KR102472080B1 - Portable fiber optics localized surface plasmon resonance measuring apparatus for ultra precise measurement - Google Patents

Abstract

The present invention relates to a portable optical fiber localized surface plasmon resonance measurement device for ultra-precision measurement. According to the present invention, in the portable fiber optic localized surface plasmon resonance measuring device for ultra-precision measurement, a sensor cartridge containing a sample to be measured or a buffer solution is coupled to a coupling part through a connector, and the sensor cartridge through an internal optical fiber. A laser unit that irradiates a laser into the inside of the sensor cartridge, a reflected light measuring unit that measures the intensity of the reflected light reflected from the inside of the sensor cartridge and converts it into a digital voltage, and the reflected light intensity measured by the reflected light measuring unit measures the reflected light intensity measured by the laser unit. It includes a reflected light control unit that adjusts the intensity of the reflected light so that the ratio is three times higher than the intensity of the reflected light, and an analysis unit that determines the infection status of the sample as positive or negative according to the change rate of the measured voltage value.
As described above, according to the present invention, the portable FO-LSPR measuring device is miniaturized so that it can be carried, so that the user can easily check for infection even outside the designated place. In addition, since accurate diagnosis is possible even when the laser is output at a size corresponding to 10 to 20% of the maximum output value, power consumption can be minimized. In addition, by adjusting and analyzing the intensity of the reflected light reflected from the sensor cartridge in a microscopic unit, measurement accuracy may be improved.

Description

Portable optical fiber local surface plasmon resonance measurement device for ultra-precision measurement

The present invention relates to a portable fiber optic localized surface plasmon resonance measuring device for ultra-precise measurement, and more particularly, ultra-precision measurement for determining whether or not a sample is infected by precisely measuring laser reflected from the inside of a sensor cartridge through an optical fiber. It relates to a portable optical fiber localized surface plasmon resonance measurement device for

BACKGROUND ART With the development of molecular biology and biochemistry, research for the detection and analysis of biological materials is being actively conducted for the interpretation of life phenomena based on chemical actions of biological materials.

In particular, Surface Enhanced Raman Scattering (hereinafter referred to as SERS), one of the Raman scattering methods that apply spectroscopic techniques to measuring biological materials, and fiber localized surface plasmon resonance, one of the surface plasmon resonance methods. (Fiber Optics Localized Surface Plasmon Resonance) is attracting attention, and based on this technique, detection of biological materials is gradually being widely applied in the bio and medical fields.

However, most diagnostic devices currently used for genetic diagnosis are mostly for laboratory use, and are not suitable for portable use, such as convenience, power consumption, and size, and thus have limitations in on-site inspection.

For example, in the case of COVID-19, a recent infectious disease, in the case of PCR analysis, which is the most reliable and widely used technique, not only is the place where the sample is collected and the place where it is tested are separated, but the time required is about 6 hours. situation is required. Of course, there is a rapid antigen test kit, but it has a problem in that it has limitations in its use because of its low sensitivity and specificity.

The background technology of the present invention is disclosed in Korean Patent Publication No. 10-2013-0102874 (published on September 23, 2013).

A technical problem to be achieved by the present invention relates to a portable optical fiber localized surface plasmon resonance measuring device for ultra-precise measurement that accurately measures laser reflected from the inside of a sensor cartridge through an optical fiber to determine whether or not a sample is infected.

According to an embodiment of the present invention for achieving this technical problem, in a portable fiber optic localized surface plasmon resonance measuring device for ultra-precision measurement, a sensor cartridge containing a sample or buffer solution to be measured and a coupling part coupled through a connector , a laser unit for radiating a laser into the sensor cartridge through an internal optical fiber, a reflected light measurement unit that measures the intensity of reflected light reflected from the inside of the sensor cartridge and converts it into a digital voltage, and the reflected light measurement unit A reflected light control unit that adjusts the intensity of the reflected light so that the measured reflected light intensity is three times higher than the reflected light intensity measured by the laser unit, and the infection status of the sample is positive or negative according to the rate of change of the measured voltage value. It includes an analysis unit that judges as

It may further include a display unit for displaying the positive or negative result on a screen.

The sensor cartridge has an antibody for carrying out an antigen-antibody reaction with the sample attached therein, and when the sample is injected through the inlet, the sample moved to the central groove proceeds with the antibody-antigen reaction with the previously attached antibody. And, when the buffer solution is injected through the inlet, a portion of the sample and the buffer solution may be discharged through the outlet.

The sensor cartridge may be detachable.

The sample includes at least one of droplets, saliva, mucus, blood and urine of the subject to be measured, and the antibody may be an antibody for examining at least one infectious disease among corona, malaria, dengue fever, sexually transmitted diseases and syphilis.

The laser unit may output a laser having a size between 10% and 20% of an allowable value compared to a maximum output value.

The optical fiber may be implemented in the form of a 2x1 optical fiber coupler in which an incident path for injecting laser into the sensor cartridge and a reflection path for outputting reflected light reflected from the inside of the sensor cartridge are separated. .

An optical fiber cartridge that prevents the optical fibers from being twisted with each other may be further included.

The reflected light measuring unit may measure the reflected light with an accuracy of 0.01 mV.

When the laser is irradiated in a state in which only the buffer solution is initially injected into the sensor cartridge, a control unit not to proceed to the next step when the voltage of the measured reflected light is 90 mV or less may be further included.

When the voltage of the reflected light is measured to be greater than 90 mV, the control unit calculates an average voltage value (V ₀ ) of the reflected light measured between 15 and 20 seconds from the time of irradiating the laser, and after injecting the sample After washing the sensor cartridge by injecting a buffer solution, an average voltage value (V ₁ ) of the reflected light measured between 35 and 40 seconds from the point of irradiation of the laser may be calculated.

The control unit may calculate a rate of change (R) of the measured voltage value through the following equation.

The analyzer determines that the rate of change (R) of the voltage value is greater than the reference value as being positive for the corresponding infectious disease, and if the rate of change (R) of the voltage value is less than the reference value, it can be determined as being negative for the corresponding infectious disease. .

As described above, according to the present invention, the portable optical fiber localized surface plasmon resonance measurement device is miniaturized to be portable, so that the user can easily check for infection even outside the designated place. In addition, since accurate diagnosis is possible even when the laser is output at a size corresponding to 10 to 20% of the maximum output value, power consumption can be minimized. In addition, by adjusting and analyzing the intensity of the reflected light reflected from the sensor cartridge in a microscopic unit, measurement accuracy may be improved.

1 is a configuration diagram for explaining the configuration of a portable optical fiber localized surface plasmon resonance measurement device for ultra-precision measurement according to an embodiment of the present invention.
2 is a view for explaining the outside of a portable optical fiber localized surface plasmon resonance measurement device for ultra-precision measurement according to an embodiment of the present invention.
3 is a diagram for explaining an optical fiber.
4 is a diagram for explaining an optical fiber cartridge.
5A is a view for explaining a sensor cartridge coupled to a portable optical fiber localized surface plasmon resonance measurement device.
FIG. 5B is a view for explaining the inside of the sensor cartridge shown in FIG. 5A.
6 is a flowchart illustrating a high-precision measurement method using a portable optical fiber localized surface plasmon resonance measurement apparatus according to an embodiment of the present invention.
FIG. 7 is a diagram for explaining step S650 of FIG. 6 .

Hereinafter, embodiments of the present invention will be described in detail so that those skilled in the art can easily practice with reference to the accompanying drawings. However, the present invention may be embodied in many different forms and is not limited to the embodiments described herein. In addition, in order to clearly explain the present invention in the drawings, parts irrelevant to the description are omitted, and similar reference numerals are attached to similar parts throughout the specification.

Throughout the specification, when a certain component is said to "include", it means that it may further include other components without excluding other components unless otherwise stated.

Then, with reference to the accompanying drawings, an embodiment of the present invention will be described in detail so that those skilled in the art can easily practice it.

Hereinafter, using FIGS. 1 to 4 , a portable optical fiber localized surface plasmon resonance (hereinafter referred to as "FO-LSPR") measurement device (100) for ultra-precision measurement according to an embodiment of the present invention. ) is explained.

1 is a configuration diagram for explaining the configuration of a portable FO-LSPR measurement device for ultra-precision measurement according to an embodiment of the present invention, and FIG. 2 is a portable FO-LSPR measurement device for ultra-precision measurement according to an embodiment of the present invention. It is a drawing showing the outside of

As shown in FIG. 1, the portable FO-LSPR measuring device 100 for ultra-precision measurement according to an embodiment of the present invention includes a coupling unit 110, a laser unit 120, a reflected light adjusting unit 130, and a reflected light measuring unit. 140, a control unit 150, an analysis unit 160 and a display unit 170.

First, the coupling unit 110 is coupled to a sensor cartridge containing a sample to be measured or a buffer solution through a connector.

Here, the sample includes at least one of droplets, saliva, mucus, blood, and urine of the subject to be measured.

In particular, as shown in FIG. 2, the portable FO-LSPR measuring device 100 according to an embodiment of the present invention has a coupling part 110 formed on the outside so as to be coupled to the sensor cartridge 200, and a connector It is coupled with the sensor cartridge 200 through.

Next, the laser unit 120 radiates a laser into the sensor cartridge 200 through an internal optical fiber.

Here, when the sensor cartridge 200 is coupled to the coupling unit 110 of the portable FO-LSPR measurement device 100, the laser unit 120 irradiates a laser through an optical fiber.

And, the laser unit 120 outputs a laser having a size between 10% and 20% of the allowable value compared to the maximum output value.

Next, the reflected light control unit 130 adjusts the reflected light intensity so that the reflected light intensity measured by the reflected light measurement unit 140 is three times higher than the reflected light intensity measured by the laser unit 120 .

Next, the reflected light measurement unit 140 measures the intensity of the reflected light reflected from the inside of the sensor cartridge 200 and converts it into a digital voltage.

Here, the reflected light measurement unit 140 may measure the reflected light with an accuracy of 0.01 mV.

Next, when the laser is irradiated with only the buffer solution injected into the sensor cartridge 200 initially, the control unit 150 controls not to proceed to the next step if the voltage of the measured reflected light is 90 mV or less.

In the embodiment of the present invention, the reference voltage for determining whether to proceed is set to 90 mV, but the reference voltage may be set differently according to the sample to be measured or the measurement environment.

In addition, the controller 150 controls the measured voltage value of the reflected light reflected from the sensor cartridge 200 into which the buffer solution is injected and the measured voltage value of the reflected light reflected from the sensor cartridge 200 into which the sample of the subject to be measured is injected. Calculate the rate of change of

Next, the analysis unit 160 determines the infection status of the sample as positive or negative according to the rate of change of the measured voltage value.

At this time, the analyzer 160 may set a reference value of the change rate of the voltage value, compare the calculated change rate of the voltage value with a preset reference value, and determine whether the sample is infected according to the comparison result. .

Next, the display unit 170 displays the positive or negative results on the screen.

That is, as shown in FIG. 2 , the display unit 170 has a screen implemented on the exterior of the portable FO-LSPR measurement device 100, and provides a result of the infection status of the measurement subject through the screen.

Hereinafter, the optical fiber cartridge 300 in which the optical fiber is wound will be described in detail using FIGS. 3 and 4 .

3 is a diagram for explaining an optical fiber, and FIG. 4 is a diagram for explaining an optical fiber cartridge.

As shown in FIG. 3, the optical fiber is included inside the portable FO-LSPR measurement device 100, and the outside of the optical fiber is surrounded by a coating that prevents the laser from escaping to the outside.

In addition, the optical fiber is in the form of a 2x1 optical fiber coupler in which an incident path for incident laser to the inside of the sensor cartridge 200 and a reflection path for outputting reflected light reflected from the inside of the sensor cartridge 200 are separated. is implemented

That is, the laser a emitted from the laser unit 120 is incident into the sensor cartridge 200 through the 2x1 optical fiber coupler. The reflected light reflected from the inside of the sensor cartridge 200 is divided into reflected light (b) returning to the laser unit 120 and reflected light (c) output to the reflected light measurement unit 140, and the reflected light control unit 130 controls the reflected light. The reflected light (c) output to the measuring unit 140 is adjusted to be output at three times greater intensity than the reflected light (b) returning to the laser unit 120.

And, as shown in FIG. 4, the optical fiber cartridge 300 may be implemented in a form in which the optical fibers shown in FIG. 3 are wound so that they are not twisted, and may be included inside the portable FO-LSPR measuring device 100.

Hereinafter, the sensor cartridge will be described using FIGS. 5A and 5B.

5A is a view for explaining a sensor cartridge coupled to a portable FO-LSPR measurement device, and FIG. 5B is a view for explaining the inside of the sensor cartridge shown in FIG. 5A.

As shown in FIG. 5A, an inlet 210 and an outlet 220 are formed outside the sensor cartridge 200 coupled to the portable FO-LSPR measuring device, and the sensor cartridge 200 is a portable FO - It is implemented so that it can be easily attached and detached from the LSPR measuring device 100.

Here, the inlet 210 is a place to inject a sample or a buffer solution of a subject to be measured. If the buffer solution is injected through the inlet 210, some of the samples and buffer solutions that do not react with the antigen-antibody among the samples are discharged through the outlet 220. ) is released through

At this time, the optical fiber may be separated into two branches, and an endogenous protein control (Internal Control) for determining an error in an experiment may be attached to one end of the optical fiber, and an infectious disease biomarker to the other end. A ligand can be attached.

More specifically, an optical fiber is mounted inside the sensor cartridge 200 shown in FIG. 5B, and the optical fiber inside the sensor cartridge 200 may be connected to the optical fiber inside the portable FO-LSPR measurement device 100.

In addition, an antibody for performing antigen-antibody reaction with the sample is attached to the end of the optical fiber. At this time, the antibody may be a biomarker antibody for examining at least one infectious disease among corona, malaria, dengue fever, sexually transmitted diseases and syphilis.

Therefore, the examiner injects the sample of the measurement subject through the inlet 210 of the sensor cartridge 200 containing the antibody of the corresponding infectious disease, and the injected sample is placed in the central groove 230 formed in the center of the sensor cartridge 200. , and the antigen-antibody reaction proceeds with the antibody already attached to the end of the optical fiber.

At this time, the laser emitted from the laser unit 120 is irradiated to the sample included in the central groove 230 inside the sensor cartridge 200 through an optical fiber, and the irradiated laser is reflected from the sample reacting with the antigen-antibody and output. .

Hereinafter, an ultra-precision measurement method using the portable FO-LSPR measuring device 100 according to an embodiment of the present invention will be described with reference to FIGS. 6 and 7 .

6 is a flowchart illustrating a high-precision measurement method using a portable FO-LSPR measuring device according to an embodiment of the present invention.

First, the inspector injects a buffer solution into the sensor cartridge 200, and couples the sensor cartridge 200 into which the buffer solution is injected to the coupling part 110 of the portable FO-LSPR measuring device 100 through a connector (S610 ).

Next, while the sensor cartridge 200 is coupled to the coupler 110 , the laser unit 120 radiates a laser beam toward the inside of the sensor cartridge 200 through an optical fiber. Then, the laser beam is transmitted to the buffer solution included in the central groove 230 of the sensor cartridge 200 and then reflected. Then, the reflected light measuring unit 140 measures the reflected light reflected from the buffer solution included in the central groove 230 (S620).

At this time, the reflected light reflected from the buffer solution included in the central groove 230 is divided into the laser unit 120 and the reflected light measurement unit 140, respectively, as described in FIG. The intensity of the reflected light measured by the measuring unit 140 is adjusted so that the intensity of the reflected light returned to the laser unit 120 is three times higher.

In addition, the laser unit 120 may irradiate with an output lower than the maximum output value to minimize heat generation of the laser.

For example, the laser emitted from the laser unit 120 and reflected by the sensor cartridge 200 is divided into the laser unit 120 and the reflected light measurement unit 140, respectively, and the reflected light measured by the laser unit 120 Assuming that the intensity of the reflected light is 1 mV, the voltage of the reflected light measured by the reflected light measuring unit 140 is 3 mV, and may have an intensity three times higher than the intensity of the reflected light returning to the laser unit 120.

In addition, the intensity of the measured reflected light is measured in an analog format and converted into a digital voltage by the reflected light measurement unit 140 .

Next, the controller 150 calculates an average voltage value (V ₀ ) of the reflected light measured between 15 and 20 seconds from the time of irradiating the laser (S630).

For example, the controller 150 may calculate an average voltage value (V ₀ ) of reflected light measured between 15 and 20 seconds as 95 mV.

Next, the control unit 150 determines whether the average voltage of the reflected light measured by the reflected light measurement unit 140 is measured with an intensity greater than 90 mV (S640).

If the calculated average voltage value (V ₀ ) is 90 mV or less, the control unit 150 controls not to proceed to the next step, and re-measures the voltage of the reflected light for the sensor cartridge 200 into which the buffer solution is injected. .

Next, when the average voltage (V ₀ ) of the reflected light is greater than 90 mV, the inspector separates the sensor cartridge 200 from the portable FO-LSPR measuring device 100, and then the sample to be measured in the sensor cartridge 200 After injecting, a buffer solution is additionally injected to wash the sensor cartridge (S645).

If it is desired to check whether the subject to be measured is corona-infected, the inspector injects the sample of the subject to be measured into the sensor cartridge 200 containing the corona antibody at the end of the optical fiber, and then the other parts of the sensor cartridge 200 are washed with a buffer solution. can do.

In addition, the inspector couples the sensor cartridge 200 to the coupling unit 110 of the portable FO-LSPR measuring device 100, and the laser unit 120 samples the antigen-antibody reaction inside the coupled sensor cartridge 200 A laser is irradiated toward, and the reflected light measurement unit 140 measures the reflected light that is reflected by hitting a sample having an antigen-antibody reaction.

Next, the control unit 150 calculates an average voltage value (V ₁ ) of the reflected light measured between 35 and 40 seconds from the time when the laser is irradiated toward the sample reacting with the antigen-antibody (S650).

For example, an average voltage value (V ₁ ) of reflected light measured between 35 and 40 seconds calculated by the controller 150 may be 100 mV.

Hereinafter, a process in which a laser is irradiated to a sample through an optical fiber and then reflected will be described using FIG. 7 .

FIG. 7 is a diagram for explaining step S650 of FIG. 6 .

As shown in FIG. 7, the laser irradiated from the laser unit 120 passes through the optical fiber and is irradiated with the antigen-antibody included in the end of the optical fiber inside the sensor cartridge 200, and the irradiated laser is irradiated with a sample that reacts with the antigen-antibody. It hits and reflects off.

That is, the reflected light measuring unit 140 measures the reflected light that is reflected after being irradiated onto the sample, and the control unit 150 measures the average voltage value of the reflected light measured between 35 and 40 seconds from the time the laser is irradiated toward the sample. Calculate (V ₁ ).

Next, the control unit 150 calculates the change rate of the voltage value using V ₁ and V ₀ (S660).

At this time, the control unit 150 calculates the change rate R of the measured voltage value through Equation 1 below.

Here, V ₁ is an average voltage value of reflected light measured between 35 and 40 seconds, and V ₀ represents an average voltage value of reflected light measured between 15 and 20 seconds.

Then, the analyzer 160 compares the magnitude of the change rate R of the voltage value with the reference value (S670).

At this time, the reference value of the change rate (R) of the voltage value is set to 0.03, and the set reference value may vary depending on the type of infectious disease.

If the change rate (R) of the voltage value is greater than the reference value, the analyzer 160 determines that the corresponding infectious disease is positive (S680).

And, if the change rate (R) of the voltage value is equal to or less than the reference value, the analysis unit 160 determines that the corresponding infectious disease is negative (S685).

That is, when a subject to be measured is infected with a specific disease and the sample causes an antigen-antibody reaction, the change rate of the voltage value of the reflected light is greatly increased. On the other hand, when the subject to be measured is not infected with a specific disease and the sample does not cause an antigen-antibody reaction, the change rate of the voltage value of the reflected light is maintained at a constant value.

For example, assuming that V ₀ is 95 mV and V ₁ is 100 mV, the rate of change (R) of the voltage value for the reflected light of the sample is 0.05, and the analysis unit 160 is positive for the corona infection disease of the subject to be measured. judge by

If the change rate (R) of the voltage value calculated through Equation 1 is 0.03 or less, the analysis unit 160 determines that the subject's corona infection is negative.

Next, the display unit 170 displays the results determined as positive or negative on the screen of the portable FO-LSPR measurement device 100 (S690).

That is, as shown in FIG. 2 , the display unit 170 provides a positive or negative result through a screen so that the infection status of the subject to be measured can be immediately confirmed.

As described above, according to an embodiment of the present invention, the portable FO-LSPR measuring device is miniaturized so that it can be carried, so that the user can easily check for infection even outside the designated place. In addition, since accurate diagnosis is possible even when the laser is output at a size corresponding to 10 to 20% of the maximum output value, power consumption can be minimized. In addition, by adjusting and analyzing the intensity of the reflected light reflected from the sensor cartridge in a microscopic unit, measurement accuracy may be improved.

Although the present invention has been described with reference to the embodiments shown in the drawings, this is only exemplary, and those skilled in the art will understand that various modifications and equivalent other embodiments are possible therefrom. Therefore, the true technical scope of protection of the present invention should be determined by the technical spirit of the appended claims.

100: portable FO-LSPR measuring device, 110: coupling unit,
120: laser unit, 130: reflected light control unit,
140: reflected light measurement unit, 150: control unit,
160: analysis unit, 170: display unit,
200: sensor cartridge, 210: inlet,
220: outlet, 230: central groove,
300: optical fiber cartridge

Claims (13)

In the portable optical fiber localized surface plasmon resonance measuring device for ultra-precision measurement,
A coupling part coupled through a connector with a sensor cartridge containing a sample to be measured or a buffer solution,
A laser unit for irradiating a laser into the sensor cartridge through an internal optical fiber;
A reflected light measurement unit that measures the intensity of the reflected light reflected from the inside of the sensor cartridge and converts it into a digital voltage;
A reflected light control unit for adjusting the intensity of the reflected light so that the reflected light intensity measured by the reflected light measuring unit is three times higher than the reflected light intensity measured by the laser unit;
An analysis unit that determines the infection status of the sample as positive or negative according to the rate of change of the measured voltage value, and
When the laser is irradiated with only the buffer solution initially injected into the sensor cartridge, a portable optical fiber localized surface plasmon resonance measuring device including a control unit to prevent proceeding to the next step when the voltage of the measured reflected light is 90 mV or less. According to claim 1,
Portable optical fiber localized surface plasmon resonance measuring device further comprising a display unit for displaying the result determined as positive or negative on a screen. According to claim 1,
The sensor cartridge,
An antibody for performing an antigen-antibody reaction with the sample is attached therein,
When the sample is injected through the inlet, the sample moved to the central groove proceeds with the antigen-antibody reaction with the previously attached antibody,
When the buffer solution is injected through the inlet, a portable optical fiber localized surface plasmon resonance measuring device that allows a portion of the sample and the buffer solution to be discharged through the outlet. According to claim 1,
The sensor cartridge is a portable optical fiber localized surface plasmon resonance measuring device formed in a detachable type. According to claim 1,
The sample is
It includes at least one of droplets, saliva, mucus, blood and urine of the measurement subject,
Antibodies,
A portable fiber optic localized surface plasmon resonance measuring device that is an antibody for testing at least one infectious disease among corona, malaria, dengue fever, venereal disease and syphilis. According to claim 1,
the laser unit,
A portable optical fiber localized surface plasmon resonance measuring device for outputting a laser having a size between 10% and 20% of the allowable value compared to the maximum output value. According to claim 1,
The optical fiber,
An incident path for injecting a laser to the inside of the sensor cartridge and
A portable optical fiber localized surface plasmon resonance measuring device implemented in the form of a 2x1 optical fiber coupler in which a reflection path for outputting reflected light reflected from the inside of the sensor cartridge is separated. According to claim 7,
A portable optical fiber localized surface plasmon resonance measuring device further comprising an optical fiber cartridge preventing the optical fibers from being twisted with each other. According to claim 1,
The reflected light measuring unit,
A portable fiber optic localized surface plasmon resonance measurement device that measures reflected light with a precision of 0.01 mV. delete According to claim 1,
The control unit,
When the voltage of the reflected light is measured to be greater than 90 mV, an average voltage value (V ₀ ) of the reflected light measured between 15 and 20 seconds from the time of irradiating the laser is calculated,
After injecting the sample, injecting a buffer solution to wash the sensor cartridge, and then calculating the average voltage value (V ₁ ) of the reflected light measured between 35 and 40 seconds from the point of irradiation of the laser, a portable optical fiber localized surface plasmon resonance measuring device. According to claim 11,
The control unit,
A portable optical fiber localized surface plasmon resonance measuring device that calculates the change rate (R) of the measured voltage value through the following equation.

According to claim 12,
The analysis unit,
If the change rate (R) of the voltage value is greater than the reference value, it is determined that the infectious disease is positive,
A portable optical fiber local surface plasmon resonance measuring device that determines that the rate of change (R) of the voltage value is less than the reference value as negative for the infectious disease.

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