KR101297246B1 - A Measuring Apparatus for Agglutination and PDA - Google Patents

Abstract

The present invention provides a chip loading unit in which a measurement sample is mounted; A light source unit including at least one light source for supplying measurement light; The spectacle is connected to any one of the light sources included in the light source unit according to the operator's operation, and supplies the light for measurement supplied from the connected light source to the measurement sample, receives the light passing through the measurement sample, and supplies the light to the detection unit. Optical path means for forming a furnace; And a detection unit for detecting light transmitted through the optical path means.
In addition, according to another aspect of the invention the chip loading unit on which the measurement sample is mounted; A light source unit including at least one light source for supplying measurement light; A first optical fiber connected to the light source unit to irradiate light supplied from the light source unit with a measurement sample mounted to the chip loading unit; A second optical fiber receiving light passing through the measurement sample and supplying the light to a spectroscope; A spectrometer that separates the light supplied from the second optical fiber for each wavelength and detects and outputs light of a specific band; An electrical signal conversion unit for converting the optical signal input from the spectroscope into an electrical signal and outputting the light detected by the spectroscope; And a control unit for determining pathogens and contamination levels of the measurement sample by wavelength information of light of a specific region obtained by analyzing the electrical signal.

Description

Immunoaggregated Scattered Light and Self-luminous Fluorescent Biochip Measuring Device {A Measuring Apparatus for Agglutination and PDA}

The present invention relates to immuno-aggregated scattering light and self-emitting fluorescence biochip measuring apparatus, and more specifically, the presence or absence of pathogens of aggregates by using scattered light that is scattered by irradiating light to agglomerates in which agglutination reaction between the test substance and the antibody immobilized particles occurs. In the immuno-aggregated scattering light and self-fluorescence fluorescent biochip measuring device which can check the contamination level or the embolization reaction of the polydiacetylene (PDA) biochip, which is a self-luminous fluorescent substance, to check the presence of pathogens and the contamination level of the sample to be tested. It is about.

Agglutination is an antigen-antibody reaction that is a kind of immune response. It refers to the aggregation of particles, and it is used not only for immunological research but also for serological diagnosis, determination of blood type, determination of deadlock in transfusion, and identification of bacteria in microbiology. It is widely used as it is used to clarify. On the other hand, the aggregate refers to a state in which the volume is increased after the collision between the particles.

Typical examples of immunoassays include radioimmunoassy (RIA), enzyme immunoassy (EIA), particle aggregation immunoassay and counting immunoassay. However, RIA and EIA have a disadvantage of requiring B (bound) / F ((free)) separation after the antigen-antibody reaction and requiring a lot of time and labor until analysis results are obtained.

Particle aggregation immunoassays have the advantage that the test sample can only be mixed with a suspension of insoluble carrier particles (eg latex particles) in which the antibody or antigen is sensitized. Accordingly, B / F separation is not necessary and can be performed with a simple operation.

In addition, the digital immunoassay is an assay that measures the degree of particle aggregation reaction using serum or plasma. The antigen- or antibody-linked latex particles react with the antigen or antibody in the sample, depending on the total number of antigens or antibodies. Aggregates.

Aggregated latex particles can be counted because of their large size. The total of the non-aggregated latex particles is represented by M (monomer), the sum of at least two aggregated latex particles is represented by P (polymer), and the sum of M and P is represented by T (total). P / T is calculated as the degree of aggregation reaction. If the calibration curve is predetermined by measuring the aggregation reactivity of the antigen or antibody at a known concentration, the amount of antigen or antibody in the sample can be known (Sinkai Etsuro et al .: Principle of Measurement of PAMIA, Sysmex J. Vol. 20 No. 1, pp77-78 (1997). As the aggregated particles are directly counted, this analysis is more accurate than the turbidity immunoassay, which detects optical changes in the entire test sample. Recently, however, it is required to quickly determine whether a patient has been infected with hepatitis virus, HIV or other pathogens, and there is a disadvantage in meeting such a demand for reasons such as time of particle aggregation immunoassay.

On the other hand, the consumption of agricultural and livestock products is rapidly increasing due to the advancement of dietary life, and the agricultural and livestock products are produced in large quantities to meet these demands. It is strengthening.

In particular, in the case of agricultural and livestock products, thorough management and supervision are required from the production stage to distribution as it is directly related to national health. However, it is not easy to have expensive inspection equipment for securing the stability of these foods, and the inspection means also has a complex disadvantage. Accordingly, there is a need for an apparatus capable of detecting various pathogens simply and accurately in place of expensive and expensive inspection equipment that requires complicated and highly labor.

In addition, in the case of a measuring device for detecting pathogens according to the prior art, there is a problem in that one measuring device supports only one type of measuring / detecting method and thus, various methods of measuring / detecting cannot be performed at the same time.

The present invention has been made to solve the problems described above, an embodiment of the present invention is immuno-aggregated scattering light and PDA configured to selectively perform immuno-aggregated scattering light measurement and polydiacetylene (PDA) fluorescent biochip measurement It relates to a fluorescent biochip measuring device.

In order to achieve the object as described above, a preferred embodiment according to the present invention is a chip loading unit is mounted measuring sample; A light source unit including at least one light source for supplying measurement light; Connected to any one of the light sources included in the light source unit according to the operator's operation, the measurement light supplied from the connected light source is supplied to the measurement sample, and the light passing through the measurement sample is supplied to the detection unit. Optical path means for forming an optical path; And it provides a immuno-aggregated scattered light and PDA fluorescence biochip measurement apparatus comprising a detection unit for detecting the light transmitted through the optical path means.

On the other hand, in order to achieve the object as described above, another preferred embodiment according to the present invention is a chip loading unit on which the measurement sample is mounted; A light source unit including at least one light source for supplying measurement light; A first optical fiber connected to the light source unit to irradiate light supplied from the light source unit with a measurement sample mounted to the chip loading unit; A second optical fiber receiving light passing through the measurement sample and supplying the light to a spectroscope; A spectrometer that separates the light supplied from the second optical fiber for each wavelength and detects and outputs light of a specific band; An electrical signal conversion unit for converting the optical signal input from the spectroscope into an electrical signal and outputting the light detected by the spectroscope; And a control unit for determining pathogens and contamination levels of the measurement sample based on wavelength information of light of a specific region obtained by analyzing the electrical signal.

In addition, in order to achieve the object as described above, another preferred embodiment according to the present invention, the chip loading unit is mounted measuring sample; A light source unit coupled to a specific light source module according to a selection of a measurer among at least one light source module to supply light for measurement; The spectacle is connected to any one of the light sources included in the light source unit according to the operator's operation, and supplies the light for measurement supplied from the connected light source to the measurement sample, receives the light passing through the measurement sample, and supplies the light to the detection unit. Optical path means for forming a furnace; And it provides a immuno-aggregated scattered light and PDA fluorescence biochip measurement apparatus comprising a detection unit for detecting the light transmitted through the optical path means.

According to an embodiment of the present invention as described above, first, the immuno-aggregated scattering light and PDA fluorescent biochip measuring apparatus that can be applied to all fields that cause biological affinity such as antigen-antibody reaction and can be used for food safety management Can provide.

Secondly, it is possible to provide an immuno-aggregated scattered light and PDA fluorescent biochip measuring device that can be easily portable to test the pathogen and contamination of the test material in real time.

1 is a perspective view showing an immuno-aggregated scattered light and a PDA fluorescent biochip measuring device according to an embodiment of the present invention,
Figure 2 is a side view of the immuno-aggregated scattered light and PDA fluorescent biochip measurement device shown in Figure 1,
3 is a side conceptual view showing a state in which the components of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 1 are connected by optical fibers;
Figure 4 is a flow chart of the immuno-aggregated scattered light and PDA fluorescent biochip measurement device shown in Figure 1,
5 is a state diagram using the immuno-aggregated scattered light and PDA fluorescent biochip measurement device shown in FIG.
FIG. 6 is a conceptual diagram illustrating a light path using scattered light in a state diagram of use of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 5;
7 is a conceptual diagram showing a path of light for PDA embolism measurement in the state diagram of use of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG.
8 is a perspective view showing an immuno-aggregated scattered light and PDA fluorescent biochip measurement apparatus according to another embodiment of the present invention,
9 is a side view showing a spectrometer employed in the immuno-aggregated scattered light and PDA fluorescence biochip measuring apparatus shown in FIG.
10 is a perspective view showing an immuno-aggregated scattering light and a PDA fluorescent biochip measuring apparatus according to another embodiment of the present invention,
FIG. 11 is a side conceptual view illustrating a state in which components of an embodiment using a single diode of the immuno-aggregated scattering light and the PDA fluorescence biochip measuring apparatus shown in FIG. 10 are connected by optical fibers; FIG.
12 is a flow chart of the immuno-aggregated scattered light and PDA fluorescence biochip measuring apparatus shown in FIG.
FIG. 13 is a conceptual diagram illustrating a light path using scattered light in a state diagram of use of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 11;
FIG. 14 is a conceptual diagram illustrating a path of light for PDA embolism measurement in a state diagram of use of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 11;
FIG. 15 is a side conceptual view illustrating a state in which components of an embodiment using a spectrometer are connected by optical fibers in the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 10;
FIG. 16 is a flow chart of an immunocoagulated scattering light and a PDA fluorescent biochip measuring apparatus shown in FIG. 15;
FIG. 17 is a conceptual diagram illustrating a light migration path using scattered light in a state diagram of use of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 15;
FIG. 18 is a conceptual diagram illustrating a movement path of light for PDA embolism measurement in a state diagram of use of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 15.

1 is a perspective view illustrating an immunoaggregated scattered light and a PDA fluorescent biochip measuring apparatus according to an embodiment of the present invention, FIG. 2 is a side view of the immunoaggregated scattered light and a PDA fluorescent biochip measuring apparatus illustrated in FIG. 1, and FIG. 1 is a side conceptual view showing a state in which the components of the immuno-aggregated scattered light and PDA fluorescent biochip measuring apparatus are connected by optical fibers, and FIG. 4 is a flow chart of the immuno-aggregated scattering light and PDA fluorescent biochip measuring apparatus shown in FIG. FIG. 5 is a diagram illustrating the use of the immunoaggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 1, and FIG. 6 is a diagram illustrating the movement path of the light using the scattered light in the state diagram of the immunoaggregated scattering light and the PDA fluorescent biochip measuring apparatus illustrated in FIG. 5. 7 is a conceptual diagram showing the PDA embolization in the state diagram of the use of the immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. It is a conceptual diagram which shows the movement path of the light for a measurement.

The immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus 1 according to the preferred embodiment (first embodiment) of the present invention include a main body 10, a light source unit 20, a filter slider 30, an optical path unit 40, The detection unit 50 includes a control unit 60 and a display unit 80.

As shown in FIG. 1, the main body 10 is preferably formed in a rectangular parallelepiped shape and small in size to facilitate portability. On the upper side of the main body 10 is provided a chip loading section 11 on which a measurement sample is mounted. The chip loading unit 11 may be replaced by a microfluidic chip 12 for measuring an immunoaggregation reaction or a PDA biochip (not shown) for measuring an PDA embolism reaction. The microfluidic chip 12 has a channel through which the substance to be tested and the antibody stator particles can be introduced, and the light source unit 20 to be described later in the observation window portion in which the aggregate is generated by the aggregation reaction between the test substance and the antibody stator particles. The light transmitted from) is irradiated.

As shown in FIG. 3, the light source 20 is installed inside the main body 10 and supplies light irradiated to the microfluidic chip 12 or the PDA biochip mounted on the chip loading unit 11. 3, the first and second light sources 21 and 22 installed on one side of the main body 10 and the first and second light sources 21 and 22 installed on the inner side of the main body 10, and the chip 20. Ferrule 23 for fixing the first optical fiber 70 connected to the loading unit 11 (installed above the first light source and installed above the first ferrule and the second light source to which the optical fiber 70 is connected / fixed) And a second ferrule to which the first optical fiber 70 is connected / fixed.

Here, the first optical fiber 70 is connected / fixed to the second ferrule installed on the upper side of the first ferrule or the second light source 22 installed on the upper side of the first light source 21 according to the operator's operation Light supplied from the first light source 21 or the second light source 22 is supplied to the measurement sample.

Preferably, the first light source 21 uses an ultraviolet LED (UV LED), and the second light source 22 preferably uses a xenon lamp (or halogen lamp). The xenon lamp can generate a broad spectrum of light from ultraviolet to infrared with high efficiency, and has an output of about 30 to 50W, and its efficiency is very high, which is advantageous in converting 50% of electrical energy into light. have.

The first light source 21 is used as a light source for measuring scattered light, and preferably has a wavelength of 380 nm, and the second light source 22 is used as a light source for detecting a liposome (Liposome) liposome in a PDA (polydiacetylene). It is used and preferably has a wavelength of 220 ~ 720nm.

The above-described polydiacetylene (PDA) is one of conjugated polymers having a change in conductivity, redox potential, absorption or emission spectrum according to the change of environment. Polydiacetylene is a polymerization form of amphiphilic monomers, and diacetylene, which is a monomer, has an advantage of easily self-assembling into a three-dimensional spherical structure in an aqueous solution. The three-dimensional spherical structure thus formed is polymerized between the monomers and the triple bonds adjacent to each other at 254 nm, and the colorless aqueous solution is changed into the blue aqueous solution having the maximum absorption wavelength at 650 nm. Blue polydiacetylene has a characteristic that the color changes according to external environmental factors. For example, when the stimulus is transferred to the PDA structure with access or binding of temperature, pH, chemicals or biomaterials (antibodies, proteins, peptides, DNA), the embolism shifts toward red (increased absorption wavelength 550nm band). Will be done. According to the degree of such external factors, the color transition appears differently, and the fluorescence characteristic that did not appear in blue has the characteristic that the maximum emission energy is stronger in the 630nm portion as the color transition occurs. Examples of sensors that can be recognized through embolization of PDA liposomes include antibody response sensors, peptide and protein reaction sensors, sensors that detect through film form or immobilization on a support, and sensors that use electrical signal conversion. That is, as described above, the antigen-antibody reaction, the peptide reaction, the protein reaction, and the like, by detecting the PDA liposome embolism, the reaction and the degree of the reaction can be measured. PDA biochip refers to a biosensor configured to detect a substance to be measured using the PDA liposome embolism reaction. For example, the PDA biochip for the detection of influenza virus can be used for influenza virus detection by binding the antibody to the ends of the liposomes that have already been made so that the color change for the selective and specific reaction with the antigen can be made.

As described above, the immuno-aggregated scattered light and the PDA fluorescent biochip measuring device can suitably measure two light sources (ultraviolet LED (UV LED), xenon lamp) (or halogen lamp) according to the measurement / analysis target. Is configured for optional use,

In the case of selecting the first light source 21, by measuring the scattered light according to the immunoaggregation reaction, it is possible to detect the presence or absence of contamination of the pathogen of the measurement sample,

When the second light source 22 is selected, a PDA (polydiacetylene, polydiacetylene) liposom (Liposom) by sensing the metabolic reaction is configured to diagnose the presence or absence of pathogens in the measurement sample.

On the other hand, immuno-aggregated scattered light and PDA fluorescence biochip measuring device according to the present invention is to measure the wavelength and the measurement sample of the light supplied to the measurement sample in order to more accurately and efficiently sense the PDA liposome embolism reaction using the second light source as described above It is more preferable to further include the structure which can limit the wavelength of the light transmitted and received by the photodiode 54.

That is, the filter slider 30 for limiting the wavelength of the light supplied to the measurement sample to a single wavelength is preferably installed above the second light source 22 as shown in FIG. 3 and as shown in FIG. 4. Filtering the light emitted from the second light source 22 to a specific wavelength, a slider body (not shown) provided on one side of the main body 10, and a filter that is preferably fitted to the hole formed in the slider body ( Not shown). The filter is configured as a 600 nm bypass filter, preferably configured to pass only light having a wavelength of 600 nm (blue wavelength), which is responsible for the PDA liposome embolism reaction (ie, red embolism reaction). In sensing, light emitted to a measurement sample as a light source is formed into a single wavelength of light (ie, light of blue wavelength) to improve accuracy and efficiency in sensing an embolism reaction.

As shown in FIG. 3, the optical path unit 40 is a light path that guides the light transmitted through the aggregate to be transmitted or scattered to the detection unit 50, which will be described later. 11 is installed on the upper side of the inclined ferrule 41 and the chip loading portion 11 is mainly installed in the upper side of the first light source 21 is transmitted from the first light source (21) to be transmitted to the detection unit 50. The upright ferrule 42 for transmitting the light emitted from the second light source 22 and passing through the PDA biochip to the detection unit 50, and the light flowing into the inclined ferrule 41 and the upright ferrule 42 is detected ( The second optical fiber 43 is connected to the 50 to be delivered.

The detection unit 50 measures the amount of light transmitted from the optical path unit 40 and transmits it to the control unit 60 to be described later. As shown in FIG. 3, the detection unit 50 is installed at one side of the main body 10 and the optical path is provided. The detection unit ferrule 51 to which the second optical fiber 43 of the unit 40 is fixed, and the light collecting lens 52 which is installed above the detection unit ferrule 51 and collects the light flowing through the detection unit ferrule 51. And a filter wheel assembly 53 installed at the main body 10 so as to be positioned below the detection unit ferrule 51 and transmitting the light transmitted through the condenser lens 52 entirely or only a required wavelength. It is installed in the main body 10 to be located below the filter wheel assembly 53 and consists of a photodiode 54 for converting the light transmitted through the filter wheel assembly 53 into a photocurrent to be transmitted to the control unit 60. .

The filter wheel assembly 53 is composed of a filter wheel 53a which is installed to be slidable to the main body 10 and a filter 53b which is preferably fitted to two filter wheels 53a. One of the two filters 53b preferably uses a global transmission filter to transmit scattered light, and the other filter uses a bandpass filter to transmit 550 nm wavelength for PDA. As described above, the color transfer of PDA liposomes occurs when the reaction (combination) occurs from blue (absorption wavelength 600nm) to red (absorption wavelength 550nm), so the filter for sensing the metastasis reaction of the PDA liposome 550nm When the bypass filter is adopted, only the single wavelength light (550 nm red), which is a measurement target for measuring the metabolic reaction, is received by the photodiode 54 so that the light-receiving unit is arranged in the CCD array. Instead of a (CCD array) it can be configured with only a single photodiode 54, there is an advantage that can simplify the device and analysis algorithm, reduce the portability and production cost of the device configuration.

Here, the above-described two filters 53b are selected according to a measurement method that an experimenter (measurer) wants to measure so that the optical path unit 40 is connected.

That is, when the measurer wants to measure the immune coagulation reaction using the scattered light, the first light source 21 is selected as the light source to irradiate light onto the measurement sample through the first optical fiber 70, and the above-described light path One side of the unit 40 is connected to the above-mentioned inclined ferrule 41 and the other side is connected to a transmission filter through which scattered light is transmitted, and transmits scattered light scattered from the measurement sample to the photodiode 54. Will be done.

On the other hand, when the measurer wants to measure the PDA liposome embolism reaction, the second light source 22 is selected as the light source and irradiates 600 nm wavelength light to the measurement sample through the filter slider 30 and the first optical fiber 70. One side of the above-described optical path unit 40 is connected to the above-described upright ferrule 42, and the other side is connected to a bandpass filter to transmit a 550 nm wavelength of the two filters 53b. Light of 550 nm wavelength emitted from the sample will be delivered to the photodiode 54.

The controller 60 acquires light quantity information of a specific region by analyzing the electrical signal transmitted from the detection unit 50, and checks pathogens and contamination levels of the test substance based on the obtained light quantity information. The control unit 60 specifically corresponds to a converter (not shown) for converting an analog electric signal into a digital signal, and a standard intensity and intensity for scattered light in a standard state in which a test substance is not contaminated for measuring immuno-aggregated scattered light. PDA consisting of standard characteristics curve for immunoaggregation reaction and concentration information corresponding to standard intensity and intensity for light of 550nm wavelength from PDA biochip in standard state without reaction for PDA embolism measurement It includes a memory (not shown) that stores a standard characteristic curve for the embolic response.

The control unit 60 compares the intensity and the standard intensity corresponding to the light quantity information obtained by converting the digital signal according to the measurement mode selected by the measurer, confirms the pathogen and contamination level of the test substance according to the comparison result, and sets the standard characteristic curve. Based on the intensity of the light is analyzed.

In more detail, when the measurer selects the immunoaggregated scattering light measurement, the controller 60 compares the light intensity information obtained from the detector 50 with the standard characteristic curve for the immunoaggregation reaction stored in the memory to determine the pathogen of the measurement sample. The presence and pollution level are calculated. On the other hand, when the measurer selects the PDA embolism response measurement, the control unit 60 compares the light intensity information obtained from the detection unit 50 with the standard characteristic curve for the PDA embolism reaction stored in the memory to determine the presence of pathogens and contamination levels in the measurement sample. Will yield.

The display unit 80 displays specific information transmitted from the control unit 60 on the screen. Preferably, display means such as an LCD may be adopted, and may be replaced with other known display means.

FIG. 5 is a diagram illustrating the use of the immunoaggregated scattered light and the PDA fluorescence biochip measuring apparatus shown in FIG. 1, and FIG. 6 is a diagram illustrating the movement path of the light using the scattered light in the state diagram of the immunoaggregated scattering light and the PDA fluorescent biochip measuring apparatus illustrated in FIG. 5. 7 is a conceptual diagram illustrating a path of light for PDA embolism measurement in a state diagram of use of the immunoaggregated scattered light and the PDA fluorescence biochip measuring apparatus illustrated in FIG. 5.

Hereinafter, the immunoaggregated scattering light measurement process of the immunoaggregated scattered light and the PDA fluorescence biochip measuring device 1 according to a preferred embodiment of the present invention will be described with reference to FIGS. 5 to 6.

As described above, the first light source 21 (380 nm ultraviolet LED (UV LED)) is selected as the light source when measuring the immuno-aggregated scattering light, and the first optical fiber 70 is connected to one side of the optical path unit 40. Is connected to the aforementioned inclined ferrule 41 and the other side is connected to a transmission filter through which scattered light is transmitted among the two filters 53b, thereby forming an optical path for immunoaggregated scattered light measurement.

On the other hand, in order to detect the immunoaggregation reaction, the test substance and the antibody stator particles are introduced into each of the channels of the microfluidic chip 12, and the microfluidic chip 12 is mounted in the chip loading part 11.

When the measurement is started in this state, the light irradiated from the first light source 21 passes through the first transmission irradiation lens L, is supplied to the first optical fiber 70, and then the second transmission irradiation lens L is again provided. It passes through and irradiates to the microfluidic chip 12 mounted in the chip loading part 11.

When the light is irradiated from the first light source 21, the microfluidic chip 12 generates scattered light, and the generated scattered light is supplied to the second optical fiber 43 connected through the inclined ferrule 41 to condense the incoming light. The light is collected by the condenser lens 52. Scattered light collected through the condenser lens 52 is supplied to the photodiode 54 through a transmission filter for transmission.

The photodiode 54 converts the received scattered light into a current signal and outputs it to the controller 60. The controller 60 converts the input analog current into digital data to obtain light quantity information of the digitized scattered light. By comparing the obtained light quantity information and the standard characteristic curve for the immunoaggregation reaction stored in the memory, the presence or absence of contamination of the measurement sample is calculated, and the calculated information is stored in the memory and / or output through the display unit 80.

Next, the PDA embolism measurement process of the immunoaggregated scattered light and the PDA fluorescence biochip measuring apparatus 1 according to a preferred embodiment of the present invention will be described with reference to FIGS. 5 and 7.

As described above, the second light source 22 (xenon lamp: 220-720 nm) is selected as the light source when measuring the PDA embolism reaction, and the first optical fiber 70 is connected to the optical path unit 40. One side is connected to the above-described upright ferrule 42, and the other side is connected to a band pass filter (550 nm bandpass filter) so that only light of 550 nm wavelength of the two filters (53b) is transmitted, the sight for measuring PDA embolism response The furnace is constructed.

On the other hand, in order to detect the PDA embolism reaction, a test substance is added to the PDA biochip, and the PDA biochip is mounted on the chip loading unit 11.

When the measurement starts in this state, the light irradiated from the second light source 22 passes through the filter slider 30 (600 nm bandpass filter), and only light of a single wavelength (600 nm) is bypassed, and the bypassed single wavelength ( 600 nm) light is passed through the first transmission lens (L) and supplied to the first optical fiber 70, and then passes through the second transmission irradiation lens (L) to the PDA biochip mounted on the chip loading section (11). Is investigated.

The light passing through the PDA biochip is condensed by the condenser lens 52 that condenses the light that is supplied to the second optical fiber 43 connected through the upright ferrule 42. The light collected through the condenser lens 52 passes through a 550 nm bandpass filter, and only light having a 550 nm wavelength is bypassed, and light of the bypassed 550 nm wavelength is supplied to the photodiode 54.

The photodiode 54 converts the received light of 550nm wavelength into a current signal and outputs it to the controller 60, and the controller 60 converts the input analog current into digital data to obtain light quantity information of the digitized 550nm wavelength light. Then, by comparing the obtained light quantity information and the standard characteristic curve for the PDA embolism reaction stored in the memory to calculate the presence of pathogens and contamination of the measurement sample, the calculated information is stored in the memory and / or via the display unit 80 Will print.

FIG. 8 is a perspective view illustrating an immunoaggregated scattered light and a PDA fluorescent biochip measuring device according to another embodiment of the present invention, and FIG. 9 is a side view illustrating a spectrometer employed in the immunoaggregated scattered light and a PDA fluorescent biochip measuring device shown in FIG. 8. .

According to another embodiment (second embodiment) of the present invention, an immuno-aggregated scattered light and a PDA fluorescent biochip measuring apparatus 100 may include a main body 110, a light source unit 120, a spectrometer 130, an electrical signal conversion unit 140, The controller 150, the communication unit 160, and the display unit 170 are included.

As shown in FIG. 8, the main body 110 is preferably formed in a rectangular parallelepiped shape and small in size to facilitate portability. On the upper side of the main body 110 is provided a chip loading portion 111 that accommodates the test substance and the antibody stator particles. In one embodiment of the present invention, the test material and the antibody stator particles are preferably installed in the form of a microfluidic chip 112 in the chip loading portion 111. The microfluidic chip 112 has a channel and an observation window into which the test substance and the antibody stator particles can be input, respectively, and the light source unit 120 which will be described later in a part where an aggregate is generated by the agglomeration reaction between the test substance and the antibody stator particles. The light transmitted from) is irradiated.

The light source unit 120 is installed on the main body 110 so as to be positioned below the microfluidic chip 112 as shown in FIG. 8, and irradiates aggregates formed on the microfluidic chip 112 mounted to the chip loading unit 111. As for supplying the light, preferably an ultraviolet LED (UV LED) having a wavelength of 380 nm is used. The ultraviolet LED may be replaced or combined with the above-described xenon lamp (or halogen lamp) preferably having a wavelength of 220-720 nm. As described in the above embodiments, the ultraviolet LED is preferably used as a scattering light source, and the xenon lamp (or halogen lamp) is used as a PDA light source.

The spectrometer 130 is installed inside the main body 110 as shown in FIG. 8 and is connected to the microfluidic chip 112 with an optical fiber 70 to detect light irradiated to the aggregates and to be described later. As transmitted to 140, the spectrometer body 131 and the spectrometer body 131 is installed in the main body 110 and the optical inlet 131a is formed on one side is fixed to the second optical fiber as shown in Figure 9, A light collecting slit 132 installed inside and collecting the light flowing into the light inlet 131a into one place, and installed inside the spectrometer body 131 to reflect light transmitted from the light collecting slit 132. The first reflector 133 and the second reflector 134 which is installed inside the spectrometer body 131 and diffuses and reflects the light transmitted from the first reflector 133 for each wavelength band, and the spectrometer body 131 Is installed inside the reflecting light transmitted from the second reflector 134 The detector is installed inside the third reflector 135 and the spectrometer body 131 and receives the light from the third reflector 135 to detect the intensity and is connected to an electrical signal converter 140 to be described later ( 136).

As shown in FIG. 8, the electrical signal converter 140 is installed inside the main body 110 to convert light transmitted through the spectrometer 130 into an electrical signal, and preferably uses a CCD array sensor. .

The controller 150 analyzes the electrical signal transmitted from the electrical signal converter 140 to obtain wavelength information of light in a specific region, and checks pathogens and contamination levels of the test material based on the wavelength information of the light. The control unit 150 specifically includes an converter (not shown) for converting an analog electric signal into a digital signal, and an immunity including concentration information corresponding to standard intensity and intensity for scattered light in a standard state in which the test substance is not immunized. It includes a memory (not shown) that pre-stores the standard characteristic curve of the flocculation reaction, and compares the intensity and standard intensity corresponding to the wavelength information of the light obtained by changing into a digital signal, and according to the comparison result pathogens and Check the contamination level and analyze the concentration according to the intensity of light based on the standard characteristic curve.

The display unit 170 displays specific information transmitted from the control unit 150 on the screen. Preferably, the display unit 170 is installed above the main body 110 and uses an LCD display.

The communication unit 160 is installed inside the main body 110 as shown in FIG. 8, and is connected to a computer or a terminal connected by the control unit 150 to provide concentration analysis information along with confirmed pathogens and contamination levels of the test substance. send. The communication unit 160 preferably uses any one of USB, RS232, CDMA, or IrDA.

10 is a perspective view showing an immuno-aggregated scattered light and a PDA fluorescence biochip measuring device according to another embodiment (third embodiment, fourth embodiment) of the present invention.

Another embodiment (third embodiment, fourth embodiment) of the present invention described below is different from the embodiment described with reference to FIGS. 1 to 9 (first and second embodiments). The scattering light measuring light source and the PDA color transition measuring light source are not configured to be fixedly provided in the measuring apparatus 200, and two light sources (the scattering light measuring light source and the PDA color transition measuring light source) are separately formed as separate light source modules. The biggest difference is that the light source module selected by the measurer is configured to be used in combination with the measuring device.

Due to this difference, in the above-described first and second embodiments, it is necessary to separately configure an optical path by operating an optical fiber, etc. according to the type of light source selected by the measurer as the light source for measurement. Therefore, since the required light source module of the plurality of light source modules is coupled to the measuring device, there is a difference that the optical path itself composed of an optical fiber or the like is almost fixed.

Hereinafter, a third embodiment and a fourth embodiment of the immunoaggregated scattered light and the PDA fluorescence biochip measuring apparatus 100 according to the present invention will be described with reference to FIGS. 10 to 18. .

The immuno-aggregated scattered light and the PDA fluorescence biochip measuring apparatus 200 according to the third and fourth embodiments of the present invention include a main body 210, a light source unit 220, a detection unit 230 or 250, and an electrical signal conversion unit ( Not shown), the control unit 260, the communication unit 270, and a display unit 280.

As shown in FIG. 10, the main body 210 is preferably formed in a rectangular parallelepiped shape and small in size to facilitate portability. On the upper side of the main body 210 is provided a chip loading section 211 is mounted a measurement sample. The chip loading unit 211 may employ a microfluidic chip 212 for measuring an immunoaggregation reaction or a PDA biochip (not shown) for measuring a PDA embolism reaction. The microfluidic chip 212 has a channel through which the test substance and the antibody stator particles can be input, respectively, and is transmitted from the light source unit 220 to be described later to a portion where the aggregate is generated by the agglomeration reaction between the test substance and the antibody stator particles. Light is irradiated. PDA biochip refers to a biosensor configured to detect a substance to be measured using a PDA liposome embolism reaction. For example, the PDA biochip for the detection of influenza virus can be used for influenza virus detection by binding the antibody to the ends of the liposomes that have already been made so that the color change for the selective and specific reaction with the antigen can be made.

The light source unit 220 is installed in the main body 210 to be positioned below the measurement sample as shown in FIG. 10, and supplies light for measurement to the microfluidic chip 212 or the PDA biochip mounted on the chip loading unit 211. Done. As described above, the light source unit according to the third and fourth embodiments of the present invention is configured to combine the light source module selected by the measurer among the plurality of light source modules to supply the light for measurement. More preferably, the light source module used in the present invention is configured to be coupled / fixed to the light source unit according to the present invention, and furthermore, according to the object of the present invention, an ultraviolet LED (UV LED) having a wavelength of 380 nm for measuring scattered light. Any one of the first light source module is configured, the second light source module consisting of a xenon lamp (or halogen lamp) having a wavelength of 220 ~ 720nm for PDA embolism reaction measurement is coupled to the light source unit according to the needs of the measurement Can be configured. It will be apparent to those skilled in the art that the above-described first light source module and second light source module are merely exemplary, and more light source modules and various light source modules may be applied and used.

The detector 230 or 250 detects the light passing through the measurement sample, converts the light into an electrical signal, and outputs the signal to the controller 260. Such a detector according to the present invention may be composed of a single diode detector using a single diode according to the invention (third embodiment), or may be composed of a spectrometer detector using a spectrometer (fourth embodiment). . The detailed configuration of this third embodiment will be described later with reference to FIGS. 11 to 14, and the detailed configuration of the fourth embodiment will be described below with reference to FIGS. 15 to 18.

The controller 260 analyzes the electrical signal transmitted from the detector 230 or 250 to obtain light quantity information of a specific region, and checks pathogens and contamination levels of the test substance based on the obtained light quantity information. The controller 260 specifically corresponds to a converter (not shown) for converting an analog electrical signal into a digital signal, and a standard intensity and intensity for scattered light in a standard state in which a test substance is not contaminated for measuring immunoaggregated scattered light. PDA consisting of standard characteristics curve for immunoaggregation reaction and concentration information corresponding to standard intensity and intensity for light of 550nm wavelength from PDA biochip in standard state without reaction for PDA embolism measurement It includes a memory (not shown) that stores a standard characteristic curve for the embolic response.

The control unit 260 compares the intensity and the standard intensity corresponding to the light quantity information obtained by converting the digital signal according to the measurement mode selected by the measurer, confirms the pathogen and contamination level of the test substance according to the comparison result, and sets the standard characteristic curve. Based on the intensity of the light is analyzed. In more detail, when the measurer selects the immunoaggregated scattered light measurement, the controller 260 compares the light intensity information obtained from the detector with a standard characteristic curve for the immunoaggregation reaction stored in the memory to determine the presence of pathogens and contamination levels in the sample. Will yield. On the other hand, when the measurer selects the PDA embolism response measurement, the controller 260 compares the light quantity information obtained from the detector with the standard characteristic curve for the PDA embolism reaction stored in the memory to calculate the presence of pathogens and the contamination level of the measurement sample. do.

The display unit 280 displays specific information transmitted from the control unit 260 on the screen. Preferably, the display unit 280 is installed above the main body 210 and uses an LCD display.

The communication unit 270 is installed inside the main body 210 as shown in FIG. 10, and is connected to a computer or a terminal connected by the control unit 260 to provide concentration analysis information along with confirmed pathogens and contamination levels of the test substance. send. The communication unit 270 is preferably configured to support at least one or more of a USB, RS232, CDMA or wired / wireless communication scheme that provides an interface by direct connection with the terminal.

FIG. 11 is a side conceptual view illustrating a state in which components of an embodiment using a single diode are connected by optical fibers among the immunoaggregated scattered light and PDA fluorescence biochip measuring apparatus shown in FIG. 10, and FIG. 12 is an immunoaggregated scattered light and PDA fluorescence shown in FIG. FIG. 13 is a flowchart illustrating a biochip measuring apparatus, and FIG. 13 is a conceptual diagram illustrating a light migration path using scattered light in a state diagram of use of the immunoaggregated scattering light and PDA fluorescence biochip measuring apparatus shown in FIG. 11, and FIG. 14 is an immunoaggregated scattering light shown in FIG. It is a conceptual diagram showing the movement path of light for the measurement of PDA embolism in the use state diagram of the PDA fluorescence biochip measuring device.

Hereinafter, the detailed configuration and function of the measuring apparatus according to the third embodiment of the present invention will be described with reference to FIGS. 11 to 14.

More preferably, the light source unit 220 according to the third embodiment of the present invention is coupled to the light source unit according to the selection of the measurer to supply the measurement light with the first light source module 221 or the second light source module 222 and the light source module. The coupling part 224 and the light source part ferrule 223 may be included.

As described above, the first light source module 221 may be configured as an ultraviolet LED (UV LED) for the scattered light measurement, the second light source module 222 is a xenon lamp (xenon lamp) or for the PDA embolism measurement It may consist of a halogen lamp. On the other hand, the light source module according to the present invention is configured in a form that can be coupled / fixed to the light source module coupling unit 224 to be described later, for the coupling / fixing method already adopted a well-known technology more detailed description Will be omitted.

The light source module coupling unit 224 is configured such that a specific light source module specified by the selection of the measurer can be combined / separated according to the operation of the measurer. It is supplied to the light path means (226, 240) through.

The light source unit ferrule 223 is installed above the light source module coupling unit 224 to connect / fix the optical path means (first optical fiber 226), and to supply the measurement sample measurement light through the first optical fiber. Will perform.

On the other hand, the measuring device according to the present invention may include the light path means (226, 240). Here, the optical path means is a light path for moving the light used in the measuring apparatus according to the present invention, that is, the light source connected to the light source unit for supplying the measurement light supplied from the light source module selected / coupled according to the operator's operation to the measurement sample It means a path for receiving and passing the light passing through the path and the measurement sample to the detection unit, the optical path means means a variety of means that can form such an optical path. As described above, the third and fourth embodiments according to the present invention are configured to couple one of the light source modules specified among the plurality of light source modules to the light source module coupling unit 224 according to the selection of the measurer. Compared to the second embodiment, the optical path is fixedly formed.

The optical path means may include a first optical fiber 226 for supplying the measurement light to the measurement sample and an optical path unit 240 for receiving the light passing through the measurement sample and supplying the light to the detection unit 230. .

The first optical fiber 226 is output from the light source module (the first light source module 221 or the second light source module 222) coupled to / fixed to the light source unit ferrule 223 and coupled to / fixed to the light source module coupling unit 224. The measurement light is supplied to the measurement sample mounted on the chip loading unit.

The light passing through the measurement sample mounted on the chip path of the optical path unit 240 is supplied to the detector 250. More preferably, the optical path unit 240 according to the present invention may include a ferrule 241 or 242 and the second optical fiber 243.

The ferrule is configured so that one side of the second optical fiber 243 is connected / fixed to supply the light passing through the measurement sample to the second optical fiber, and more preferably, the upright ferrule 242 or the inclined ferrule 241 according to the selection of the measurer. Any one of the ferrules) may be selectively used in combination. That is, the upright ferrule 242 or the inclined ferrule 241 may be detachably configured at one side of one side of the chip loading unit, and may be coupled to or separated from one side of the chip loading unit according to the selection of the measurer. Therefore, the measurer forms an optical path by selecting a suitable ferrule among the upright ferrule 242 or the inclined ferrule 241 according to the type of measurement and coupling the ferrule to one side of the chip loading unit.

When measuring the scattered light scattered at a certain angle it is more preferable that the oblique ferrule 241 is coupled to one side of the chip loading portion to form an optical path, when measuring the PDA embolism reaction, the upright ferrule 242 is chip loading It is more preferable to form an optical path on one side of the part. Therefore, when measuring scattered light, the first light source module 221 and the inclined ferrule 241 form a set and are coupled to the measuring device. When measuring the PDA embolism reaction, the second light source module 222 and the upright ferrule are measured. 242 is coupled to the measuring device in a set.

The second optical fiber 243 is connected / fixed to the inclined ferrule 241 or the upright ferrule 242 described above to transmit the light flowing through the inclined ferrule 241 or the upright ferrule 242 to the detection unit 250. do.

The detector 250 according to the third embodiment of the present invention may be configured using a single diode. The single diode detector 250 configured using the single diode is configured similarly to the detector 50 according to the first embodiment described above.

That is, the detector 250 according to the third embodiment of the present invention may include a detector ferrule 251, a condenser lens 252, a filter wheel assembly 253, and a photodiode 254.

The detection unit ferrule 251 is installed on one side of the main body 210 and is configured to connect / fix the second optical fiber 243 of the optical path unit 240. The condenser lens 252 is installed on the upper side of the detection unit ferrule 251 and performs a function of condensing the light flowing through the detection unit ferrule 51 and outputting the light to the filter wheel assembly 253. The condenser lens 252 is not an essential configuration in embodiments according to the present invention, and may be selectively included for efficient condensing an optical signal.

The filter wheel assembly 253 is installed on the main body 210 so as to be positioned below the detection unit ferrule 251, and the condenser lens 252 (in the embodiment including the condenser lens, the second optical fiber when the condenser lens is not included) The light transmitted through the entire transmission or to perform the function to transmit only the required wavelengths. The filter wheel assembly 253 is an essential component of the single diode detection unit 250 constructed using a single diode according to the present invention, and the single diode itself has a problem in that it cannot selectively detect light of a specific wavelength band. Therefore, it is a component devised to solve this problem.

The filter wheel assembly 253 is composed of a filter wheel (53a) that is installed to be slidable to the main body 210, and a filter (253b) that is preferably fitted to two of the filter wheel (253a). One of the two filters 253b preferably uses a global transmission filter to transmit scattered light, and the other filter uses a bandpass filter to transmit 550 nm wavelength for PDA. As described above, the color transfer of the PDA liposomes occurs when the reaction (combination) occurs from blue (600 nm) to red (550 nm), so the 550 nm bypass filter is used to detect the color transfer reaction of the PDA liposomes. In case of adoption, only the single wavelength of light (550nm red), which is the measurement target for the measurement of embolism reaction, is configured to be received by the photodiode 254. Instead of using a single photodiode 254 can be configured instead of the configuration, there is an advantage that it is possible to simplify the device and analysis algorithm and to reduce the portability and production cost of the device configuration. Therefore, when the first light source module is coupled to the measurement device for measuring the scattered light, the global transmission filter will be selected among the two filters 253b, and the second light source module is coupled to the measurement device for the PDA embolism response measurement. The band pass filter will be selected from the two filters 253b.

The photodiode 254 is installed in the main body 210 to be positioned below the filter wheel assembly 253 and converts light transmitted through the filter wheel assembly 253 into a current to be transmitted to the controller 260.

In the case of measuring scattered light using the third embodiment configured as described above, as shown in FIG. 13, the first light source module 221 is coupled to the light source module coupling unit 224 to output the measurement light. The output measurement light is supplied to the measurement sample through the first optical fiber 226, and the light passing through the measurement sample is passed to the filter wheel assembly 253 through the inclined ferrule 241 and the second optical fiber 243. Supplied. In this case, since the scattered light is measured, the entire transmissive filter is selected and set among the two filters 253b included in the filter wheel assembly 253. Therefore, all of the light supplied to the filter wheel assembly 253 is output to the photodiode 254.

On the other hand, when measuring the PDA embolism reaction by using a third embodiment configured as described above, as shown in Figure 14, the second light source module 222 is coupled to the light source module coupling unit 224 The measurement light is output, and the output measurement light is supplied to the measurement sample through the first optical fiber 226, and the light passing through the measurement sample passes through the upright ferrule 242 and the second optical fiber 243 through the filter wheel. Supplied to assembly 253. At this time, the PDA embolism is a case of measuring the response, the bandpass filter of the two filters 253b included in the filter wheel assembly 253 is selected and set. Therefore, light belonging to a specific band among the light supplied to the filter wheel assembly 253 is bypassed and output to the photodiode 254.

FIG. 15 is a side conceptual view illustrating a state in which components of an embodiment using a spectrometer are connected by optical fibers among the immunoaggregated scattered light and the PDA fluorescent biochip measuring device shown in FIG. 10, and FIG. 16 is an immunoaggregated scattered light and PDA fluorescent biochip shown in FIG. 15. Figure 17 is a flow chart of the measuring device, Figure 17 is a conceptual diagram showing the movement path of the light using the scattered light in the state of use of the immuno-aggregated scattered light and PDA fluorescence biochip measuring device shown in Figure 15, Figure 18 is an immuno-aggregated scattered light and PDA shown in Figure 15 It is a conceptual diagram showing the path of light for PDA embolism measurement in the state diagram of use of the fluorescent biochip measuring device.

Hereinafter, a detailed configuration and function of the measuring apparatus according to the fourth embodiment of the present invention will be described with reference to FIGS. 15 to 18.

First, the measuring device according to the third embodiment of the present invention described above with reference to FIGS. 11 to 14 and the measuring device according to the fourth embodiment described below differ only in the configuration of the detection unit, Since the detailed configuration and function are the same, the detailed description of the same configuration will be omitted, and the description will be mainly given on the configuration of the detection unit having the difference.

The measuring apparatus according to the fourth embodiment of the present invention may include a light source unit 220, light path means 226 and 240, and a detector 230.

The light source unit 220 according to the fourth exemplary embodiment of the present invention is coupled to the light source unit according to the selection of the measurer to supply the measurement light to the first light source module 221 or the second light source module 222 and the light source module coupling unit ( 224, a light source unit ferrule 223, and the structure and function of the first light source module 221, the second light source module 222, the light source module coupling unit 224, and the light source unit ferrule 223 described above. Same as the third embodiment.

In addition, according to the fourth embodiment of the present invention, the optical path means 226 and 240 are configured to supply the first optical fiber 226 for supplying the measurement light to the measurement sample and the light passing through the measurement sample to the second optical fiber. And a second optical fiber 243 connected to the ferrule (upright ferrule 242 or inclined ferrule 241) and the light received by being connected to the ferrule to the detector 230.

Meanwhile, the detector 230 according to the fourth embodiment of the present invention may be configured using a spectrometer. The spectroscope detector configured using the spectroscope is configured almost similarly to the detector 130 according to the second embodiment described above.

That is, the detection unit according to the fourth embodiment of the present invention may be configured using the spectrometer 230, and more preferably, may further include a detection unit ferrule 251 and a condenser lens 252.

The detection unit ferrule 251 is installed on one side of the main body 210 and is configured to connect / fix the second optical fiber 243 of the optical path unit 240. The condenser lens 252 is installed on the upper side of the detection unit ferrule 251 and performs a function of condensing the light flowing through the detection unit ferrule 51 and outputting the light to the spectrometer 230. The condenser lens 252 is not an essential configuration in embodiments according to the present invention, and may be selectively included for efficient condensing an optical signal.

The spectrometer 230 is installed inside the main body 210 and receives the light passing through the measurement sample through the second optical fiber 243, and selectively receives only light of a specific band according to a preset pass band setting among the received light. It passes through and transmits to the electric signal converter (not shown). In the case of using the spectrometer 230, only the light of a specific band can be selectively supplied to the controller 260 according to a measurer's operation, so that a filter as in the above-described third embodiment is not required, and a finer setting and The advantage is that measurement is possible. It may also be set to function as an all-pass filter when operating the spectrometer. Since the physical and optical configuration of the spectrometer 230 according to the fourth embodiment is the same as the spectrometer 130 according to the second embodiment of the present invention described with reference to FIG. 9, a detailed description thereof will be omitted.

The electrical signal converter is installed inside the main body 210 and converts the light transmitted through the spectrometer 230 into an electrical signal. Preferably, a CCD array sensor may be adopted and used.

When measuring the scattered light using the fourth embodiment configured as described above, as shown in FIG. 17, the first light source module 221 is coupled to the light source module coupling unit 224 to output the measurement light. The output measurement light is supplied to the measurement sample through the first optical fiber 226, and the light passing through the measurement sample is supplied to the spectrometer 230 through the warp ferrule 241 and the second optical fiber 243. . In this case, since the scattered light is measured, the spectrometer 230 is set to allow the entire band (or 380 nm band pass) to pass.

On the other hand, when measuring the PDA embolism reaction using the fourth embodiment configured as described above, as shown in FIG. 18, the second light source module 222 is coupled to the light source module coupling unit 224 The measurement light is output, and the output measurement light is supplied to the measurement sample through the first optical fiber 226, and the light passing through the measurement sample is passed through the upright ferrule 242 and the second optical fiber 243 through a spectrometer ( 230). In this case, since the PDA embolism reaction is measured, the spectrometer 230 is set to separate and output only light of a specific band (550 nm wavelength band pass).

As the present invention can be variously modified by those skilled in the art without departing from the scope of the claims, the technical protection scope of the present invention is not limited to the specific preferred embodiments described above. Do not.

1,100, 200: Immunoaggregated Scattered Light and PDA Fluorescence Biochip Measuring Device
10,110 body
11,111: chip loading part 12,112: microfluidic chip
20,120: light source unit 21: first light source
22: second light source 23: ferrule
30: filter slider 40: optical path unit
41: inclined ferrule 42: upright ferrule
43: second optical fiber 50: detection unit
51 detection unit ferrule 52: condensing lens
53 filter wheel assembly 53a: filter wheel
53b: filter 54: photodiode
60,150 control unit 70,170 display unit
130: spectroscope 131: spectroscope body
131a: light inlet 132: condensing slit
133: first reflecting mirror 134: second reflecting mirror
135: third reflector 136: detection unit
140: electrical signal conversion unit 160: communication unit
70: first optical fiber

Claims (21)

A chip loading unit in which a measurement sample is mounted;
A light source unit including at least one light source for supplying measurement light;
The spectacle is connected to any one of the light sources included in the light source unit according to the operator's operation, and supplies the light for measurement supplied from the connected light source to the measurement sample, receives the light passing through the measurement sample, and supplies the light to the detection unit. Optical path means for forming a furnace; And
And a detection unit for detecting the light transmitted through the optical path means.
The method of claim 1,
The light source unit includes:
A first light source for supplying light for measuring immunocoagulated scattered light;
A second light source for supplying light for PDA embolism reaction measurement;
A first ferrule installed above the first light source to which the optical path means is connected / fixed; And
And a second ferrule installed above the second light source and connected to and fixed to the optical path means.
The method of claim 2,
The light source unit may further include a filter slider disposed between the second light source and the second ferrule to bypass only light of a specific wavelength band among the light supplied from the second light source and to supply the light path to the optical path means. Immunoaggregated scattered light and PDA fluorescent biochip measuring device.
The method of claim 1,
The optical path means,
A first optical fiber connected to any one of the light sources according to an operator's operation, the first optical fiber supplying light for measurement with a measurement sample mounted on the chip loading unit; And
And an optical path unit for supplying the light passing through the measurement sample mounted to the chip loading unit to the detection unit.
5. The method of claim 4,
The light path unit,
A ferrule attached to one side of the chip loading unit to receive the light passing through the measurement sample and supply the light to the connected optical fiber; And
And a second optical fiber for supplying light supplied to the ferrule to the detection unit.
The method of claim 5,
The ferrule,
An inclined ferrule configured to be detachably attached to one side of the chip loading part, and to receive scattered light passing through a measurement sample when the chip loading part is attached to one side of the chip loading part according to a selection of a measurer;
It is detachably configured on one side of the chip loading part, and when attached to one side of the chip loading part according to the selection of the measurer, the chip loading part is attached to one side of the chip loading part according to the choice of the measurer among the upright ferrules. Immunoaggregated scattered light and PDA fluorescence biochip measuring device, characterized in that any one.
The method of claim 1,
Wherein:
A detection unit ferrule to which the optical fiber of the optical path means is fixed;
A filter wheel connected to the detection unit ferrule so that only a specific wavelength of light transmitted through the optical fiber passes; And
And a photodiode for receiving the light transmitted through the filter wheel, converting the light into a current signal, and outputting the photodiode.
The method of claim 7, wherein
The filter wheel includes at least one filter, and the immuno-aggregated scattered light and PDA fluorescent biochip measuring device, characterized in that the operation is operated so that a specific filter is located between the detection unit ferrule and the photodiode according to the operator's operation.
9. The method of claim 8,
The filter wheel,
Transmission filter for measuring immunocoagulated scattered light; And
An immuno-aggregated scattered light and a PDA fluorescence biochip measuring apparatus comprising a bandpass filter for measuring a PDA embolism reaction.
A chip loading unit in which a measurement sample is mounted;
A light source unit including at least one light source for supplying measurement light;
A first optical fiber connected to the light source unit to irradiate light supplied from the light source unit with a measurement sample mounted to the chip loading unit;
A second optical fiber receiving light passing through the measurement sample and supplying the light to a spectroscope;
A spectrometer that separates the light supplied from the second optical fiber for each wavelength and detects and outputs light of a specific band;
An electrical signal converter for converting light of the measurement band output from the spectroscope into an electrical signal and outputting the electrical signal; And
And a control unit configured to determine pathogens and contamination levels of the measurement sample based on wavelength information of light of a specific region obtained by analyzing the electrical signal.
The method of claim 10,
The spectroscope,
A spectroscope body having a light inlet through which an optical fiber is fixed at one side;
A light collecting slit installed inside the body of the spectroscope and collecting light introduced into the light inlet into one place;
A first reflecting mirror installed inside the spectrometer body and reflecting light transmitted from the condensing slit;
A second reflector installed inside the spectrometer body and reflecting the light transmitted from the first reflector by wavelength band;
A third reflector installed inside the spectrometer body and reflecting light transmitted from the second reflector;
And a detection unit installed inside the spectrometer body and detecting the light transmitted from the third reflecting mirror.
The method of claim 10,
The light source unit includes a light source for measuring immunoaggregated scattered light and a light source for measuring PDA embolism reaction.
And the first optical fiber is connected to any one of the light source for measuring immunoaggregated scattering light and the light source for measuring PDA embolism reaction according to an operator's operation.
A chip loading unit in which a measurement sample is mounted;
A light source unit coupled to a light source module according to a selection of a measurer among at least one light source module to supply light for measurement;
A light path connected to the light source unit to supply the measurement light supplied from the light source module selected / combined according to the measurement of the measurer to the measurement sample, and receive light passing through the measurement sample to supply to the detection unit; Light path means; And
And a detection unit for detecting the light transmitted through the optical path means.
The method of claim 13,
The light source module is any one of the first light source module for supplying the light for measuring immuno-aggregated scattering light or the second light source module for supplying light for PDA embolism reaction measurement device for immuno-aggregated scattering light and PDA fluorescent biochip .
The method of claim 13,
The light source unit includes:
A specific light source module is coupled / separated according to the operator's operation, and includes a light source module coupler configured to supply measurement light output from the coupled light source module; And
And a light source unit ferrule installed above the light source module coupling unit and configured to connect / fix the optical path means.
The method of claim 13,
The light path means,
A first optical fiber connected to a light source unit ferrule to supply light for measurement with a measurement sample mounted to the chip loading unit; And
And an optical path unit for supplying the light passing through the measurement sample mounted to the chip loading unit to the detection unit.
17. The method of claim 16,
The light path unit,
A ferrule attached to one side of the chip loading unit to receive the light passing through the measurement sample and supply the light to the connected optical fiber; And
It includes a second optical fiber for supplying the light supplied to the detection connected to the ferrule,
The ferrule is detachably configured on one side of the chip loading part, and when attached to one side of the chip loading part according to the selection of a measurer, the inclined ferrule receiving the scattered light passing through the measurement sample, and detachable on one side of the chip loading part. When configured to be attached to one side of the chip loading portion according to the selection of the measuring device is an immunocoagulation, characterized in that any one attached to one side of the chip loading portion in accordance with the selection of the measuring device of the upright ferrule is received light passing through the measurement sample Scattered light and PDA fluorescence biochip measuring device.
The method of claim 13,
The detector is a single diode detector,
The single diode detector,
A detection unit ferrule to which the optical fiber of the optical path means is fixed;
A filter wheel for passing only a specific wavelength of light transmitted through the detection unit ferrule; And
And a photodiode for receiving the light transmitted through the filter wheel, converting the light into a current signal, and outputting the photodiode.
19. The method of claim 18,
The filter wheel includes at least one filter, and the immuno-aggregated scattered light and PDA fluorescent biochip measuring device, characterized in that the operation is operated so that a specific filter is located between the detection unit ferrule and the photodiode according to the operator's operation.
20. The method of claim 19,
The filter wheel,
Transmission filter for measuring immunocoagulated scattered light; And
Immunoagglomerated scattered light and PDA fluorescence biochip measuring apparatus comprising a bandpass filter for measuring PDA embolism reaction
The method of claim 13,
The detector is a spectrometer detector,
The spectrometer detector,
A detection unit ferrule to which the optical fiber of the optical path means is fixed;
A spectrometer for passing only a specific wavelength of light transmitted through the detection unit ferrule; And
And an electric signal converter for converting the light of the measurement band output from the spectrometer into an electrical signal and outputting the light.

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