4
FIG. 3C is a schematic plan view of a cell having one optical path length, and FIG. 3C is a schematic plan view of a cell having a continuously changing optical path length.

FIG. 4 is a schematic plan view showing an example of a detector in a detection unit, (A) is an array-shaped light receiving element composed of a CCD, and (B) is a diagram.
Represents a light receiving element array in which light receiving elements such as photodiodes are arranged in an array, and (C) represents a single light receiving element.

5A and 5B are diagrams showing an example of a spectroscopic unit, FIG. 5A showing an example using a filter, and FIG. 5B showing an example using a spectroscope.

FIG. 6 is a schematic configuration diagram showing a measuring device using a wavelength tunable laser as a light source.

FIG. 7 is a schematic configuration diagram showing a measuring device that uses a lamp that generates continuous-wavelength light as a light source and performs pre-spectroscopy with a filter.

FIG. 8 is a schematic configuration diagram showing a measuring device that uses a lamp that generates continuous-wavelength light as a light source and performs post-splitting by a spectroscope.

FIG. 9 is a diagram showing spectra of a plurality of samples having different glucose aqueous solution concentrations.

FIG. 10 is a diagram showing a correlation coefficient between the absorbance and the concentration of an aqueous glucose solution.

FIG. 11 is a diagram of a calibration curve showing the relationship between the concentration of a glucose aqueous solution at 4398 cm ⁻¹ and the absorbance.

FIG. 12 is a diagram showing spectra of a plurality of samples having different hemoglobin aqueous solution concentrations.

FIG. 13 is a diagram showing spectra of a plurality of samples having different concentrations of an aqueous hemoglobin solution.

FIG. 14 is a diagram showing a wavelength distribution chart of a correlation coefficient (absorbance-concentration) of an aqueous hemoglobin solution.

FIG. 15 is a diagram of a calibration curve showing the relationship between the concentration of a hemoglobin aqueous solution at 10500 cm ⁻¹ and the absorbance.

FIG. 16 is a diagram showing spectra of a plurality of samples having different concentrations of an albumin aqueous solution.

FIG. 17 is a diagram showing a wavelength distribution chart of a correlation coefficient (absorbance-concentration) of an aqueous albumin solution.

FIG. 18 is a diagram of a calibration curve showing the relationship between the concentration of an albumin aqueous solution at 4371 cm ⁻¹ and the absorbance.

FIG. 19 is a diagram showing spectra of a plurality of samples having different concentrations of a lithium acetoacetate aqueous solution.

FIG. 20 is a diagram showing a wavelength distribution chart of a correlation coefficient (absorbance-concentration) of a lithium acetoacetate aqueous solution.

FIG. 21: 5780 cm ^{−1 of} lithium acetoacetate aqueous solution
It is a figure of the calibration curve showing the relationship of the density | concentration and the light absorbency in FIG.

FIG. 22 is a diagram showing spectra of a plurality of samples having different concentrations of an ascorbic acid aqueous solution.

FIG. 23: Correlation coefficient of ascorbic acid aqueous solution (absorbance-
It is a figure which shows the wavelength distribution chart of (density).

FIG. 24 is a diagram of a calibration curve showing the relationship between the concentration of an ascorbic acid aqueous solution at 4404 cm ⁻¹ and the absorbance.

FIG. 25 is a diagram showing spectra of a plurality of samples having different creatinine aqueous solution concentrations.

FIG. 26 is a diagram showing a wavelength distribution chart of a correlation coefficient (absorbance-concentration) of a creatinine aqueous solution.

FIG. 27 is a diagram of a calibration curve showing the relationship between the concentration of creatinine aqueous solution at 4370 cm ⁻¹ and the absorbance.

FIG. 28 is a diagram showing spectra of a plurality of samples having different concentrations of an aqueous sodium chloride solution.

FIG. 29: Correlation coefficient of sodium chloride aqueous solution (absorbance-
It is a figure which shows the wavelength distribution chart of (density).

FIG. 30 is a diagram of a calibration curve showing the relationship between the concentration of sodium chloride aqueous solution at 6645 cm ⁻¹ and the absorbance.

FIG. 31 is a diagram showing spectra of a plurality of samples having different concentrations of an aqueous sodium nitrite solution.

FIG. 32 is a diagram showing a wavelength distribution chart of a correlation coefficient (absorbance-concentration) of an aqueous sodium nitrite solution.

FIG. 33 is a calibration curve diagram showing the relationship between the concentration of an aqueous sodium nitrite solution at 6766 cm ⁻¹ and the absorbance.

[Explanation of symbols]

 2 sample setting unit 4 monitoring mechanism 6 computer 8 light source unit 10 driving unit 12 detection unit 14 signal processing interface

 ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Kakin Xu 57, Higashikujo Nishi-Amita-cho, Minami-ku, Kyoto-shi, Kyoto 57 Kyoto Daiichi Kagaku Co., Ltd. (72) Hiroko Kubo Higashi-kujo, Minami-ku, Kyoto-shi, Kyoto 57 Nishi-Amita-cho Kyoto Daiichi Science Co., Ltd.

Claims (3)

[Claims] 1. The absolute value of the correlation coefficient between the concentration and the absorbance in the visible or near-infrared wavelength region of the single component aqueous solution of each urinary component to be measured is 0.5 or more, preferably A wavelength of 0.9 or more is selected as a measurement wavelength peculiar to the component, and a urine sample is irradiated with visible light or near-infrared light, and each of a plurality of urinary components to be measured is selected under the above conditions. Measuring the absorbance at the measurement wavelength, and quantitatively analyzing the plurality of urinary components simultaneously by a multivariate regression analysis method. 2. The measurement wavelength of each urinary component avoids a wavelength region having strong absorption for water and has a high transmittance for water of 25,000 to 5280 cm ⁻¹ or 4980 to 400.
The measuring method according to claim 1, wherein the measuring method is selected from a wave number region of 0 cm ^-1 . 3. The urine component to be measured contains a plurality of glucose, hemoglobin, albumin, lithium acetoacetate, ascorbic acid, creatinine, sodium chloride and sodium nitrite, and the measurement wavelength of each component is wavenumber. In terms of glucose, 11380-9720 cm ^-1 , 9
430-9400 cm ^-1 , 9340-9320 cm ^-1 ,
9260-6560 cm ^-1 , 6510-5540c
m ^-1 , 5530-5280 cm ^-1 , 4980-4850
cm ^-1, 4830~4480cm ^-1, 4440~433
Select from 0 cm ^-1 or 4300~4010cm ^-1, for the hemoglobin 25000~7250cm ^-1,
7220-6430 cm ^-1 , 6190-5690c
m ^-1 , 5660-5280 cm ^-1 or 4900-408
It is selected from 0 cm ^-1 and for albumin 7280-6350 cm ^-1 , 59
10-5880 cm ^-1 , 5790-5740 cm ^-1 , 5
630-5300 cm ^-1 , 4900-4720 cm ^-1 ,
4670-4280 cm ^-1 or 4230-4070 cm
^-1 selected, 8490-6360 cm for lithium acetoacetate
^-1 , 6040-5610 cm ^-1 , 5430-5300c
m ^-1 , 4900-4760 cm ^-1 , 4680-4510
cm ^-1 or selected from 4470~4320cm ^-1, 7270~6520cm ^-1 for ascorbic acid,
6430-5290 cm ^-1 , 4950-4860 cm ^-1
Or 4810-4090 cm ^-1 , and for creatinine 9370-5870 cm ^-1 , 5
810 to 5280 cm ^-1 , 4980 to 4730 cm ^-1 ,
4690-4320 cm ^-1 or 4290-4090 cm
Select ^-1 for sodium chloride selected from 7640～5280Cm ^-1 or 4980～4080Cm ^-1, relative to the sodium nitrite 8680~5300c
m ^-1 , 4980-4210 cm ^-1 or 4160-410
The measuring method according to claim 2, wherein the measuring method is selected from 0 cm ^-1 .