KR20200085972A - Optical Sensor for a Cancer Diagnosis and Sensing Device therewith - Google Patents

Abstract

The present invention relates to an optical sensor and, more particularly, to an optical sensor device for early cancer diagnosis. Provided to this end are: a case (10) having an inner hollow (15), a gas inflow port (70), and a gas discharge port (75); a light source (20) provided above the hollow (15); a first reflector (60) reflecting light from the light source (20) in a first direction; a seventh reflector (57) for reflecting the incident light from the first reflector (60); a third reflector (50) and a fourth reflector (52) provided so as to face the seventh reflector (57); a first infrared sensor (30) provided on one of the seventh reflector (57) and the third and fourth reflectors (50, 52); a second infrared sensor (32) provided on the other of the seventh reflector (57) and the third and fourth reflectors (50, 52); an eighth reflector (58) for reflecting the incident light from a second reflector (65); a fifth reflector (54) and a sixth reflector (56) provided so as to face the eighth reflector (58); a third infrared sensor (34) provided on one of the eighth reflector (58) and the fifth and sixth reflectors (54, 56); and a fourth infrared sensor (36) provided on the other of the eighth reflector (58) and the fifth and sixth reflectors (54, 56).

Description

Optical sensor for early cancer diagnosis and sensor device including the same

The present invention relates to an optical sensor, and more particularly, to an optical sensor for early cancer diagnosis and a sensor device including the same.

According to recent research results, about 874 types of volatile organic compounds (VOCs) are detected by breathing, about 874 types, 279 types in urine, and 381 types in feces. In addition, it is known that about 15.7% of VOCs through the respiratory tract exhibit the same components of VOCs as urine. In patients with bile acid diarrhoea (BAD), 2-flopanol and acetamide are released, and in patients with liver disease, dimethyl sulfide, hydrogen sulfide, and mercaptans It is known to increase. These are due to imbalances in the intestinal microflora, and the concept of'Dysbiosis' has been established.

In other words, the main functions of intestinal microbes are 1) affecting metabolic activity, 2) regulating hormone secretion in the intestinal epithelium, 3) regulating fidelity of intestinal function, and 4) maintaining homeostasis of intestinal immune function. . Studies on the fermentation of intestinal microorganisms and their intestinal foods and the types and etiology of VOCs in feces have been actively studied through measurement and discrimination of VOCs through maturation of urine and feces.

Therefore, it is indispensable to understand the VOCs generated in the process of fermentation (fermentation) of urine and feces as human body excretion and to study the correlation analysis of human etiology.

On the other hand, when looking at the'status of cause of death in Korea in 2016' released by the National Statistical Office, the number of deaths from cancer was the highest in the cause of death, heart disease, cerebrovascular disease, In the order of pneumonia, suicide (deliberate self-harm), diabetes, chronic lower respiratory tract disease, liver disease, hypertensive disease, and transportation accidents, the cause of these teenage deaths accounted for 69.5% of the total.

The number of deaths from cancer per 100,000 population was 153, and it was reported that the death rate from colorectal cancer was higher than the mortality rate from gastric cancer after the statistical data were prepared in 1983.

Differences by cancer type/men and women were 188.8 early mortality in men, followed by lung cancer (52.2), liver cancer (31.5), stomach cancer (20.8), colon cancer (18.4), and lung cancer (in women). 18.1 patients, colon cancer (14.6 people), liver cancer (11.6 people), gastric cancer (11.5 people), and pancreatic cancer (10.6 people) were reported in the order of the results (National Cancer Information Center).

carcinoma International Disease Classification The number of deaths Fraction (%) Survey mortality man Lung cancer C33-C34 13,324 27.6 52.2 Liver cancer C22 8,044 16.7 31.5 Stomach cancer C16 5,318 11.0 20.8 Colorectal cancer C18-C21 4,686 9.7 18.4 Woman Lung cancer C33-C34 4,639 15.5 18.1 Colorectal cancer C18-C21 3,746 12.5 14.6 Liver cancer C22 2,957 9.9 11.6 Pancreatic cancer C25 2,713 9.0 10.6

When comparing the domestic situation with advanced foreign countries, the incidence rate of age standardization as shown in [Table 2] is the same as the international comparison table. Located in Korea, it shows that the incidence of colorectal cancer is similar to that of developed countries, indicating that the factors associated with westernization of eating habits dominate.

International comparison of age standardization rates.
[Unit: 100,000 people] ranking* Korea
(2014) 2012 estimate Japan USA England - All cancers 297.1 All cancers 260.4 All cancers 347.0 All cancers 284.0 man One top 52.7 top 45.7 prostate 98.2 prostate 73.2 2 lungs 43.7 Leader 42.1 lungs 44.2 Leader 36.8 3 Leader 42.6 lungs 38.8 Leader 28.5 lungs 34.9 4 liver 31.4 prostate 30.4 bladder 19.6 Skin malignant 13.7 Woman One thyroid 69.8 breast 51.5 breast 92.9 breast 95.0 2 breast 47.7 Leader 23.5 lungs 33.7 lungs 25.8 3 Leader 23.0 top 16.5 Leader 22.0 Leader 24.4 4 top 21.4 lungs 12.9 thyroid 20.0 Malignant skin
Melanoma 15.6

As can be seen from the domestic and foreign cases shown in [Table 1] and [Table 2], the incidence of colorectal cancer is relatively high in both men and women, stomach cancer in Korean men, and breast cancer in women is relatively high. It is showing.

On the other hand, as shown in [Table 3], the proportion of patients in the local/local atmosphere of colorectal cancer in the proportion of patients by major cancer types occupies about 80% of the total. However, if colon cancer is metastasized, the survival rate is less than 20%, which means that early cancer detection and treatment are important.

Summary of major carcinoma summary 5-year relative survival rate (all men and women: 2010-2014).
(unit: %) Occur
ranking carcinoma Summary Limited Topical remote do not know Patient fraction Survival rate Patient fraction Survival rate Patient fraction Survival rate Patient fraction Survival rate One thyroid 42.6 100.6 50.6 100.4 0.7 71.6 6.1 99.1 2 top 60.3 95.9 23.0 60.1 11.2 6.3 5.5 41.9 3 Leader 38.1 95.6 41.2 81.2 14.9 19.3 5.8 60.0 4 lungs 20.0 61.2 26.6 33.7 44.5 5.9 8.8 17.2 5 breast 57.4 98.1 34.6 90.6 4.8 37.3 3.3 83.6 6 liver 46.0 53.1 24.7 19.3 15.9 3.2 13.4 24.1

Therefore, early diagnosis of cancer can lead a healthy life and can be said to be treatable. Early diagnosis of colorectal cancer is fecal Occult Blood Test (FOBT), Fecal Immunochemical Test (FIT) ), S-shape colonoscopy (FS), colonoscopy, etc. are being performed. In other words, FOBT or FIT is performed first, and the results of this are analyzed, and then additional clinical trials are conducted. In the case of FOBT or FIT, sensitivity and selectivity are low, and thus, clinical response has not been obtained. In particular, it is an examination method through feces, and thus it has not been well received at home and abroad because it provides discomfort to patients. On the other hand, the method of FS or colonoscopy is superior to the above-described method, but it is an invasive method of the human body, and the low accessibility of the patient is an obstacle to early diagnosis and treatment of colorectal cancer due to the high cost of examination.

Therefore, in the medical and engineering fields, studies on non-invasive early cancer diagnosis methods are underway, and for this purpose, tracking and management of biomarkers (biomarkers) occurring in the correlation between diseases and substances and byproducts that cause them, and to detect them Research into water systems or sensors is ongoing. One of these research directions is a polymer or semiconductor gas sensor array (array: array for checking the presence or absence of a specific gas by forming 32 sensor arrays and comparing and evaluating their output changes for various gases) Although a technology for determining the presence or absence of a specific gas in a mixed gas has been applied, a non-dispersive infrared gas sensor (NDIR) due to the disadvantages of the chemical method sensor (slow recovery time due to chemical reaction, deterioration of durability, etc.) ) Has been reported for the first time in 2017 on a method for measuring gas concentrations using an optical method.

However, the conventional NDIR method has the following problems and was not easily utilized for cancer diagnosis. First, although it is significantly lower than the semiconductor or polymer method, the infrared light source changes optical properties over time due to changes in physical properties of the filament or black body surface. That is, as the use period or the number of uses increases, the intensity of light (light) decreases (aging change, after about 3 years), resulting in a decrease in output voltage, which causes errors between the actual concentration and the high concentration gas concentration. Provided. That is, there is a problem in that the sensitivity of the gas sensor is reduced or a value different from the actual concentration is measured.

Second, the existing white cell (Cell) and non-dispersive infrared gas sensor (NDIR) (Korea Patent Registration No. 10-1810423) having a structure applied to it have one light source and one infrared detector (or When using a structure in which four infrared sensors were physically combined, only one type of gas concentration could be measured by using four components. In order to measure the concentration of multiple gases using a white cell structure, it was possible to additionally fabricate another plurality of structures, thereby causing additional cost. That is, it has the disadvantage that the entire system is complicated when measuring gas in the conventional way, and it is impossible to manufacture a multi-gas sensor (about 30 or more) system using the existing polymer and semiconductor sensor array.

Third, among the fermentation gas components of various cancer patients or colon disease patients (enteritis, Crohn's disease, colon cancer patients), the specific components and central wavelengths of absorption of these gases are presented in [Table 5]. As shown in Table 5, various biomarkers are known to absorb infrared rays at wavelengths between 3 μm and 10 μm. Therefore, for example, in the case of butyrate gas, if you want to accurately measure this gas in the same wavelength band, about 9 (3.36, 5.78, 6.82, 7.27, 7.65, 7.95, 8.50, 9.10, 9.75 ㎛) An infrared gas sensor with a band filter is required, but with the development of recent technologies, 3.12 ~ 4.4 μm (LFP-3144C-337), 3.8 ~ 5.0 μm (LFP-3850C-337), 5.5 ~ 8.0 μm (LFP-5580C- 337), an infrared sensor with a Fabry-Perot Interferometer (FPI) capable of adjusting the absorption wavelength at intervals of about 30 nm in the band of 8.0 to 10.5 μm (LFP-80105C-337) is in early production (Infratec, Germany). Therefore, by arranging these sensors and adjusting the absorption wavelength band, it is possible to secure sensor output in all wavelength ranges within the 3 to 10 μm band, and to secure about 40 characteristic values for each sensor, 3 If you place two infrared sensors, you can expect the same infrared sensor device in which about 120 polymer or semiconductor type sensors are arranged. However, the development of an optical waveguide (optical waveguide) and a sensor system or device using the sensor can be integrated and driven.

(1) Republic of Korea Patent Publication No. 10-2014-0020532 (published on February 19, 2014, composite light source device for optical diagnosis and light treatment) (2) Republic of Korea Patent Registration No. 10-1746406 (announcement date 14 June 2017, non-dispersive infrared gas sensor with an oval optical structure and gas concentration measurement method using the same) (3) Republic of Korea Patent Registration No. 10-1810423 (Announcement date December 20, 2017, gas concentration measurement method of non-dispersed gas sensor and compensation method for aging change)

Therefore, the present invention was devised to solve the above problems, and the first object is not only to check the aging change through the voltage measured by the gas sensor and to measure gas concentration more accurately, but also to use one light source. It uses a plurality of infrared sensors and can be used as multiple gas sensor modules, and each infrared sensor can be used as a multi-sensor or sensor array structure by controlling the infrared absorption wavelength at regular wavelength intervals. It is described in providing an optical sensor capable of early diagnosis of various diseases including cancer and a sensor device including the same by accurately determining the presence or absence of a specific gas in the mixed gas by measuring infrared rays in a wide absorption wavelength band.)

The second object of the present invention is to provide an optical sensor for early cancer diagnosis and a sensor device including the same, which enables early detection of cancer by analyzing a patient's breath or fermentation gas of a specimen.

A third object of the present invention is to provide a more accurate gas concentration through a plurality of infrared sensors, and to accurately determine whether a specific gas component is included. Is to provide.

However, the technical problems to be achieved in the present invention are not limited to the technical problems mentioned above, and other technical problems that are not mentioned are clearly understood by those skilled in the art from the following description. Will be understandable.

In order to achieve the above technical problem, a cavity 15 is formed inside, a case 10 having an inlet 70 through which gas is introduced and an outlet 75 through which the gas is discharged; A light source 20 provided on the cavity 15; A first reflector 60 reflecting light irradiated from the light source 20 in a first direction; A seventh reflector 57 for reflecting light incident from the first reflector 60; A third reflector 50 and a fourth reflector 52 provided to face the seventh reflector 57; A first infrared sensor 30 provided on one side of the seventh reflector 57 and the third and fourth reflectors 50 and 52; A second infrared sensor 32 provided on the other side of the seventh reflecting mirror 57 and the third and fourth reflecting mirrors 50 and 52; An eighth reflector 58 for reflecting light incident from the second reflector 65; A fifth reflector 54 and a sixth reflector 56 provided to face the eighth reflector 58; A third infrared sensor 34 provided on one side of the eighth reflector 58 and the fifth and sixth reflectors 54 and 56; And an eighth reflector (58) and a fourth infrared sensor (36) provided on the other side of the fifth and sixth reflectors (54,56).

Further, the light source 20 is provided in the central region of the cavity 15.

In addition, one of the first infrared sensor 30 and the second infrared sensor 32 is a reference sensor, the other further includes an FPI filter 120, the third infrared sensor 34 and the fourth The infrared sensor 36 is an infrared sensor equipped with an FPI filter, and is a sensor capable of measuring infrared intensity at an interval of about 30 nm.

In addition, the case 10 is a rectangular shape, the first, 2, 3, 4 infrared sensors 30, 32, 34, 36 are provided in each corner area of the rectangular shape.

In addition, the gas is a fermentation gas of respiration or sputum, and the sputum is one of urine, feces, blood, sweat, saliva, and hormones.

In addition, at least two of the first, second, third, and fourth infrared sensors 30, 32, 34, and 36 are infrared sensors incorporating an FPI filter capable of detecting the concentration of volatile organic compounds contained in the fermentation gas.

The object of the present invention as described above, as another embodiment, the cavity 15 is formed in the inside, the case 10 is formed with an inlet 70 through which gas is introduced and an outlet 75 through which gas is discharged; A light source 20 provided on the cavity 15; A first reflector 60 reflecting light irradiated from the light source 20 in a first direction; A seventh reflector 57 for reflecting light incident from the first reflector 60; A third reflector 50 and a fourth reflector 52 provided to face the seventh reflector 57; A first infrared sensor 30 provided on one side of the seventh reflector 57 and the third and fourth reflectors 50 and 52; A second infrared sensor 32 provided on the other side of the seventh reflector 57 and the third and fourth reflectors 50 and 52; An eighth reflector 58 for reflecting light incident from the second reflector 65; A fifth reflector 54 and a sixth reflector 56 provided to face the eighth reflector 58; A third infrared sensor 34 provided on one side of the eighth reflector 58 and the fifth and sixth reflectors 54 and 56; And a fourth infrared sensor 36 provided on the other side of the eighth reflector 58 and the fifth and sixth reflectors 54 and 56; the optical sensor 100 including;

Any one of the first, second, third, and fourth infrared sensors 30, 32, 34, 36 is a reference sensor, and the FPI filter 120 further included in the remaining sensors; A center wavelength control unit 180 for controlling the center wavelength of the FPI filter 120 based on the output signals of the first, second, third, and fourth infrared sensors 30, 32, 34, and 36; And a control unit 200 for recognizing a biomarker based on the output signals of the first, second, third, and fourth infrared sensors 30, 32, 34, and 36. It can also be achieved by.

In addition, the central wavelength control unit 180 controls the voltage applied to the FPI filter 120 to control the central wavelength.

In addition, the infrared absorption wavelength of the biomarker is at least one of the 3.1 to 4.4 μm band, the 5.5 to 8.0 μm band, and the 8.0 to 10.5 μm band.

In addition, the first valve 250 is installed on the inlet 70 side to control the inflow of gas; A second valve 260 installed on the outlet 75 side to control gas discharge; And a pump 270 for introducing gas into the cavity 15.

In addition, the control unit 200 controls the operation of the first and second valves 250 and 260 and the pump 270.

According to one embodiment of the present invention, by analyzing the patient's respiration or fermentation gas of the specimen, non-invasive early detection of cancer is possible, thereby improving the possibility of reaching the cure. .

In addition, it is possible to calculate a more accurate gas concentration through a plurality of infrared sensors, and it is also possible to check whether the operation is normal, thereby preventing the sensor from malfunctioning and improving reliability, and especially detecting and concentration of biomarkers in respiratory gas. It also has the ability to measure.

In addition, it is possible to check the aging change through the voltage measured by the gas sensor and make a more accurate gas concentration measurement. In addition, there is an advantage that it is possible to measure the concentration of several types of VOCs at the same time rather than one type of VOCs.

However, the effects obtainable in the present invention are not limited to the above-mentioned effects, and other effects not mentioned will be clearly understood by those skilled in the art from the following description. Will be able to.

The following drawings attached in this specification are intended to illustrate preferred embodiments of the present invention, and serve to further understand the technical idea of the present invention together with the detailed description of the invention described below, and thus the present invention is described in such drawings. It is not limited to interpretation.
1 is a schematic plan view of an optical sensor 100 for early cancer diagnosis according to an embodiment of the present invention,
FIG. 2 is an operation state diagram showing a reflection path of the infrared ray 80 when the optical sensor 100 shown in FIG. 1 operates.
3 is a graph showing the incident energy of each sensor when the light irradiated from the light source 20 is reflected symmetrically left and right,
3A is a graph of incident energy of the first infrared sensor (gas sensor) 30,
3B is a graph of incident energy of the fourth infrared sensor (gas sensor) 36,
3C is a graph of incident energy of the second infrared sensor (reference sensor) 32,
3D is a graph of incident energy of the third infrared sensor (reference sensor) 34,
Figure 4a is a graph showing the measurement results showing an example of the center wavelength dependence of the output voltage of a single infrared sensor equipped with an FPI filter,
Figure 4b is a graph showing the carbon dioxide gas dependence results of the sensor cumulative voltage using a single infrared sensor equipped with an FPI filter,
Figure 4c is a graph showing the analysis results of the main component in a state in which various biomarkers are mixed,
Figure 4d is a block diagram showing the components and signal processing system diagram of the optical gas device for early cancer diagnosis.

Hereinafter, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings so that those skilled in the art to which the present invention pertains may easily practice. However, since the description of the present invention is only an example for structural or functional description, the scope of the present invention should not be interpreted as being limited by the examples described in the text. That is, since the embodiments can be variously changed and have various forms, it should be understood that the scope of the present invention includes equivalents capable of realizing technical ideas. In addition, the purpose or effect presented in the present invention does not mean that a specific embodiment should include all of them or only such an effect, and the scope of the present invention should not be understood as being limited thereby.

The meaning of the terms described in the present invention should be understood as follows.

Terms such as “first” and “second” are for distinguishing one component from other components, and the scope of rights should not be limited by these terms. For example, the first component may be referred to as the second component, and similarly, the second component may also be referred to as the first component. When a component is said to be "connected" to another component, it may be understood that other components may exist in the middle, although they may be directly connected to the other component. On the other hand, when a component is said to be "directly connected" to another component, it should be understood that no other component exists in the middle. On the other hand, other expressions describing the relationship between the components, that is, "between" and "immediately between" or "adjacent to" and "directly neighboring to" should be interpreted similarly.

Singular expressions are to be understood as including plural expressions unless the context clearly indicates otherwise, and terms such as “comprises” or “having” refer to the features, numbers, steps, actions, components, parts, or components described. It is to be understood that a combination is intended to indicate the existence, and does not preclude the existence or addition possibility of one or more other features or numbers, steps, operations, components, parts or combinations thereof.

All terms used herein have the same meaning as generally understood by a person skilled in the art to which the present invention pertains, unless otherwise defined. The terms defined in the commonly used dictionary should be interpreted to be consistent with meanings in the context of related technologies, and cannot be interpreted as having ideal or excessively formal meanings unless explicitly defined in the present invention.

Example Configuration

Hereinafter, the configuration of the preferred embodiment will be described in detail with reference to the accompanying drawings. First, FIG. 1 is a schematic plan view of an optical sensor 100 for early cancer diagnosis according to an embodiment of the present invention. As shown in Fig. 1, the case 10 is a rectangular parallelepiped (126 mm wide, 76 mm long, 20 mm deep) having a substantially rectangular plane. One side of the case 10 is provided with an inlet 70 through which the gas to be measured flows, and an outlet 75 for discharging the gas is provided on the opposite side. The inside of the case 10 is emptied into the cavity 15, and various sensors and reflectors are disposed in the inner edge region of the case 10.

The cavity 15 is largely divided into two regions by the light source 20, and the central region is connected. The light source 20 is disposed in the center of the cavity 15 and irradiates infrared light toward the first and second reflectors 60 and 65.

The first reflector 60 is disposed in front of the light source 20, and is manufactured at an inclined or inclined angle to reflect the infrared light emitted from the light source 20 toward the third and fourth reflectors 50 and 52.

The third and fourth reflectors 50 and 52 are divided from each other, and are arranged side by side to face the seventh reflector 57.

The seventh reflecting mirror 57 is provided in front of the third and fourth reflecting mirrors 50 and 52 and is arranged to reflect infrared rays to the third and fourth reflecting mirrors 50 and 52 several times. That is, the third and fourth reflectors 50 and 52 are two mirrors divided from each other, and the seventh reflector 57 is a mirror having two or more mirror surfaces compared to the third and fourth reflectors 50 and 52. .

The first infrared sensor 30 is a gas sensor, and is disposed at the upper left (based on FIG. 1) of the case 10. The gas sensor means a sensor having a filter or FPI filter corresponding to a specific wavelength in front of the first infrared sensor 30 to detect the gas concentration of a specific component. The first infrared sensor 30 may be configured to adjust a specific wavelength of infrared light that passes through the filter, detect the signal, and is configured to output an electrical signal proportional to it.

The second infrared sensor 32 is a sensor having a characteristic capable of transmitting a reference wavelength (for example, 3.90 μm), and is disposed at the bottom left of the case 10 (based on FIG. 1 ). The reference sensor means a sensor having a filter corresponding to a specific wavelength band of infrared light irradiated from the light source 20 or artificially adjusting a transmission wavelength so as to pass infrared light of a specific wavelength. The second infrared sensor 32 detects a specific wavelength of the incoming infrared light and outputs an electric signal proportional to it, measures the voltage of the first infrared sensor 30 by using it as a reference voltage, or degrades the infrared light source. This sensor is applied to the compensation of the output voltage and can provide a signal including the output of a specific wavelength band.

The second reflector 65 is disposed in front of the light source 20, and is inclined to reflect infrared rays emitted from the light source 20 toward the fifth and sixth reflectors 54 and 56.

The fifth and sixth reflectors 54 and 56 are divided from each other, and are arranged side by side to face the eighth reflector 58.

The eighth reflector 58 is provided in front of the fifth and sixth reflectors 54 and 56 and is arranged to reflect infrared rays to the fifth and sixth reflectors 54 and 56 several times. That is, the fifth and sixth reflectors 54 and 56 are two mirrors divided from each other, and the eighth reflector 58 is a single mirror having twice or more mirrors.

The fourth infrared sensor 36 is a gas sensor, and is disposed on the upper right side of the case 10 (see FIG. 1 ). The gas sensor means a sensor equipped with a filter capable of sequentially transmitting a specific wavelength to the front portion of the fourth infrared sensor 36 to detect the gas concentration of a specific component. The fourth infrared sensor 36 is configured to detect the energy of a specific wavelength of infrared rays flowing through the filter and output an electric signal proportional to it. In addition, optionally, the filter of the fourth infrared sensor 36 is provided with a filter having an infrared transmission characteristic different from that of the first infrared sensor 30, so that the first infrared sensor 30/third infrared sensor 34 and third filter are provided. 4 The infrared sensor 36 may be configured to measure the concentration of different components.

The third infrared sensor 34 is an infrared sensor equipped with an FPI filter, and is disposed at the lower right of the case 10 (refer to FIG. 1 ). The third infrared sensor 34 has a function of adjusting a specific wavelength of the incoming infrared rays, detects a signal accordingly, outputs an electric signal proportional to this, and sequentially outputs the voltage according to the change of the infrared wavelength. Measure with.

The first, third, and fourth infrared sensors transmit 10.5 µm infrared rays from 3.1 µm infrared rays by adjusting the driving voltage of the FPI filter so that the infrared transmission regions are different from each other, and transmit infrared rays at regular intervals (for example, 30 to 50). nm) to enable infrared sensor array. Therefore, it is possible to configure the optical sensor array having a specific absorption wavelength of about 80 to 120.

The controller can measure the gas concentration of a specific component in the introduced gas by receiving and processing signals output from the first, second, third, and fourth infrared sensors 30, 32, 34, and 36. Among these components, the concentration of volatile organic compounds (eg, methane, ethane, acetylene, toluene, ethylene, etc.) can be detected to diagnose the presence of cancer early.

The gas flowing through the inlet 70 is a breath or fermentation (or ripening) gas of the specimen, and the specimen is one of urine, feces, blood, sweat, saliva, and hormones of the patient.

Figure 4d is a block diagram showing the components and signal processing system diagram of the optical gas device for early cancer diagnosis.

The OP amplifier 140 is connected to the first, second, third, and fourth infrared sensors 30, 32, 34, 36, amplifies the received signal to a higher voltage, and transmits the amplified signal to the ADC 160 do. To this end, the OP amplifier 140 has four channels of amplification circuit.

ADC (Analog-to-Digital Converter, 160) converts the analog signal received from the OP amplifier 140 to a digital signal. The ADC 160 transmits a digital signal to the control unit 200.

The control unit 200 is connected to the central wavelength control unit 180, is connected to the pulse generator 210, the output signal of the control unit 200 is a DAC (Digital-to-Analog Converter, 230) and / or RS485 (240) It is sent out through the port. The control unit 200 may be implemented by an MCU (eg, dsPIC30F4013).

The central wavelength control unit 180 receives the output signals of the first, second, third, and fourth infrared sensors 30, 32, 34, and 36, and the first, second, third, and fourth infrared sensors 30, 32, 34, Each center wavelength can be adjusted by controlling the voltage applied to 36).

The pulse generator 210 receives a command from the control unit 200 and transmits a pulse signal to the light source 20.

The first valve 250 is installed at the inlet 70 side to block or unblock the inflow of gas. To this end, the first valve 250 may be a solenoid valve.

The second valve 260 is installed at the outlet 75 side to block or unblock the discharge of gas. To this end, the second valve 260 may be a solenoid valve.

The pump 270 is installed in the vicinity of the first valve 250 and serves to supply gas to the cavity 15.

Example action

Hereinafter, the operation of the preferred embodiment will be described in detail with reference to the accompanying drawings. As a background technology for operation, analysis of VOCs by etiology according to microbial changes in the intestine and excretion of specific patients (colorectal cancer, CD, liver cancer, BAD, etc.) and lung cancer, Chronic Obstructive Pulmonary Disease (COPD), breast cancer, Electronic nose (Gas Chromatography/Mass Spectroscopy) analysis, Oxide semiconductor [ www.alpha-mos.com ] or Nanocomposite sensor array [ www.sensigent.com ] for early diagnosis through respiratory gas analysis in patients with liver cancer Electronic-Nose) is used.

Among the concentration analysis techniques of VOCs, the GC/MS method has secured a large amount of accurate databases, but it takes about 4 to 5 hours for quantitative analysis, which takes a long time to confirm the disease, and the equipment is expensive, so it can be used in small hospitals. It is difficult to equip.

In addition, even if VOCs that cause etiology are detected according to the GC/MS method, it is a condition requiring diagnosis of liver cancer and colon cancer through an additional high-reliability biopsy or colonoscopy. Is extremely preferred.

Of the papers related to the medical approach of the electronic nose (EN) studied to date, 24% are types of sensors, 19% are objects, 18% EN, 15% are clinical, 14% are carcinoma, 7% are sensors The chemical reaction, 2% is for data analysis, 1% for other etiologies. Gas sensors used in electronic noses typically check the pattern for various VOCs by recognizing the change in the surface resistance of the sensor when it comes into contact with VOCs in a heated state of about 150 to 450 ℃.

At this time, a problem arises in the stability of organic/inorganic compounds, and this requires regular inspection and calibration. Therefore, periodic calibration is not involved, and research on non-chemical gas sensors that require stable sensor characteristics for a long period of time is indispensable.

FIG. 2 is an operation state diagram showing a reflection path of the infrared ray 80 when the optical sensor 100 shown in FIG. 1 operates. 2, an embodiment of the present invention uses a structure that dramatically increases the optical path using a white cell structure. The light (light) irradiated from the light source 20 through the white cell structure allows the collected infrared rays to reach the first, second, third, and fourth infrared sensors 30, 32, 34, 36 without using a separate lens.

And, the infrared light 80 irradiated from one light source 20 passes through two white cell structures and is designed to be divided into four light (lights). Of these, two long light paths (light) are incident on the first and fourth infrared sensors 30 and 36. Then, the remaining two lights (light) reach the second and third infrared sensors 32 and 34, and are used as a standard when measuring broadband, multi-gas, or determining and compensating for sensor output compensation or secular variation. At this time, the energy received from the infrared detector follows the following Lambert-Beer's Law.

Here, I _d is the light energy in the infrared detector, I _o is the initial light energy, a is the absorption coefficient of the gas, x is the concentration of the gas, L is the optical path.

As shown in FIGS. 1 and 2, the infrared ray 80 that finally passes through the white cell structure has about 12 reflections, and the optical path at this time is about 767 mm. And, the infrared ray 80 irradiated from the light source 20 has a radioactivity in the direction of ±30° from the optical axis. At this time, among the light deviating more than ±13° from the optical axis, the seventh reflector 57 and the eighth reflector 58 are respectively reflected. There are two paths. There are second and third infrared sensors 32 and 34 that can measure the reference voltage where this light (light) is collected.

3 is a graph of a simulation analysis showing the incident energy of each sensor when light irradiated from the light source 20 is reflected symmetrically, and FIG. 3A is an incident energy graph of the first infrared sensor (gas sensor) 30, 3B is a graph of incident energy of the fourth infrared sensor (gas sensor) 36, FIG. 3C is a graph of incident energy of the second infrared sensor (reference sensor) 32, and FIG. 3D is a third infrared sensor (reference sensor) ( 34).

3A and 3B are energy incident on the first and fourth infrared sensors 30 and 36, respectively, after light (light) irradiated from the light source 20 reflects the white cell structure 12 times. 3C and 3D, the light irradiated from the light source 20 has a radiation range of about ±30° with the optical axis, and the irradiated light has first and second reflectors 60 and 65 arranged parallel to the optical axis. It is the amount of incident energy of light that is reflected directly to the seventh and eighth reflectors 57 and 58 that do not encounter each other. As shown in FIG. 3, infrared rays 80 having a continuous wavelength emitted from the light source 20 are irradiated to the 1.2 mm×1.2 mm active regions of the first, second, third, and fourth infrared sensors 30, 32, 34, and 36, respectively. do. [Table 4] is a table showing the amount of energy incident on each infrared sensor.

Left incident energy (W) Right incident energy (W) Gas sensor (light path 767mm) 0.0076 0.0073 Reference sensor (light path 96mm) 0.0023 0.0016

On the other hand, Figure 4 shows an example of the measurement results for the optical gas device for early cancer diagnosis to be secured in the present invention.

FIG. 4A shows the output voltage of the infrared sensor according to the central wavelength in the nitrogen gas state and the ethanol and carbon dioxide gas using an infrared sensor (LFP-3144C-337) equipped with an FPI filter provided by Infratec (Dresden, Germany). Shows the actual measurement result of the voltage difference according to the change in the center wavelength in the presence of. As shown in FIG. 4A, the measurement result shows that there is a change in the output voltage in a specific wavelength region (only near the infrared absorption region of ethanol and carbon dioxide gas shown in [Table 5]) in 2000 ppm of ethanol and 500 ppm of carbon dioxide. Can be. In the case of carbon dioxide gas as an example, it can be determined that the production of a more sophisticated gas sensor is possible by summing the outputs of the central wavelengths where the output voltage difference is generated and analyzing the correlation between these voltages and the gas concentration. . In addition, since the infrared sensor does not react with any gas at the central wavelength of 3.91 μm, the reference voltage output state can be indicated, so it has the advantage of being able to perform two functions with one infrared sensor.

Looking at the case of FIG. 4B, which shows the change in the cumulative output voltage by adding the output of a certain portion of the central wavelength according to the change in the carbon dioxide gas concentration to which the above-mentioned matter is actually applied, the cumulative voltage increases and the measurement increases as the gas concentration increases. It can be seen that it is also possible to fabricate a sensor that has an error of 5% or less and can predict the entire concentration section. In addition, as can be seen in [Table 5], carbon dioxide was 4.26㎛, acetone was 5.80㎛, toluene and butyrate were respectively 6.65/6.80㎛, butyrate alone was 8.50㎛, and acetone was near 9.38㎛. The cumulative calculation shows that the presence or absence of the target gas can be measured even in a low concentration range. Therefore, the presence of a specific biomarker and the concentration calculation can also be performed in parallel, thereby securing the advantage of accurate diagnosis.

Figure 4c shows the results of the principal component analysis (Principal components analysis) in a state in which various biomarkers are mixed with a sensor device equipped with only one infrared sensor (LFP-3144C-337) equipped with an FPI filter. However, in FIG. 4c, sprite means carbonated drinking water, CK1 means perfume, M means methanol, I means isopropyl alcohol, A means acetone, and T means toluene liquid. It shows the result of analyzing the gases flowing into the sensor through the nitrogen gas by flowing nitrogen gas to these mixed liquids. As can be seen in FIG. 4c, it was impossible to distinguish between CK1 and methanol, but the infrared sensor equipped with an FPI filter for sprites and M, M+I, M+I+A, and M+I+A+T gases ( LFP-3144C-337) It can be confirmed that the presence or absence of a specific gas could be accurately determined by using only one. That is, it is possible to accurately distinguish the presence or absence of biomarkers (acetone, ethanol, toluene, isopropyl alcohol, etc.) belonging to the excrement of various cancer patients.

Therefore, through the combination of three or more sensors equipped with FPI, the reason for limiting to three or more is, as shown in [Table 5], looking at the infrared absorption wavelengths of known biomarkers, 3.1 ~ 4.4 ㎛ band, Since it is known to mainly absorb infrared rays in the 5.5 to 8.0 μm band and 8.0 to 10.5 μm band, it can be determined that all the biomarkers shown in [Table 5] can be detected. In addition, a combination of these three infrared sensors and a reference sensor for determining the deterioration of the infrared light source (Reference IR sensor, an infrared sensor with a narrowband filter with a central wavelength of 3.91 µm) was manufactured, and the presence or absence of a specific gas was produced. An optical gas device equipped with an algorithm capable of determining (for example, a principal component analysis algorithm) can accurately determine the presence or absence of cancer or various diseases by accurately determining biomarkers contained in fermentation gas of human feces.

Figure 4d is a block diagram showing the components and signal processing system diagram of the optical gas device for early cancer diagnosis. As illustrated in FIG. 4D, the power supply unit 220 is divided into two analog/digital power sources to provide separate power for analog signals and digital signal processing. One light source 20 irradiates the infrared ray 80 through the pulse generator 210. Since there may be a very small amount of biomarkers in the optical sensor 100, the first and second valves 250 and 260 of the inlet 70 and the outlet 75 of the optical sensor 100 are controlled to control gas inflow and outflow.

Then, after storing the output voltage in a gas state in which the organic mixture gas does not exist, the pump 270 is used for a certain period of time (a time in which a gas having a volume slightly larger than the internal volume of the cavity 15 can be sucked). Inhale the sample gas. Then, after measuring the target gas for a certain period of time (which makes it possible to measure about 5 times), the difference between the results is obtained, and the primary component (Principal Component Analysis, PCA) analysis is performed to enable early cancer diagnosis. .

In addition, the first, third, and fourth infrared sensors 30, 34, and 36 use an infrared sensor equipped with an FPI filter 120. A voltage regulation circuit is built in the central wavelength control unit 180 for adjusting the central wavelength of the FPI filter 120. The central wavelength control unit 180 measures the supplied voltage and returns it to ensure the accuracy of the filter regulation voltage. The output voltage of the sensor according to the change in the center wavelength in each sensor is amplified through the OP amplifier 140 having a small offset voltage, and then converted into a digital signal through the ADC 160. In the converted digital signal, an algorithm (PCA or discriminant gas analysis) for analyzing biomarkers present in the mixed gas is performed by the control unit 200. It is configured to diagnose cancer or disease at an early stage by outputting the result through DAC 230 or RS485 240 communication.

The detailed description of preferred embodiments of the present invention disclosed as described above has been provided to enable those skilled in the art to implement and practice the present invention. Although described above with reference to preferred embodiments of the present invention, those skilled in the art will appreciate that various modifications and changes can be made to the present invention without departing from the scope of the present invention. For example, those skilled in the art can use each of the configurations described in the above-described embodiments in a manner of combining with each other. Accordingly, the present invention is not intended to be limited to the embodiments presented herein, but to give the broadest scope consistent with the principles and novel features disclosed herein.

The present invention may be embodied in other specific forms without departing from the spirit and essential features of the present invention. Accordingly, the above detailed description should not be construed as limiting in all respects, but should be considered illustrative. The scope of the invention should be determined by rational interpretation of the appended claims, and all changes within the equivalent scope of the invention are included in the scope of the invention. The present invention is not intended to be limited to the embodiments presented herein, but to give the broadest scope consistent with the principles and novel features disclosed herein. In addition, in the claims, claims that do not have an explicit citation relationship may be combined to constitute an embodiment, or may be included as new claims by amendment after filing.

10: case,
15: cavity,
20: light source,
30: first infrared sensor,
32: second infrared sensor,
34: third infrared sensor,
36: fourth infrared sensor,
50: third reflector,
52: fourth reflector,
54: fifth reflector,
56: sixth reflector,
57: seventh reflector,
58: eighth reflector,
60: first reflector,
65: second reflector,
70: inlet,
75: outlet,
80: infrared,
100: sensor.
120: FPI filter,
140: OP amplifier,
160: ADC,
180: central wavelength control unit,
200: control unit,
210: pulse generator,
220: control unit,
230: DAC,
240: RS485.
250: first valve,
260: second valve,
270: pump.

Claims (13)

A case 10 in which a cavity 15 is formed, an inlet 70 through which gas is introduced, and an outlet 75 through which the gas is discharged;
A light source 20 provided on the cavity 15;
A first reflector 60 reflecting light irradiated from the light source 20 in a first direction;
A seventh reflector 57 for reflecting light incident from the first reflector 60;
A third reflector 50 and a fourth reflector 52 provided to face the seventh reflector 57;
A first infrared sensor 30 provided on one side of the seventh reflector 57 and the third and fourth reflectors 50 and 52;
A second infrared sensor 32 provided on the other side of the seventh reflector 57 and the third and fourth reflectors 50 and 52;
An eighth reflector 58 for reflecting light incident from the second reflector 65;
A fifth reflector 54 and a sixth reflector 56 provided to face the eighth reflector 58;
A third infrared sensor 34 provided on one side of the eighth reflector 58 and the fifth and sixth reflectors 54 and 56; And
And a fourth infrared sensor (36) provided on the other side of the eighth reflector (58) and the fifth and sixth reflectors (54,56). According to claim 1,
The light source 20 is an optical sensor for early cancer diagnosis, characterized in that provided in the central region of the cavity (15). According to claim 1,
One of the first infrared sensor 30 and the second infrared sensor 32 is a reference sensor, and the other is an optical sensor for early cancer diagnosis, further comprising an FPI filter 120. According to claim 1,
At least one of the third infrared sensor 34 and the fourth infrared sensor 36 is an optical sensor for early cancer diagnosis, characterized in that the sensor with an FPI filter (120). According to claim 1,
The case 10 is a rectangular shape,
The first, 2, 3, 4 infrared sensors (30, 32, 34, 36) are early optical sensors for cancer diagnosis, characterized in that provided in each corner area of the rectangular shape. According to claim 1,
The gas is an optical sensor for early cancer diagnosis, characterized in that the fermentation gas of respiration or temporary samples. The method of claim 6,
The temporary sample is urine, feces, blood, sweat, saliva, an optical sensor for early cancer diagnosis, characterized in that one of the hormone. According to claim 1,
At least two of the first, 2, 3, and 4 infrared sensors 30, 32, 34, and 36 have a built-in FPI filter 120 capable of detecting the concentration of volatile organic compounds contained in the fermentation gas. Optical sensor for early cancer diagnosis. A case 10 in which a cavity 15 is formed, an inlet 70 through which gas is introduced, and an outlet 75 through which the gas is discharged; A light source 20 provided on the cavity 15; A first reflector 60 reflecting light irradiated from the light source 20 in a first direction; A seventh reflector 57 for reflecting light incident from the first reflector 60; A third reflector 50 and a fourth reflector 52 provided to face the seventh reflector 57; A first infrared sensor 30 provided on one side of the seventh reflector 57 and the third and fourth reflectors 50 and 52; A second infrared sensor 32 provided on the other side of the seventh reflector 57 and the third and fourth reflectors 50 and 52; An eighth reflector 58 for reflecting light incident from the second reflector 65; A fifth reflector 54 and a sixth reflector 56 provided to face the eighth reflector 58; A third infrared sensor 34 provided on one side of the eighth reflector 58 and the fifth and sixth reflectors 54 and 56; And a fourth infrared sensor 36 provided on the other side of the eighth reflector 58 and the fifth and sixth reflectors 54 and 56;
Any one of the first, second, third, and fourth infrared sensors 30, 32, 34, and 36 is a reference sensor, and the FPI filter 120 further included in the remaining sensors;
A center wavelength control unit 180 for controlling the center wavelength of the FPI filter 120 based on the output signals of the first, second, third, and fourth infrared sensors 30, 32, 34, and 36; And
And a control unit (200) for recognizing a biomarker based on the output signals of the first, second, third, and fourth infrared sensors (30, 32, 34, 36). The method of claim 9,
The central wavelength control unit 180 controls the voltage applied to the FPI filter 120 to control the central wavelength. The method of claim 9,
The infrared absorption wavelength of the biomarker is 3.1 ~ 4.4 μm band, 5.5 ~ 8.0 μm band, 8.0 ~ 10.5 μm optical sensor device for early cancer diagnosis, characterized in that at least one of the band. The method of claim 9,
A first valve 250 installed at the inlet 70 side to control the inflow of the gas;
A second valve 260 installed at the outlet 75 to control the discharge of the gas; And
And a pump (270) for introducing the gas into the cavity (15). The method of claim 12,
The control unit 200 controls the operation of the first and second valves 250 and 260 and the pump 270, an optical sensor device for early cancer diagnosis.

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