KR100943095B1 - The apparatus and method for real time analyzing components of urine in toilet by using minature atr infrared spectroscopy - Google Patents

Abstract

The present invention relates to a small urine component analyzer for toilet and real-time urine component analysis method using the same for measuring and analyzing the urine in the toilet in real time. More specifically, the toilet seat; A urine collecting portion formed on the inner surface of the toilet bowl in a concave shape or a flat shape; An analyzer configured to analyze the components of urine collected from the urine collection unit and directly attached to the toilet seat, and comprising a light source unit, a composite filter, a reflector, and a detector; And an attenuation prism (ATR) further provided in the analysis unit for analyzing urine components. Including, but in order to keep the signal-to-noise ratio (SN ratio) as high as possible the shape of the light emitting surface perpendicular to the light path and the light receiving surface shape of the light receiving portion of the detector corresponding to the shape similar to each other small urine components for the toilet It is to provide an analysis device. It also provides a real-time analysis method using the urine component analysis device.

Toilet, urine component, ATR, high SN ratio, small urine component analyzer, real-time urine component analysis method, infrared spectrometer, health diagnosis system

Description

Small urine component analyzer for toilet and real-time urine component analysis method using the same {THE APPARATUS AND METHOD FOR REAL TIME ANALYZING COMPONENTS OF URINE IN TOILET BY USING MINATURE ATR INFRARED SPECTROSCOPY}

The present invention relates to a urine component analysis device and method for measuring the concentration of the components contained in the urine, and more particularly, Attenuated Total Reflectance infrared spectroscopy (hereinafter referred to as "ATR-IR") It relates to a small urine component analysis device for measuring in real time the concentration of the components contained in the urine and the like and a real-time analysis method using the same.

The present invention relates to a device and method for real-time measurement and analysis of urine in a toilet. More specifically, the development of a compact infrared spectrometer and urine sample that can be used in a special environment such as a conventional infrared spectrometer Attenuated Total Reflectance (ATR), which can be collected and reproducibly measured, provides a method for effectively attaching a small infrared spectrometer including ATR to a toilet and a cleaning method. In addition, using the ATR IR miniature spectrometer attached to the toilet, urine components such as glucose (glucose), creatine (creatine), urea (protein), urea (protein), albumin, PH, trigloside, cholesterol (Cholesterol) It provides an effective algorithm for measuring and analyzing bilirubin, uric acid and nitrite.

In general, methods for testing urine components using visible light are mainly used. In the visible region, three wavelengths are used to analyze components contained in urine, and a method of testing using urine test paper is mainly used. In this method, since the disposable urine test sheet should be used continuously, the general public must frequently purchase a separate test sheet to measure the components of urine, and the method of measuring urine and the method of measuring urine on the test sheet are very inconvenient. In addition, urine test strips and equipment have to be kept at home, such as difficult to be distributed to the public.

Spectroscopic analysis is used as a method of not using a urine test paper, and infrared spectroscopy can effectively analyze various components in urine. However, there is no case of attaching the infrared spectrometer to the toilet because the existing infrared spectrometer is very large and cannot be attached directly to the toilet. When miniaturizing the infrared spectrometer, signal / noise ratio (Signal / Noise, In the urine sample, glucose (Glucose), creatine (Creatine), urea (Urea), protein, albumin, PH, trigloside, cholesterol (Cholesterol) and bilirubin (Bilirubin) ), Uric acid and nitrite cannot be analyzed effectively. In addition, in order to apply to the toilet, it is necessary to have an automatic washing device because a person cannot wash after measuring a sample every time as in a laboratory. Also, in the infrared region, a mixed component cannot be effectively measured due to the influence of moisture.

As another spectroscopic method applied to the toilet, a separate introduction apparatus for introducing a sample from the toilet is used to introduce a sample, and the analyzer, light source, and detector of the introduced sample are arranged side by side (180 degrees). It is constructed in a transmissive manner. In the case of this mode, additional equipment is added, in particular the light used in this mode corresponds to near infrared. The wavelength band used in this near infrared analyzer is 800 nm to 2,500 nm. The light of the wavelength band is suitable for the analysis of a single component of the components contained in the urine, but when analyzing the components of the plurality of components contained in the urine, the measurement values for the plurality of components overlap, There is a problem in analyzing urine components. As a result of such a problem, a device and method for analyzing a plurality of components contained in urine more conveniently and more precisely have not been provided until now.

In addition, there is no device for convenient measurement of blood pressure and body fat as well as analysis of urine as a result of sitting on the toilet, so users or patients have to measure urine, blood pressure and body fat at different times at different times. There is a problem.

In order to solve the above problems, the present invention provides a small spectrometer applying a mid-infrared wavelength of 2,500 to 15,000nm to have a maximum SN ratio for applying to the toilet, urine sample in a special environment called toilet An apparatus and a method for easily receiving and measuring and maintaining reproducibility are provided. In addition, the purpose of the present invention is to provide an algorithm for measuring, analyzing, and quantifying urine in a toilet equipped with a spectroscope, and to provide a device and a real-time analysis method for easily analyzing urine in a toilet.

In addition, an object of the present invention is to provide a health diagnosis system capable of measuring blood pressure, body fat, and the like almost simultaneously with urine component analysis.

In order to achieve the above object, the present invention is a toilet; A urine collecting portion formed on the inner surface of the toilet bowl in a concave shape or a flat shape; An analysis unit analyzing a component of urine collected from the collection unit and directly attached to the toilet, including an at least one of a light source unit, a composite filter, a reflector, and a detector; And an ATR further provided in the analysis unit for analyzing urine components. To include, but in order to minimize the light loss and to maintain the signal-to-noise ratio (SN ratio) as high as possible, the shape of the light emitting surface perpendicular to the light path and the light receiving surface shape of the light receiving portion of the detector correspond to each other in a similar shape. It is characterized by providing a small urine component analysis device for the toilet.

The light source unit used in the present invention uses mid-infrared rays having a wavelength range of 2,500 to 15,000 nm, and the analysis unit of the present invention includes a shape of the light emitting surface of the light source unit in which the cross-sectional shape of the transmission unit perpendicular to the optical path is perpendicular to the optical path, and the light receiving unit of the detector. Corresponding to the shape of the light receiving surface and similar to each other.

Here, the total trajectory distance from the light source until the light reaches the detector through the prism is in the range of about 10 to 30 mm, and when the mirror tunnel or taper rod is provided between the prism and the detector, the total trajectory distance is about 10 to It is preferable that it is the range of 50 mm.

At this time, the spacing between the light source and the prism is 300㎛ ~ 5mm, the spacing between the prism and the detector is characterized in that 300㎛ ~ 5mm.

Meanwhile, in the present invention, the light source unit has an array structure in which a plurality of small light sources are arranged side by side to form a single layer, and the array structure of the light source unit includes a pulse waveform of the light source reaching the light receiving unit of the light source generated from the light source unit and the detector. It may consist of two or more layers to match this. In the present invention, the light source unit is any one of a triangular prism shape, a circular shape, or a rectangular rectangle, wherein the light transmitting part of the prism and the analysis part is similar to the shape of the light emitting surface of the light source part 751 perpendicular to the optical path. .

In addition, the analysis unit in the present invention may include a tapered rod or mirror tunnel to guide the light passing through the prism to the detector.

On the other hand, the urine component that can be analyzed in the urine component analyzer of the present invention is glucose (Glucose), creatine (Creatine), urea (Urea), protein, albumin, PH, trigloseide, cholesterol (Cholesterol), bilirubin (Bilirubin) ), Uric acid (Uric acid), nitrite (Nitrite) is characterized in that any one.

In addition, the analysis device of the present invention may be configured to further comprise at least one or more of the blood pressure measuring device, body fat measuring device, and electrocardiogram measuring device, in which case the analysis device is operated after the user is authenticated by the fingerprint recognition device It is characterized by.

The present invention provides an analysis method using the urine component analysis device, comprising: measuring a spectrum of a reference substance introduced through a urine collection unit of a toilet using an analysis unit ATR; Measuring an absorption spectrum of urine introduced through the urine collecting unit using an ATR of an analyzing unit; Obtaining a calibration curve indicating a correlation between a standard value of each component of urine measured in advance and an absorption spectrum; And estimating the amount of each component included in the urine using the calibration curve. Including, but in order to keep the signal-to-noise ratio (SN ratio) as high as possible, the shape of the light emitting surface perpendicular to the light path and the light receiving surface shape of the light receiving portion of the detector correspond to each other in a similar shape to each other Provide a method.

Herein, the spectrum of the reference material and the absorption spectrum of urine are measured using mid-infrared rays in the wavelength range of 2,500 to 15,000 nm introduced into the ATR.

At this time, the prism preferably corresponds to the shape of the cross section of the transmissive portion perpendicular to the optical path similar to the shape of the light emitting surface of the light source portion perpendicular to the optical path and the shape of the light receiving surface of the light receiving portion of the detector.

Meanwhile, the reference substance is water, air, or a combination thereof according to the urine component to be measured, and the urine component is glucose, creatine, urea, protein, albumin, and PH. It is characterized in that any one of, trigloside, cholesterol (Cholesterol), bilirubin (Bilirubin), uric acid (Uric acid), nitrite (Nitrite).

The urine component analysis method further includes the step of washing the urine collection unit using a washing solution after measuring the absorption spectrum of the urine, the washing solution and the reference material may be the same. In addition, the urine component analysis method may further comprise the step of drying the urine collecting portion using the air injection port formed in a position higher than the urine collecting portion.

In addition, in order to achieve the above object, the present invention comprises a toilet for bidet installed on the rear of the toilet and a body fat measurement device formed in combination with the toilet, wherein the body fat measurement device is the left side of the toilet And a handle installed on the right side; And eight electrodes each provided in pairs at four contacts, two of which are located at a portion of the upper surface of the toilet seat in contact with a user's hip or thigh, and the other two contacts are disposed at the handle. It provides a medical examination system, characterized in that located in.

Each of the contacts includes a voltage electrode and a current electrode, and the handle is installed in a recessed shape in the toilet and is characterized in that it comprises a cover for preventing water from getting on the handle.

The health diagnosis system further includes a urine component analyzer for measuring the components contained in the urine using ATR, wherein the ATR is characterized in that attached directly to the toilet.

In addition, to achieve the above object, the present invention is a toilet bidet installed on the rear side of the toilet; A weight measuring device for measuring a weight of a user using a plurality of load cells installed under the toilet seat of the toilet bowl; And urine component analyzer for measuring the components contained in the urine using the ATR; Including, but the ATR provides a health diagnostic system, characterized in that attached directly to the toilet.

The health diagnosis system includes a blood pressure measuring device capable of measuring the blood pressure of the user; And a fingerprint recognition device for identifying the user of the urine component analyzing device through fingerprint recognition, wherein the blood pressure measuring device and the fingerprint recognition device are located in an arm support unit on which the user's arm can be placed. The fingerprint recognition and blood pressure measurement may be simultaneously performed using the fingerprint recognition device and the blood pressure measurement device while sitting on the toilet.

The health diagnosis system includes urine component information measured by the urine component analyzer, weight information measured by the weight measuring device, fingerprint information measured by the fingerprint recognition device, blood pressure information measured by the blood pressure measuring device, and body fat measurement. A monitor for displaying at least one of the body fat information measured by the device, characterized in that the monitor is located in the arm support.

The health diagnosis system further includes a drug injection device for supplying a drug used in the health diagnosis system, the drug injection device is installed in an oblique direction behind the toilet, the drug injection device is connected to the toilet bidet It is characterized by.

The health diagnosis system may transmit at least one of the urine component information, weight information, fingerprint information, blood pressure information, and body fat information using the Internet or Ethernet.

In addition, in order to achieve the above object, the present invention comprises a toilet bidet installed in the rear of the toilet and an electrocardiogram measuring device is formed in combination with the toilet, wherein the ECG measuring device is the left of the toilet Two contacts located at the right / handle; And two contacts positioned at a portion of the upper surface of the toilet seat in contact with a user's hip or thigh, wherein each contact has two electrodes, and the ECG measuring device is connected to the four contacts. The present invention provides a health diagnosis system, which measures an electrocardiogram of a user by measuring an electric potential difference between each electrode by flowing an induced current using eight electrodes located.

The small urine component analysis device for a toilet according to the present invention and a real-time urine component analysis method using the same have a unique configuration in order to minimize light loss and maintain the signal-to-noise ratio (SN ratio), which is the core of spectral analysis, as high as possible, It can be installed in a narrow space of special environment, and it is effective to measure all the components of a plurality of urine test items at the same time precisely and in real time.

In particular, the present invention is configured such that the surface shapes perpendicular to the optical path are similar to each other in the shape of the light emitting surface of the light source portion, the light transmitting portion of the prism, and the light receiving surface of the detector, which are the main components of the spectroscopic analysis, so that the overall configuration is reduced in size and light. By minimizing the loss and increasing the light intensity, it increases the sensory activity and shows the reliable spectroscopic effect.

In addition, the present invention provides a health diagnosis system that conveniently measures the blood pressure, body fat, as well as the analysis of urine components through a simple action sitting on the toilet, the user or inspector periodically convenient to check urine components, blood pressure, body fat, etc. There is an effect that can be measured.

The terminology used in the present invention is a general term that is currently widely used as possible, but in certain cases, the term is arbitrarily selected by the applicant, in which case the meaning of the term is described in the detailed description of the invention. It should be understood that the present invention in terms of terms other than these terms.

Hereinafter, with reference to the accompanying drawings a preferred embodiment of the present invention that can specifically realize the above object, the present invention is not limited or limited by the above embodiments.

1A is a perspective view illustrating a medical diagnosis system including a urine component analyzing apparatus 700 according to an embodiment of the present invention. Referring to FIG. 1A, the health diagnosis system includes a blood pressure measuring device 100, a bidet control device 200, a fingerprint recognition device 300, a monitor 400, a main control device 500, and a body fat measuring device 600. , Urine component analysis device 700, drug injection device 800 and weight measuring device 900.

In FIG. 1A, the blood pressure measuring device 100 has a rectangular parallelepiped shape or an open cuff shape, and is illustrated as being located on the upper surface of the arm support part 1000. It is not limited to position.

In addition, the health diagnosis system may measure body weight using the weight measuring apparatus 900 and body fat using the body fat measuring apparatus 600.

Meanwhile, FIGS. 1B to 1D are perspective views of various models showing a health diagnosis system including a urine component analyzing apparatus 700 according to another embodiment of the present invention.

Body fat measurement starts when a person sits on the toilet 710 and grabs the handle 609 of the body fat measuring apparatus 600 in which electrodes 601 to 608 on the left / right side of the toilet 710 are embedded. The body fat measuring device 600 is described in detail with reference to FIGS. 2A and 2B.

In detail describing a method for measuring body fat, when the "body fat measurement" button of the main control device 500 is pressed, the pressure sensor of the weight measuring device 900 operates to measure the weight. Then, pressing the "start" button, while sitting down, both arms are extended to hold the handle 609 of the body fat measurement device 600. When the body fat measurement is completed, the corresponding information such as body fat percentage and muscle mass is displayed on the monitor 400 by using the user's age, gender, height and weight measured using the weight measuring apparatus 900 previously stored. If the weight information has already been obtained, the weight measurement process may be omitted.

The monitor 400 may protrude in a manner of rotating in a horizontal direction about one axis fixed from a lower surface of the arm support part 1000. After protruding, the monitor 400 may be rotated in a vertical direction about another fixed axis, so that the monitor 400 may be adjusted to an inclination or an angle that is convenient for a user to see.

In addition, the health diagnosis system may measure and display sugar, protein, blood, and the like contained in urine using the urine component analyzer 700. A detailed description of the urine component analyzer 700 will be described later with reference to FIGS. 2 to 6.

In addition, the medical examination system includes a drug injection device 800 located behind the urine component analyzer 700. The chemical injection device 800 may be injected with a chemical such as a cleaning agent (for example, vaginal cleaner), a fragrance. The drug injection device 800 may be made in a form that can be accurately combined with the drug case, it may be made in a slightly oblique form can be made so that the drug can be easily lowered. Therefore, while the entirety of the medicine case is inserted into the medicine injecting device 800 and used, when all of the medicines are used, the medicine case can be removed and discarded from the medicine injecting device 800. The drug injection device 800 is connected to the bidet device, the drug injected into the drug injection device 800 is injected through the bidet device.

Figure 2a shows a body fat measurement apparatus 600 constituting a health diagnosis system according to an embodiment of the present invention. 2A, in the body fat measuring apparatus 600, four electrodes 601, 602, 603, and 604 are installed on the toilet seat 710, and two electrodes 605 on each of the handles 609. , 606, 607, and 608 are installed to measure body fat using all eight electrodes.

That is, a voltage electrode and a current electrode are respectively provided at the handles 609 on the left and right sides of the toilet 710, and further four electrodes (two voltage electrodes, Two current electrodes are provided, and two electrodes (voltage electrode and current electrode) constitute one contact point.

Figure 2b shows a handle 609 of the body fat measurement apparatus 600 according to an embodiment of the present invention. Referring to FIG. 2B, the handle 609 may be installed in a recessed shape on both sides of the toilet 710, and a cover 611 may be attached on the cover 611 to prevent water from getting wet. In addition, a slit 610 may be installed at a lower side of the cover 611 so that water introduced into the outer edge groove of the cover 611 may escape. The present invention is not limited to the shape of the cover 611 and the slit 610.

3 is an apparatus diagram of a Fourier Transform infrared spectrometer used in a general laboratory. Referring to FIG. 3, the infrared spectrometer includes a light source unit 741, a beam splitter 742, a first reflector 743, a monochromator, and a sample measuring unit 744. 745), detector 746, and the like.

When using a conventional infrared spectroscopy as shown in Figure 3, the size generally reaches 20 to 50cm, the weight is about 10kg it is practically very difficult to apply to a small space such as a toilet according to the present invention.

In general, as the light generated by the infrared light source unit moves away from the light source, the intensity decreases rapidly with a reciprocal ratio of the squared distance. In conventional large-scale FT-IR spectroscopy, the frequency is adjusted by using a chopper to prevent light spread and background noise while using a high output light source to increase the signal-to-noise ratio (SN ratio), or It must be used after a complicated process such as additional use of a monochromator or interferometer, but in the toilet 710, the chopper, a monochromator, or an interferometer may be used. Can't. For this reason, when the heat generating area of the heat sink having a single structure of the light source unit 741 is increased in order to obtain sufficient light from the miniaturized light source unit 741, the response time is long and the detector cannot detect it. In addition, when the light output is reduced to reduce the size of the heat sink, it is difficult to transmit optimal light to the ATR. For this reason, there have been attempts using infrared spectroscopy for urine component analysis, but it is not possible to obtain reliable and stable results in the mid-infrared range.

The inventors of the present invention devised to solve this problem in the configuration of the analyzer 700 that can be mounted in a narrow space, such as the toilet 710 in order to overcome the conventional technical limitations, miniaturization of the size of the analyzer 700 At the same time, a method to increase the signal-to-noise ratio (SN ratio), that is, to reduce the amount of light loss and increase the intensity of the light (intensity), to find the optimal design scheme to synchronize the frequency with the detector (755). Such an optimal design includes a technique of employing a line sensor in the light receiving portion 762 of the detector 755 that can accommodate the desired spectrum. The frequency synchronization may include a technique for controlling frequency synchronization of a signal between a light source and a detector 755 sensor in a CPU.

4A is a conceptual diagram illustrating an internal spectral analysis principle of the analysis apparatus 700 of the present invention. In the present invention, the light source unit 751 (IR Source), the ATR, the filter 761, and the light-receiving unit 762 (line sensor) of the detector 755 for minimizing the optical loss necessary for miniaturization of the analysis device 700. The shapes of the faces are similar to each other. That is, if the corresponding surface of the light source 751 where the light is generated is a rectangle having a large aspect ratio, the ATR prism 753, the mirror or tapered rod, and the filter 761 through which the generated light passes ( LVF) and the light receiving portion 762 (line sensor) of the detector 755 also have a rectangular shape.

By such a configuration, the analysis apparatus 700 of the present invention maximizes the signal-to-noise ratio, has no response time delay in the detector 755, prevents mismatch of pulse waveforms, and at the same time controls the intensity of light generated from the light source unit 751. You can increase it as much as possible. To this end, the analysis apparatus 700 of the present invention is set the material, polishing characteristics, placement angle, and the interval between each component to achieve the best performance for each component.

4B is an embodiment of an analysis apparatus 700 of the present invention. In the analyzer 700, the light source unit 751 is 13-14 mm long and 3-4 mm wide, and the ATR prism 753 is 13-14 mm long and 3-4 mm wide, and has a detector ( The light receiving portion 762 (line sensor portion) of 755 shows a configuration in which the length and width are about 12 mm and 2 mm, respectively.

That is, the concept of the above embodiment is to make the shape of the sensor of the detector 755 and the shape of the light source 751 and the prism 753 similar to each other in order to minimize the optical loss in hardware.

Here, the distance between the light source portion 751 and the prism 753 is 300 μm to 5 mm, and the distance between the prism 753 and the detector 755 has a range of 300 μm to 5 mm. The total trajectory distance until the light generated by the light source unit 751 reaches the detector 755 via the prism 753 is in the range of about 10 to 30 mm. However, when the mirror tunnel 759 or the tapered rod is provided between the prism 753 and the detector 755, the total trajectory distance is preferably in the range of about 10 to 50 mm. In general, since the intensity decreases with the inverse ratio of the square of the light source distance and has the property of spreading to the surroundings, it is preferable that the analysis apparatus mounted on the small toilet 710 like the present invention keep the light path as short as possible.

The design concept of maintaining the distance between each component in a certain range is also to optimize the SN ratio by preventing the light intensity from being attenuated by the square of the propagation distance in order to minimize the optical loss in hardware.

The present invention was able to achieve a miniaturization of the analysis device by omitting the separate drive equipment provided in the existing large-scale FT-IR equipment in such a way to keep the distance between the components or the total trajectory distance of the light source very short, toilet 710 It can be installed in a small space such as) to enable urine analysis.

5 shows the main configuration of the analysis unit 750 of the present invention. The analysis unit 750 of the present invention is a light emitting surface shape of the light source unit 751 perpendicular to the optical path, the transmissive portion of the prism 753 and the detector 755 in order to minimize the light loss and keep the signal-to-noise ratio (SN ratio) as high as possible. The light receiving surface of each of the light receiving units 762 is configured to correspond to each other in a similar shape.

5A illustrates that the light source unit 751 has a rectangular shape, and the light source generated from the light source unit 751 also has a rectangular cross section in the traveling direction, so that the light source unit 751 is incident on the prism 753 and the prism 753 also has no loss of the light source. It has a rectangular shape similarly to the cross-sectional shape of the said light source part 751. In addition, the light source incident on the prism 753 and reflected after refraction has a rectangular cross section perpendicular to the advancing direction and is finally incident on the detector 755. At this time, the light receiving unit 762 of the detector 755 is also It has a rectangular shape so that there is no loss of the light source. The light source generated from the light source unit 751 by the features of such a configuration can be efficiently used in the miniaturized analyzer 700 because the light source reaches the light receiving unit 762 via the prism 753 without loss.

FIG. 5B is a conceptual diagram illustrating a combination of circular shapes of the light source unit 751, the prism 753, and the light receiver 762 of the detector 755. 5C illustrates a combination of triangular shapes of the light source unit 751, the prism 753, and the detector light receiver 762 as another embodiment. At this time, the prism 753 is sufficient if the incidence plane and the outgoing plane are arranged to form a predetermined angle, and includes, for example, a rectangular structure having a triangular prism shape. In addition, the present invention, if the shape of the light emitting surface of the light source portion 751 perpendicular to the optical path, the transmission portion of the prism 753 and the light receiving surface of the light receiving portion 762 of the detector 755 are similar to each other, in addition to the above examples. It belongs to the category of thought.

6A and 7A are perspective views illustrating an analysis unit 750 of the urine component analyzing apparatus 700 according to the present invention. 6A and 7A, the analysis unit 750 includes a light source unit 751, a reflector 752, a prism 753, a light guide 754, a detector 755, and a controller 756. It includes. In the analyzer 750 according to the above embodiment, the ATR includes a prism 753 and an optical inductor 754. The analysis unit 750 according to the embodiment has a structure for minimizing the signal to noise ratio (SN ratio) as much as possible to be used as a urine measurement sensor when installed in the toilet 710.

6A and 7A illustrate an embodiment of the present invention, wherein the light source unit 751 includes a plurality of small light sources having low power to increase the lifetime of the light source unit 751 while increasing the signal-to-noise ratio (SN ratio) as much as possible. It is also possible to take a multi-array structure by stacking in one or a plurality of rows. In the spectral analysis, in order to increase the signal-to-noise ratio, a method of increasing the intensity of the light source by using a halogen lamp or increasing the size of the heating plate can be used.However, since the size of a single heating plate is large, the response time is delayed in the detector so that accurate detection is possible. There is a difficult problem. In order to solve this problem, the light source unit 751 of the present invention forms a linear light source unit 751 in an array form by arranging a plurality of heat generating units having a small heating area in a row. That is, by using 10 or more small heat generating parts of 1 mm x 1 mm or arranging five or more small heat generating parts of 1.5 mm x 1.5 mm in a row, the reaction time at the detector 755 is delayed while increasing the total amount of light. Can solve the problem. That is, by adopting a plurality of small heating unit (light source unit 751), the size of each heating unit is relatively small compared to the conventional, so that the modulation depth (modulation depth) so that there is no problem in the light emitting function even if dozens of times on / off per second It is possible to improve the control, and to control the synchronization of the optical signal (pulse) of the light source unit 751 and the detector 755 in the CPU controller by software. In addition, by using platinum and platinum as the material of the light source unit 751, even if it is turned on and off tens of times per second, the mechanical durability is improved, and thus the problem of deterioration of luminous ability can be solved.

Further, the array structure of the light source unit 751 may be formed of two layers so that the pulse waveforms of the light source generated by the light source unit 751 and the light source reaching the light receiving unit 762 of the detector 755 coincide with each other. This is also to match the signal wavelength of the light source reaching the light receiving portion 762 of the detector 755 while maintaining the intensity of the light source. By such a configuration, more accurate and reliable results can be obtained.

Since the analysis unit 750 of the present invention cannot use a chopper due to its structural characteristics, such as a toilet, the light source unit 751 uses a plurality of light sources of low output as described above. You can also use (linear multi array) rays. In order to downsize the analyzer 700 of the present invention, a complex filter 761 (Linear Variable Filter, LVF) is used in front of the detector 755. The composite filter 761 is manufactured by MEMS technology.

In the present invention, ATR is a method of obtaining an infrared spectrum of a sample 758 which is difficult to deal with in general absorption spectroscopy, and may be suitably used to measure low-soluble solid, film, fiber, paste and adhesive and / or powder samples. Or the device.

When light passes from a dense medium to a coarse medium, reflection usually occurs. The reflection rate of incident light increases as the incident angle increases and total reflection occurs when a certain critical angle is exceeded.

It is experimentally and theoretically known that when such reflection occurs, light behaves as if it penetrates a small distance into a coarse medium, where the depth of penetration of the light varies from a few tenths to several wavelengths. Specifically, when the urine sample naturally flows and wets the surface of the ATR exposed to the toilet 710, the light passes through the ATR.

As described above, the ATR device can be suitably used to measure low solubility solid, film, fiber, paste and adhesive and / or powder samples. Recently, materials such as diamond or ZnSe, which are resistant to aqueous solutions, have been developed. Used to analyze the solution. When light passes from a dense medium to a coarse medium, reflection usually occurs. The reflection rate of incident light increases as the incident angle increases and total reflection occurs when a certain critical angle is exceeded. It is experimentally and theoretically known that when such reflection occurs, light behaves as if it penetrates a small distance into a coarse medium, where the depth of penetration of the light varies from a few tenths to several wavelengths.

The final penetration depth depends on the wavelength of the incident light, the index of refraction of the two materials, and the angle of incidence on the interface, which is called an evanescent wave, and when the coarse medium absorbs the evanescent wave, the light at the absorption band wavelength is attenuated. (attenuated) Light passing through the prism 753 is introduced into the detector 755 through an LVF (not shown) through an optimal optical system to an optical guide 754, such as a tapered rod. The light detected by the detector 755 is converted into a digital signal by the controller 756 and measured. The controller 756 measures the detected data and electronically controls each of the parts.

6B is a perspective view illustrating a state in which the spectroscopic module 760 employed in the analyzer 750 is attached to the toilet.

7A is a cross-sectional view illustrating a state in which light passes through the analysis unit 750 of the urine component analyzer 700. Referring to FIG. 7A, the light generated by the light source unit 751 is reflected by the reflector 752 surrounding the light source unit 751 and is incident on the ATR prism 753. The reflector 752 has a parabolic shape therein, and the light source unit 751 is positioned at a focal point of the parabola, and when the light generated by the light source unit 751 is reflected by the reflector 752, the ATR prism ( 753). Although FIG. 7A shows a parabolic reflector 752, the present invention is not limited to the shape of the reflector 752.

The light 757 incident on the ATR prism 753 is partially reflected by the sample 758 at the oblique surface of the ATR prism 753, and then totally reflected to form a light guide (Tapered Rod) 754. Is introduced into the detector 755. The detector 755 senses the intensity of the introduced light. As described above, the analysis unit 755 solves the problem of increasing the total light intensity by using a plurality of low-output light sources and rapidly decreasing the light intensity by using parallel light.

Although not shown in detail, since the analysis unit 750 is mounted on the toilet, urine should be present in a certain amount of the prism 753, so that the analysis unit 750 may be slightly recessed based on the inner side of the toilet. .

Thereafter, for washing the analysis unit 750, after the human excretion, the washing may be performed by using the water for washing the toilet, and secondly, the washing may be performed by using an air spray apparatus 720 separately provided on the toilet. have. It is preferable that the air injector 720 is mounted in the toilet, and is installed at an appropriate angle at which the air can be accurately injected to the analyzer 750.

On the other hand, Figure 7b is an external perspective view of the spectroscopic module 760 employed in the analysis unit 750 of another embodiment according to the present invention, Figure 7c is a side cross-sectional view of FIG.

Fig. 10 is a view showing the principle of the reflector 752 shown in Figs. 8 and 9, and Fig. 11 is a view showing the principle of the reflector 752 according to the present invention. 10 and 11, light generated by the light source unit 751 is reflected by a parabolic reflector 752 and is incident on the ATR prism 753. The parabolic reflector 752 is obtained using Equation 1 below.

Where c is the curvature (= 1 / r (curvature radius)), k is the conic constant and y is the height at the optical axis.

The reflector 752 has a cylindrical shape with a r value of 2 mm, a k value of -1, and a maximum outer diameter of 4 mm. That is, the y-axis direction is parabolic, and has a long shape (14 mm) in the x-axis direction. The light reflected by the reflector 752 is introduced into the prism 753. In this way, the light emitting surface shape of the light source portion 751 perpendicular to the optical path, the transmission portion of the prism 753, and the light receiving surface shape of the light receiving portion 762 of the detector 755 are similar to each other so that the loss of the light source can be avoided. Can increase.

12 and 13 are diagrams showing conditions for total reflection of light in the prism 753. As described above, the light 757 incident on the prism 753 has a portion of wavelengths absorbed by the sample 758 at the oblique surface of the prism 753, and the rest is totally reflected. In FIG. 12, light incident on the oblique plane at an angle of i follows Snell's law according to Equation 2 below on the oblique plane.

Where n is the refractive index of the medium (3.43) and n 'is the refractive index of air (1). In order for the light to totally reflect inside the prism 753 as i ', the light must be smaller than 90 degrees perpendicular to the normal of the oblique plane of the prism 753 (in this case, sini' = 1), where i is Obtained by 3.

The value of i obtained through the experiment is about 17 kHz, but the present invention is not limited thereto. Therefore, if i is greater than 17 degrees, light is totally reflected at the oblique side of the prism 753. In the present invention, i is incident at an angle of about 45 degrees, so most of the light is totally reflected at the oblique surface of the prism 753. The prism 753 has a triangular prism shape in which the length of the x-axis direction is 14 mm and the cut plane is an isosceles triangle like the size of the light source. The light totally reflected by the prism 753 is introduced into the detector 755 through the light guide 754.

FIG. 13 is a view illustrating a principle of transmitting light through the light guide 754. The optical inductor 754 is a glass block having six inclined surfaces that are tapered toward the lower side. As shown in FIG. 13, the light incident on the optical inductor 754 is totally reflected and transmitted from the inside. In this case, when the light is reflected from the inclined plane, it is added by an inclined angle. Therefore, if the inclination of the inclined surface of the light guide 754 is urgent, the total reflection condition is broken and the light rays may escape the light guide 754, so the inclination of the inclined surface should be appropriately adjusted.

A mirror tunnel 759 may be used instead of the light guide 754. Even when the mirror tunnel 759 is used, if the inclination angle is large, the light may be reflected and returned from the mirror tunnel 759, so the inclination of the inclined surface should be appropriately adjusted. In the light guide 754, 100% total reflection of light occurs, but in the case of the mirror tunnel 759, the light reflectance is 90%.

14 is a graph showing the intensity of light generated by the light source, and FIG. 15 is a graph showing the intensity of light measured by the detector 755 when the distance between the light source unit 751 and the detector 755 is 1 mm. Referring to FIG. 14, the light produced by the light source unit 751 and passed through the reflector 752 is measured very evenly, but when the distance exceeds 5 mm, the light intensity rapidly decreases again. In order to introduce the light, the distance between the light source unit 751 and the ATR is 5 mm or less. More preferably, the interval may be selected in the range of 0.5 to 3 mm in consideration of kinematic properties. By such a configuration, it is possible to configure a compact mid-infrared spectrometer that can be mounted in a narrow space called the toilet 710.

FIG. 15 illustrates the intensity of light measured by the detector 755 when a mirror tunnel 759 in the form of a rhombus (13 × 3 × 27mm) is used to efficiently transmit the light from the ATR to the detector 755.

16 is a flowchart illustrating a method of analyzing urine components in the urine component analyzing apparatus 700 of the present invention. Referring to FIG. 16, an analysis system including an analysis unit 750 of the urine component measuring apparatus 700 according to the present invention is driven (S1010). Then, the reference material is introduced into the analysis unit 750, and the analysis unit 750 measures a reference spectrum (S1020). The reference material includes water.

The sample is then introduced directly into the ATR through the urine section in the toilet 710. Next, the analyzer 750 including the ATR, the composite filter 761, and the like measure the absorption spectrum using the introduced sample (S1030). The absorption spectrum represents a constant wavenumber absorbed from the reference material compared with the reference spectrum, and the calculation formula is calculated as -log (reference spectrum / sample spectrum).

Next, a calibration curve indicating the correlation between the standard value and the absorption spectrum of each component of the sample previously measured is obtained (S1040). Substituting an absorption spectrum of the sample into the calibration curve may estimate each component value included in the sample (S1050). In general, the calibration curve is verified by using standard urine components and actual values, and then the R ^ 2 and SEC, which are statistical measures of correlation, are introduced into the computer in advance.

This entire process is called routine analysis. The most important of the routine analysis values is the standard error of prediction (SEP), which can be obtained simultaneously with the measurement as a statistical indicator of how the measured and actual values differ.

That is, the correlation between the standard value which measured each component (for example, Glucose, Albumin, Nitrite, Bilirubin, etc.) in a sample (for example, urine) and a general absorption spectrum is shown by a calibration curve. There is a measure of good or bad correlation, one is R ^ 2 and the other is represented by SEC (Standard error of calibration) and SEP (Standard error of prediction). R ^ 2, SEC, and SEP represent the correlation between the standard value and the absorption spectrum when the standard value and the value of the spectrum are represented by arbitrary straight lines.

Ideally, that is, the best correlation between the standard value and the absorption spectrum is statistically R ^ 2 is 1 and SEC and SEP are close to zero. The relationship between the standard value and the absorption spectrum can be expressed using multiple linear regression (MLR) or regression of partial least square (PLSR).

The calibration curve is used to measure component values, such as glucose (Glucose), included in the sample. The component value is represented by a root mean of standard error prediction (RMSEP) value, which is a reliability significance. By measuring the component value within such reliability significance, each component value contained in a sample can be measured.

 17 is a graph showing the results of glucose measurement spectra in urine using the urine component analyzer 700. 17 shows the measurement spectra for 20%, 10%, 5% and 0.2% Glucose concentrations. Water, the reference material, is measured first, followed by the absorption spectrum of glucose for the reference material. The intensity of this spectrum is represented by an absorbance unit (AU) value, which is the absorbance of the Y axis. The absorption spectrum measured by ATR-IR is about 0.01AU, and the Glucose absorption spectrum can be confirmed between 900 and 1400 wave numbers in the measured wave range of 4000 to 900 wave numbers. Glucose concentrations decrease in absorption spectrum as the concentration decreases in steps of 20% to 0.2%.

18 is a graph showing the results of creatine measurement spectrum in urine using the urine component analyzer 700. 18 shows the measurement spectra for 5%, 2% and 1% creatine concentrations. The measurement spectrum is also an absorption spectrum in which creatine is measured using a reference substance as water. The absorption spectrum measured by ATR-IR is shown at about 0.008 AU, and the creatine absorption spectrum can be confirmed between 1400 and 1900 waves in the measured wave range of 4000 to 900 waves. As the creatine concentration decreases in steps of 5% to 1%, the absorption spectrum also decreases.

19 is a graph showing the results of urea (Urea) measurement spectrum in urine using the urine component analyzer 700. 19 shows the measurement spectra for 10%, 5% and 2% Urea concentrations. The measurement spectrum is also an absorption spectrum in which urea is measured using a reference substance as water. Absorption spectra measured by ATR-IR are shown at about 0.012 AU, and urea absorption spectra can be found between 1400 and 1900 wavenumbers in which the creatine in FIG. As the concentration of urea decreases in steps of 10% to 2%, the absorption spectrum also decreases.

20 is a graph showing a spectrum measurement result of cholesterol in urine using the urine component analyzer 700. 20 shows the measurement spectra for 2%, 1% and 0.5% cholesterol concentrations. In this measurement spectrum, the absorption spectrum of cholesterol was measured using the reference substance as chloroform (CHCl 3). Absorption spectra measured by ATR-IR are shown at about 0.005 AU, and cholesterol absorption spectra can be confirmed between 2700 and 3100 waves in the measured wave range of 4000 to 900 waves. Absorption spectra decrease as the cholesterol level decreases in steps from 2% to 0.5%.

21 is a graph showing the results of bilirubin measurement spectra in urine using the urine component analyzer 700. FIG. 21 shows the measurement spectra for 2%, 1% and 0.5% bilirubin concentrations. In the above measurement, it is an absorption spectrum in which bilirubin is measured using chloroform (CHCl 3), which is the same reference substance as in FIG. 18. The absorption spectrum measured by ATR-IR is about 0.004 AU, and the bilirubin absorption spectrum can be confirmed between 1300 and 1800 waves in the measured wave range of 4000 to 900 waves. In addition, the absorption spectrum decreases as the bilirubin concentration decreases in steps of 2% to 0.5%.

22 is a graph of the urine acid measurement spectrum result in urine using the urine component analyzer 700. 22 shows the measurement spectra for 2%, 1% and 0.5% Uric acid concentrations. In the said measurement spectrum, a reference material is water and sodium hydroxide (NaOH), and it is an absorption spectrum which measured uric acid. Absorption spectrum measured by ATR-IR is shown at about 0.005AU, the Uric a cid absorption spectrum can be confirmed between 1100 to 1700 wavenumber, which is the measured wave range. As the concentration of uric acid decreases in steps of 2% to 0.5%, the absorption spectrum also decreases.

23 is a graph showing the results of nitrite measurement spectra in urine using the urine component analyzer 700. FIG. 23 shows the measurement spectra for 2%, 1% and 0.5% nitrite concentrations. In the said measurement spectrum, a reference material is made into water and it is the absorption spectrum measured by nitrite. Absorption spectra measured by ATR-IR appear at around 0.002 AU at the highest concentrations, and are between 1100 and 1500 wavenumbers, the measured wave range. As the concentration of nitrite decreases in steps of 2% to 0.5%, the absorption spectrum also decreases.

24 is a graph of glucose calibration curve of urine using the urine component analyzer 700. As shown in FIG. 24, the correlation between the change in the absorption spectrum of glucose at concentrations of 20%, 10%, 5%, and 0.2% and the concentration standard value shows that the correlation with the absorption spectrum has a very high R ^ 2 of 0.999. Since it appears linear, it is possible to estimate the amount of glucose through the absorption spectrum.

25 is a graph of creatine calibration curve of urine components using the urine component analyzer 700. As shown, the correlation between the change in the absorption spectrum of creatine at concentrations of 5%, 2% and 1% and the concentration standard value shows that the correlation of the absorption spectrum is very linear, with R ^ 2 of 0.999. The amount of creatine can be estimated through the absorption spectrum.

FIG. 26 is a urea calibration curve graph of urine components using the urine component analyzer 700 according to the first embodiment. As shown, the correlation between the change in the absorption spectrum of the concentration-specific elements of 10%, 5% and 2% and the concentration standard values shows that the correlation with the absorption spectrum is very linear, with R ^ 2 being 0.987. Estimate the amount of elements through the spectrum.

27 is a graph of the cholesterol calibration curve in urine components using the urine component analyzer 700. As shown, the correlation between the changes in the absorption spectrum of cholesterol at concentrations of 2%, 1% and 0.5% and the concentration standard values shows that the correlation with the absorption spectrum is very linear, with R ^ 2 being 0.997. You can estimate the amount of cholesterol through.

28 is a graph of bilirubin calibration curve of urine components using the urine component analyzer 700 according to the first embodiment. As shown, the correlation between the change in the absorption spectrum of bilirubin at concentrations of 2%, 1% and 0.5% and the concentration standard value shows that the correlation with the absorption spectrum is very linear with R ^ 2 of 0.988. The amount of bilirubin can be estimated by

FIG. 29 is an absorption spectrum for measuring uric acid included in a urine sample using the urine component analyzer 700 according to the first embodiment. As shown, the absorption spectrum of a) is measured by measuring the entire sample on the basis of water and then measuring the absorption spectrum of uric acid in the sample. It is difficult to separate the uric acid absorption spectrum at the same concentration by sample components such as creatine. However, in case of b), the absorption spectrum is measured by using urine except uric acid as reference material to separate individual absorption spectrum of uric acid. In this case, it can be seen that the absorption spectrum of the surrounding creatine and the like is excluded and the uric acid absorption spectrum appears.

30 is an absorption spectrum for measuring urea contained in a urine sample using the urine component analyzer 700. As shown in FIG. 29, the absorption spectrum of a) is measured as a whole based on water, and then the absorption spectrum of urea in the sample. As in Fig. 29, it is difficult to separate the uric acid absorption spectrum at the same concentration by the sample components such as ambient creatine. However, in the case of b), absorption spectra were measured using urine excluding urea as a reference material to separate the individual absorption spectra of urea. In this case, it can be confirmed that the absorption spectrum of the surrounding creatine and the like is excluded and the urea absorption spectrum appears.

FIG. 31 is a spectrum of a glucose standard sample measured using a conventional FT-IR, and FIG. 32 is a spectrum of a glucose standard sample measured using a urine component analyzer 700. The glucose standard sample is obtained by dissolving glucose in tertiary distilled water, preparing 100 mg / dL, 300 mg / dL, 500 mg / dL, and 1000 mg / dL. As shown in Figure 31 and 32, using the conventional FT-IR and the urine component analyzer 700 according to the present invention, the glucose peak appears at 950 ~ 1150cm-1 without significant difference in the spectrum of the glucose standard sample It can be seen.

In general, conventional IR equipment has a low sensitivity of the light source has been widely used for measuring instruments using the FT method. In the conventional FT method, the light beam of the light source is divided into two parts, and then the length of the light path of one light beam is periodically converted to generate an interference pattern, and then the data must be processed using the Fourier transform method. At this time, the speed of the moving mirror is constant in order to obtain satisfactory interference, and the He-Ne Laser must be used to ensure the position of the moving mirror at every moment. There is a problem that can not be attached and the price also costs tens of millions of won. However, the urine component analyzer 700 according to the present invention can be manufactured in a very small form at a very low cost, and has the advantage of having almost the same effects as the conventional method as shown in FIGS. 31 and 32.

FIG. 33 is a spectrum measured from a diabetic patient in a hospital using a conventional FT-IR, and FIG. 34 is a spectrum measured from a urine sample using the urine component analyzer 700 according to the present invention. to be. As shown in FIGS. 33 and 34, the urine sample collected from the diabetic patient showed a protein peak near 1600 cm −1, but the peak of glucose did not overlap. However, the baseline was slightly elevated due to several other substances present in the urine.

As described above, the present invention has been described by specific embodiments such as specific components and the like, but the embodiments and the drawings are provided only to help a more general understanding of the present invention, and the present invention is limited to the above embodiments. In other words, various modifications and variations are possible to those skilled in the art to which the present invention pertains.

Therefore, the spirit of the present invention should not be limited to the described embodiments, and all of the equivalents or equivalents of the claims as well as the claims to be described later will belong to the scope of the present invention. .

Figure 1a is a perspective view showing a medical examination system including a urine component analysis device according to an embodiment of the present invention.

1b to (d) a perspective view of a medical examination system including a urine component analysis device according to another embodiment of the present invention.

Figure 2a is a perspective view showing a body fat measurement apparatus constituting a health diagnosis system according to an embodiment of the present invention.

Figure 2b is a perspective view of the handle of the body fat measurement apparatus according to an embodiment of the present invention.

3 is a conceptual diagram of a general infrared spectrometer.

Figure 4a is a conceptual diagram of the spectroscopic analysis of the urine component analyzer according to the present invention.

Figure 4b is an embodiment of the urine component analysis device according to the present invention

5 is a conceptual diagram of a light source unit, a prism, and a detector light receiving unit in the analysis unit according to the present invention, (a) is a rectangle, (b) is a circle, and (c) is a triangle.

Figure 6a is a perspective view showing that the analysis unit is attached to the toilet bowl in accordance with the present invention.

Figure 6b is a perspective view showing that the analysis unit (spectral module) of another embodiment according to the present invention is attached to the toilet.

Figure 7a is a perspective view of the cut portion of the analysis portion attached to the toilet bowl in accordance with the present invention.

Figure 7b is an external perspective view of a spectroscopic module which is an analysis unit of another embodiment according to the present invention.

7C is a side cross-sectional view of the spectral module of FIG. 7B in accordance with the present invention.

8 is a perspective view of an analysis unit according to the present invention

9 is a conceptual view of the analysis section in accordance with the present invention

10 is a conceptual diagram of the principle of the reflector in the analysis unit according to the present invention

11 is a conceptual diagram of the principle of the reflector in the analysis unit according to the present invention

12 is a conceptual diagram of a prism in the analysis unit according to the present invention

Figure 13 is a conceptual diagram for the tapered rod and mirror tunnel in the analysis unit according to the present invention

14 is a screen showing that the light irradiation in the analysis unit according to the present invention

15 is a screen showing the amount of light efficiency introduced into the detector when the distance between the light source and the detector 1mm according to the present invention

16 is a flow chart showing a method of analyzing urine components according to the present invention.

17 is a graph showing the results of measurement of glucose in urine (Glucose) using the urine component analyzer according to the present invention.

18 is a graph of the results of creatine measurement spectrum in urine using the urine component analyzer according to the present invention.

Figure 19 is a graph of the urea (Urea) measurement spectrum results in the urine using the urine component analyzer according to the present invention.

20 is a graph showing a spectrum measurement result of cholesterol in urine using the urine component analyzer according to the present invention.

21 is a graph showing the results of bilirubin measurement spectra in urine using the urine component analyzer according to the present invention;

22 is a graph of the results of measurement of uric acid (Uric acid) spectrum in urine using the urine component analyzer according to the present invention.

23 is a graph showing the results of nitrite measurement spectra in urine using the urine component analyzer according to the present invention.

24 is a graph of glucose calibration curve results in urine using the urine component analyzer according to the present invention.

25 is a graph of the results of creatine calibration curve in urine using the urine component analyzer according to the present invention.

Figure 26 is a graph of the results of the urea (Urea) calibration curve in the urine using the urine component analyzer according to the present invention.

Figure 27 is a graph of the cholesterol (Cholesterol) calibration curve results in urine using the urine component analyzer according to the present invention.

28 is a graph of the results of bilirubin calibration curve in urine using the urine component analyzer according to the present invention.

29 is a graph of measuring uric acid in the sample mixture in urine using the urine component analyzer according to the present invention.

30 is a graph of the measurement of urea (Urea) in the sample mixture in urine using the urine component analyzer according to the present invention.

31 Spectrum of standard glucose according to FT IR

32 Spectrum of standard glucose according to LVF IR

33 is a spectrum of urine samples according to FT IR

Figure 34 is a spectrum of urine samples according to LVF IR

** Description of the symbols for the main parts of the drawings **

1000: arm support 100: blood pressure measuring device

200: bidet control device 300: fingerprint recognition device

400: monitor 500: main controller

600: body fat measurement device 601 ~ 608: electrode

609: handle 610: slit

611: Cover

700: urine component analyzer 710: toilet seat

720: air injection device 750: analysis unit

751: light source 752: reflector

753: Prism 754: the light guide

755: Detector 756: Controller

757: light incident on the prism 758: sample

759: mirror tunnel

760: spectral module 761: composite filter

762: light receiver

800: drug injection device 900: weight measuring device

Claims (19)

Toilet seat 710; A urine collecting portion (not shown) formed on the inner surface of the toilet in a concave shape or a flat shape; Analyzing the components of urine collected from the urine collecting portion and directly attached to the toilet bowl 710, the light source unit 751, a composite filter ( 761, an analyzer 750 including any one or more of a reflector 752 and a detector 755; And An attenuation prism 753 (ATR prism) further included in the analysis unit 750 for analyzing urine components; ≪ / RTI > The light emitting surface shape of the light source unit 751 perpendicular to the optical path and the light receiving surface shape of the light receiving unit 762 of the detector 755 are similar to each other in order to minimize light loss and keep the signal-to-noise ratio (SN ratio) as high as possible. Small urine component analysis device for the toilet, characterized in that corresponding. The method of claim 1, The light source unit 751 is a small urine component analysis device for the toilet, characterized in that using the mid-infrared wavelength range of 2,500 to 15,000nm. 3. The method of claim 2, The prism 753 has a cross-sectional shape of the transmissive portion perpendicular to the optical path so as to correspond to the shape of the light emitting surface of the light source 751 perpendicular to the optical path and the shape of the light receiving surface of the light receiving unit 762 of the detector 755. Small urine component analysis device for the toilet, characterized in that. 3. The method of claim 2, The total urine distance of the light from the light source unit 751 to the detector 755 is 10 to 50 mm, the small urine component analysis device for the toilet. The method of claim 4, wherein Small urine component analysis device for the toilet, characterized in that the interval between the light source unit 751 and the prism (753) is 300㎛ ~ 5mm. The method of claim 4, wherein Small urine component analysis device for the toilet, characterized in that the interval between the prism (753) and the detector (755) is 300㎛ ~ 5mm. 3. The method of claim 2, The light source unit (751) is a small urine component analysis device for the toilet, characterized in that it has an array structure in which a plurality of small heat generating units are arranged side by side. The method of claim 7, wherein The array structure of the light source unit 751 comprises two or more layers so that the pulse waveforms of the light source generated by the light source unit 751 and the light source reaching the light receiving unit 762 of the detector 755 coincide with each other. Urine component analyzer. The method of claim 3, The prism (753) is a small urine component analysis device for the toilet, characterized in that the entrance surface and the exit surface is arranged to form a predetermined angle. The method of claim 3, The analysis unit 750 comprises a small urine component analysis device for the toilet, characterized in that it comprises a tapered rod or mirror tunnel (759) to guide the light passing through the prism (753) to the detector (755). The method of claim 1, The urine component is glucose (Glucose), creatine (Creatine), urea (Urea), protein, albumin, PH, trigloside, cholesterol (Cholesterol), bilirubin (Bilirubin), uric acid (Uric acid), nitrite (Nitrite) Small urine component analysis device for toilet seat, characterized in that any one of. The method of claim 1, The analysis device 700 is a small urine component analysis device for the toilet, characterized in that further comprising any one or more of the blood pressure measuring device 100, body fat measuring device 600, and electrocardiogram measuring device. The method of claim 12, The analysis device 700 is a small urine component analysis device for the toilet, characterized in that operated after the user is authenticated by the fingerprint recognition device (300). Measuring the spectrum of the reference material introduced through the urine collecting part of the toilet using the ATR of the analyzing part 750; Measuring the absorption spectrum of urine introduced through the urine collecting unit using the ATR of the analyzing unit 750; Obtaining a calibration curve indicating a correlation between a standard value of each component of urine measured in advance and an absorption spectrum; And Estimating the amount of each component included in the urine using the calibration curve; Including, In order to keep the signal-to-noise ratio (SN ratio) as high as possible, the shape of the light emitting surface of the light source unit 751 perpendicular to the optical path and the shape of the light receiving surface of the light receiving unit 762 of the detector 755 correspond to each other. Real-time urine component analysis method. The method of claim 14, The spectrum of the reference material and the absorption spectrum of urine are measured by using the light introduced into the ATR. The method of claim 15, The light is a real-time urine component analysis method, characterized in that the wavelength range of 2,500 ~ 15,000nm mid-infrared. The method of claim 14, The prism 753 used for the spectral analysis is different from the light emitting surface shape of the light source unit 751 and the light receiving surface shape of the light receiving unit 762 of the detector 755 where the transmissive cross section shape perpendicular to the optical path is perpendicular to the optical path. Real-time urine component analysis method characterized in that the correspondence. The method of claim 14, The reference material is a real-time urine component analysis method, characterized in that water, air, or a combination thereof according to the urine component to be measured. The method of claim 14, The urine component is glucose (Glucose), creatine (Creatine), urea (Urea), protein, albumin, PH, trigloside, cholesterol (Cholesterol), bilirubin (Bilirubin), uric acid (Uric acid), nitrite (Nitrite) Real-time urine component analysis method, characterized in that any one of.

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