WO2014062033A1

WO2014062033A1 - Micro pcr chip and real-time pcr device comprising same

Info

Publication number: WO2014062033A1
Application number: PCT/KR2013/009343
Authority: WO
Inventors: 김성우; 김덕중
Original assignee: 나노바이오시스(주)
Priority date: 2012-10-19
Filing date: 2013-10-18
Publication date: 2014-04-24
Also published as: KR20140050446A; KR102003784B1

Abstract

An embodiment of the present invention relates to a micro PCR chip and to a real-time PCR device comprising same, whereby it is possible to provide a micro PCR chip which is able to simultaneously accommodate a plurality of small-volume samples and at the same time ensure maximum thermal contact efficiency with a heating block so as to ensure rapid results and which is also able to accurately measure optical signals emitted from nucleic acid amplification products even without any separate filtering or processing, and also whereby, based on this, it is possible to provide a real-time PCR device which is able to rapidly obtain nucleic acid amplification results of guaranteed reliability even without a complicated light-signal measuring module.

Description

Micro PCR chip and real-time PCR device including the same

The present invention relates to a very small PCR chip for performing real-time polymerase chain reaction (PCR) and a real-time PCR device including the same.

Real-time polymerase chain reaction (PCR) has been widely used in performing nucleic acid analysis as an advantage that nucleic acid amplification products can be confirmed in real time during the reaction cycle without performing electrophoresis on gels. In general, a device for implementing real-time PCR is a thermal cycler having at least one heating block for performing a nucleic acid amplification reaction and a signal for measuring in real time a signal generated from a nucleic acid amplification product. And a detector. Such a signal detector may be exemplified as an optical detector for detecting a fluorescence signal generated from a nucleic acid amplification product, an electrical signal detector for detecting an electrical signal generated through specific binding of a nucleic acid amplification product and a medium which is mutually coupled thereto. Can be.

Meanwhile, recently, in the medical field, efficient diagnosis and treatment methods for implementing personalized medicine have been actively developed. In order to realize personalized medicine, rapid and accurate diagnosis and treatment of many individuals is required. In this case, in the diagnosis and treatment, the nucleic acid amplification step is the most basic premise process, and real time PCR, which is an example of performing this, is a prerequisite step in personalized medicine realization. However, since real-time PCR presupposes a complex process, it takes considerable time to complete, and the apparatus for implementing this is largely expensive and large, which is a barrier to practical personalized medicine. Recently, many attempts have been made to solve such problems.

In this regard, Korean Laid-Open Patent Publication No. 10-2004-0048754 (a real-time fluorescence retrieval apparatus with temperature control) is sensitive to fluorescence of several wavelengths in a few hundred to thousands of samples within seconds and even at low concentrations of samples. It provides a compact fluorescence detector that can search and analyze enzyme reactions in real time and is portable at an economical price. Specifically, the prior fluorescence detection device is a device for analyzing a sample by searching for a fluorescence emitted from the sample after irradiating a light source to a biological sample, a sample container, a light source positioned to irradiate the sample container, the light emitted from the sample A fluorescence retrieval device comprising a detector for detecting fluorescence, a fluorescence shifting device for moving fluorescence emitted from the sample to the detector, a wavelength selection device, and a control unit, the fluorescence retrieval device comprising: an array of LEDs arranged to sequentially emit a plurality of LEDs; A well chamber block having a plurality of wells for inserting a sample container; A multi-channel PMT for detecting fluorescence emitted from the sample by each LED emission of the LED array; And a plurality of optical fibers for individually moving the fluorescence emitted from each sample to the multi-channel PMT.

In addition, Korean Patent Registration No. 10-0794703 (real-time monitoring device of the biochemical reaction) provides a device that can compare the degree of reaction of a plurality of samples by minimizing the deviation of the light detection sensitivity during the reaction in the reaction tube plate. Specifically, the preceding real-time monitoring device is a thermostat block system consisting of a thermoelectric element which is a heat supply source capable of supplying heat to the reaction tube and a heat transfer block for transferring heat to the reaction tube; An irradiation light source unit including a lamp and an optical waveguide for irradiating uniform light to a sample in the reaction tube; And an optical system including a reflector for changing a light path and a light receiving unit for receiving fluorescence generated in a sample in the reaction tube by light irradiated by the irradiation light source unit.

In addition, Korean Patent No. 10-1089045 (A real-time monitoring device of the nucleic acid amplification reaction product) performs a nucleic acid amplification reaction such as polymerase chain reaction of a plurality of trace samples in real time to monitor the production of reaction products generated during the reaction In order to efficiently separate the interference of the excitation light and fluorescence, to provide a real-time monitoring device for a biochemical reaction including a polarizer, a polarization beam splitter, a polarization converter and the like.

In addition, Korean Patent Application Publication No. 10-2008-0103548 (a real-time detection device for nucleic acid amplification products) can effectively exclude or reduce the error factor on the device without using a second fluorescent signal used for correction, A plurality of wells are subjected to temperature cycles to detect in real time the fluorescence intensity from the nucleic acid amplification products in each well, furthermore, the fluorescence measurement [DNA] raw obtained from the wells and the surrounding connections in the vicinity of the wells. Real time of nucleic acid amplification products which can determine fluorescence intensity [DNA] real of the well by detecting fluorescence measurement [DNA] bg obtained from the wall and subtracting fluorescence measurement [DNA] bg from fluorescence measurement [DNA] raw It provides a detection device.

In addition, Korean Patent No. 10-0794699 (a real-time monitoring device for nucleic acid amplification reaction products) monitors the production of reaction products generated during the reaction while performing nucleic acid amplification reactions such as polymerase chain reaction of a plurality of trace samples. A sample reaction unit including a reaction vessel having a plurality of wells for holding a plurality of samples, a transparent sealing cover for covering the reaction vessel, and a thermoelectric element for supplying a heat source to the reaction vessel; A light emitting element unit comprising a selective transmission filter positioned in front of the excitation light source and a linear polarizer for linearly polarizing the light passing through the filter; A light receiving element portion comprising a linear polarizer in a direction perpendicular to the linear polarizer of the light emitting element portion, a condenser lens for condensing light passing through the linear polarizer, a selective transmission filter for selectively transmitting the light passing through the condenser lens, and a fluorescent sensing element It provides a real-time monitoring device of the nucleic acid amplification reaction product, characterized in that configured.

However, these prior arts add a large number of complex and sophisticated fluorescence signal measurement modules to simultaneously measure a large number of nucleic acid amplification products, so the problem of large size and high cost of the device is still a problem. Furthermore, the prior art aims to measure a large number of small samples simultaneously, but the signal sensitivity is significantly reduced by bubbles generated by heating in a small sample solution contained in a small reaction vessel during the nucleic acid amplification process. The solution is not disclosed at all.

Therefore, there will still be a need for a real-time PCR implementation apparatus capable of simultaneously measuring a large number of small amounts of nucleic acid amplification products, ensuring reliability of measured values, and further enabling rapid real-time monitoring of nucleic acid amplification products at low cost.

The present invention is to provide a real-time PCR device that can measure a large number of small amounts of nucleic acid amplification products at the same time quickly, detect the nucleic acid amplification products at low cost, and further secure the reliability of the results.

In order to carry out the above-mentioned task to be solved,

One embodiment of the present invention comprises a PCR reaction chamber (chamber) with an open top surface; And an open top surface of the PCR reaction chamber, which seals the open top surface, and protrudes toward the inside of the PCR reaction chamber from a portion of the sealing surface that is in contact with the open top surface and extends along the optical path. It provides a micro-Polymerase Chain Reaction chip, including a cover having a light transmitting portion of the material.

In the micro PCR chip according to an embodiment of the present invention,

The PCR reaction chamber may be implemented to have a liquid sample capacity of 10 μl or less. In this case, the PCR reaction chamber can accommodate 5 to 8 μl of liquid sample.

The light transmitting part may be disposed at the center of the sealing surface.

The light transmitting part may be implemented to reach a position partially spaced upward from the bottom bottom surface of the PCR reaction chamber or upward from the bottom bottom surface of the PCR reaction chamber.

The cover may further include a hole that penetrates through the light transmitting part, and a flexible packing part which contacts the open top surface of the PCR reaction chamber to seal the open top surface.

The micro PCR chip may include two or more unit modules including the PCR reaction chamber and the cover.

The micro PCR chip may have a flat plate shape.

The micro PCR chip may include a first plate having a flat plate shape; A second plate having a flat plate shape disposed on the first plate, the plate having the PCR reaction chamber; And a third plate disposed on an upper portion of the second plate to seal the open top surface in contact with an open top surface of the PCR reaction chamber and serve as a cover having the light transmitting part. . In this case, further comprising a hole that surrounds the light transmitting part between the second plate and the third plate, and a flexible packing part which contacts the open top surface of the PCR reaction chamber to seal the open top surface. Can be.

The micro PCR chip may further include a heat dissipation unit implemented to discharge heat generated from the PCR reaction chamber to the outside.

Another embodiment of the present invention the micro PCR chip; One or more thermal blocks implemented to thermally contact at least one side of the micro PCR chip; And a light detection module implemented to detect an optical signal generated from a PCR amplification product inside the PCR reaction chamber of the micro PCR chip.

Another embodiment of the present invention the micro PCR chip; A first thermal block disposed on a substrate and configured to be in thermal contact with the micro PCR chip; A second thermal block disposed on the substrate and spaced apart from the first thermal block, and configured to be in thermal contact with the micro PCR chip; A chip holder movable left and right and / or up and down by a driving means over the first row block and the second row block, and on which the micro PCR chip is mounted; And PCR amplification in the PCR reaction chamber of the micro PCR chip, wherein the micro PCR chip is disposed between the first row block and the second row block, when the micro PCR chip is moved between the first row block and the second row block by the driving means. It provides a real-time PCR device, including a light detection module implemented to detect an optical signal generated from the product.

According to the above mentioned problem solving means,

Accommodate multiple small amounts of nucleic acid amplification products at the same time and at the same time secure the maximum thermal contact efficiency with the heat block to ensure fast results. Furthermore, the optical signal generated from the nucleic acid amplification products can be accurately and accurately filtered without processing or processing. A micro PCR chip that can be measured can be provided.

In addition, on the premise of the micro PCR chip, it is possible to provide a real-time PCR device that can quickly secure a nucleic acid amplification result secured without the need for complicated measurement module.

1 to 3 relates to a phenomenon in which the optical signal sensitivity is reduced by bubbles generated during the PCR process in a micro-miniaturized PCR vessel (small size, x1 / 20) compared to a conventional PCR vessel (large size).

4 is a cross-sectional view of the basic configuration of a micro PCR chip according to an embodiment of the present invention.

Figure 5 relates to the principle that the optical signal is emitted from the PCR product, without the influence of bubbles generated during the PCR process in the micro PCR chip according to an embodiment of the present invention.

6 relates to various types of light transmitting portions of a micro PCR chip according to an embodiment of the present invention.

7 to 9 are related to the flexible packing of the micro PCR chip according to an embodiment of the present invention.

10 is a micro PCR chip according to an embodiment of the present invention in which two or more unit modules including a PCR reaction chamber and a cover including a light transmitting unit are repeatedly implemented.

11 to 12 relate to the cross-sectional exploded view of a micro PCR chip according to an embodiment of the present invention.

Figure 13 relates to a micro PCR chip according to an embodiment of the present invention including a heat release.

14 to 15 are to detect an optical signal generated from a micro PCR chip, a thermal block in thermal contact with the micro PCR chip, and a PCR amplification product inside a PCR reaction chamber of the micro PCR chip according to an embodiment of the present invention. It relates to a real-time PCR device according to another embodiment of the present invention including an implemented light detection module.

16 to 18 are micro PCR chips according to an embodiment of the present invention, two row blocks, a chip holder mounted with the micro PCR chip and movable between the two row blocks by a driving means, and the two row blocks. And an optical detection module disposed between the micro PCR chips and configured to detect an optical signal generated from a PCR amplification product inside the PCR reaction chamber of the micro PCR chip when the micro PCR chip is moved between the two thermal blocks by the driving means. It relates to a real-time PCR device according to another embodiment of the present invention.

19 is an actual implementation diagram of a micro PCR chip according to an embodiment of the present invention.

FIG. 20 is a fluorescence photograph of PCR results after real-time PCR using the micro PCR chip of FIG. 19 and the real-time PCR apparatus of FIG. 18.

21 to 23 are graphs showing PCR results after real-time PCR using the micro PCR chip of FIG. 19 and the real-time PCR apparatus of FIG. 18.

Hereinafter, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings. The following description is merely a means for easily understanding the embodiments according to the present invention, but is not intended to limit the protection scope of the present invention.

Embodiments of the present invention relate to polymerase chain reaction (PCR), and more particularly, real-time PCR for monitoring nucleic acid amplification reactions in real time.

PCR is a technology that repeatedly heats and cools PCR samples and reagents containing nucleic acids, thereby serially replicating specific nucleotide sequences of nucleic acids to exponentially amplify nucleic acids having specific nucleotide sequences. It is now widely used for diagnosis and analysis of diseases in engineering and medical fields. Recently, various PCR apparatuses for efficiently performing PCR have been developed. PCR apparatus is collectively referred to as a device implemented to perform PCR for amplifying a nucleic acid having a specific base sequence. In general, a PCR device is a denaturing step of separating a double-stranded DNA into a single-stranded DNA by heating a PCR sample and reagent comprising a double-stranded DNA to a specific temperature, for example about 95 ° C., Provide an oligonucleotide primer having a sequence complementary to a specific nucleotide sequence to be amplified in the PCR sample and reagent, and cooled to a specific temperature, for example 55 ℃ with the isolated single strand of DNA An annealing step of forming a partial DNA-primer complex by binding the primer to a specific nucleotide sequence of a strand of DNA, and after the annealing step, the PCR sample and reagent are subjected to an activity temperature of DNA polymerase, for example, Maintaining at 72 ° C. to form double stranded DNA based on the primers of the partial DNA-primer complex by DNA polymerase. By performing an extension (or amplification) step and repeating the extension (or amplification) step, for example, 20 to 40 times, the DNA having the specific base sequence can be implemented to be exponentially amplified. . On the other hand, the recent PCR apparatus may perform the annealing step and the extension (or amplification) at the same time, in which case the PCR device performs the two steps consisting of the annealing and extension (or amplification) steps following the denaturation step. By doing so, the first circulation can be completed.

Real-time PCR uses a nucleic acid amplification reaction to monitor the production of nucleic acid amplification products by applying an optical system module, such as a fluorescence photometer, to a thermal cycler used for PCR. Say. Unlike general PCR, real-time PCR does not require electrophoresis to identify nucleic acid amplification products, which has the advantage of analyzing nucleic acid amplification products accurately and quickly in real time. Accordingly, the real-time PCR apparatus has also been actively developed in recent years. In order to realize the above advantages, the real-time PCR apparatus not only increases the efficiency of the thermal cycler but also accurately and accurately measures the optical signal generated from the nucleic acid amplification product. You should be able to.

1 to 3 relates to a phenomenon in which optical signal sensitivity is reduced by bubbles generated during a PCR process in a conventional PCR vessel (large) and an ultra-miniaturized PCR vessel (small, × 1/20).

For practical realization of personalized medical services, PCR devices have recently been aimed at miniaturization, portability, speed, and economy. Existing PCR apparatus is not only a container for PCR samples and reagents, but also the device itself is large, difficult to operate and difficult to carry, as well as a considerable waste of PCR samples and reagents accordingly, there was also a problem that a considerable cost. Furthermore, the large amount of PCR samples and reagents used was quite time consuming and difficult to implement efficient PCR.

According to Fig. 1, the left figure is a conventionally used PCR vessel (large size), and the right figure is a PCR vessel (small size) in which the size and liquid sample capacity are extremely small (× 1/20) compared to the PCR vessel (large size). ). In general, a conventional PCR vessel (large) is composed of a reaction chamber containing a PCR sample and reagents and a cover thereof, the reaction chamber and the cover is made of a light transmitting material, about 200 μl of liquid PCR was performed with a sample capacity and about 20 μl of sample and reagents. The PCR vessel (small) also includes a reaction chamber containing a PCR sample and a reagent and a cover thereof, and the reaction chamber and the cover may be made of a light transmissive material, in which case the PCR vessel ( Small) has a liquid sample capacity of about 10 μl, and PCR is performed with about 5 to 8 μl of sample and reagents received. As such, fabricating ultra-miniaturized PCR vessels can be readily implemented in the currently known art. However, miniaturization of PCR vessels is difficult to implement easily because they have a significant adverse effect on the measurement of nucleic acid amplification products as follows.

According to FIG. 2, it is easy to identify a phenomenon in which an optical signal sensitivity decreases due to a bubble generated during a PCR process in an ultra-miniaturized PCR vessel (small size, × 1/20) compared to a conventional PCR vessel (large size). . As described above, PCR involves a heat supply step, so that a considerable amount of bubbles are generated inside the PCR vessel by heating the liquid sample, which blocks the light signal generated from the nucleic acid amplification product. do. Meanwhile, according to FIG. 2, bubbles generated inside the PCR vessel (large) reduce the optical signal sensitivity by blocking the optical signals generated from the nucleic acid amplification products, but the internal space of the reaction vessel compared to the size and number of the bubbles themselves. Because of this sufficiently large size, the bubbles are dispersed inside the PCR vessel (large) or clustered on the inner wall of the PCR vessel (large), so that although optical signal sensitivity is inferior, optical signal measurement is not impossible. However, according to FIG. 3 in which the portion “a” of FIG. 2 and FIG. 2 are enlarged, the bubble generated inside the PCR vessel (small) has a relatively small internal space of the reaction vessel relative to the size and number of bubbles itself. By blocking the optical signal generated from the nucleic acid amplification product, the optical signal sensitivity is significantly reduced and non-uniform, resulting in less reliable results. Therefore, when miniaturizing the PCR apparatus and at the same time miniaturizing the PCR vessel mounted therein, it is necessary to fully consider a method of securing the reliability of the result due to the decrease in optical signal sensitivity and the nonuniformity.

According to FIG. 4, a micro-polymer chain reaction chip 1 according to an embodiment of the present invention 1 includes a PCR reaction chamber 10 having an open top surface; And an open top surface of the PCR reaction chamber 10, which is in contact with the open top surface of the PCR reaction chamber 10, to seal the open top surface, and protrude toward the inside of the PCR reaction chamber 10 from a portion of the sealing surface that is in contact with the open top surface of the optical path. And a cover 20 having a light transmitting portion 25 of a light transmissive material extending along (21).

The PCR reaction chamber 10 is open to the upper surface, but the lower surface and the side border surface is implemented to accommodate a liquid sample, that is, a PCR sample and reagents. The PCR reaction chamber 10 should be implemented so as not to be affected by repetitive heating and cooling during the PCR process, and is not limited to a specific shape and / or material as long as it can maintain this function. However, since the micro PCR chip 1 according to the embodiment of the present invention is based on the real-time optical signal measurement of the nucleic acid amplification product, at least a portion overlapping the optical path 21 is preferably implemented by a light transmissive material. Do.

The cover 20 abuts the open top surface of the PCR reaction chamber 10 and serves to seal the open top surface. As the cover 20 seals the open top surface of the PCR reaction chamber 10, PCR samples and reagents reacting inside the PCR reaction chamber 10 are not leaked to the outside, and the PCR reaction chamber 10 is closed. It maintains the internal temperature. On the other hand, the cover 20 may be implemented in a variety of shapes and / or materials if it can implement the above functions. However, since the micro PCR chip 1 according to an embodiment of the present invention presupposes the real-time optical signal measurement of the nucleic acid amplification product, it is preferable that the micro PCR chip 1 is made of a light transmitting material.

Meanwhile, according to FIG. 4, the cover 20 protrudes toward the inside of the PCR reaction chamber 10 from a portion of the sealing surface that is in contact with the open top surface, and extends along the light path 21. Light transmission portion 25 is provided. The light transmitting part 25 is implemented as a light transmitting material and is implemented to extend along the light path 21 for the measurement of the nucleic acid amplification product, the optical signal generated from the nucleic acid amplification product in the PCR reaction chamber 10 passes through That's the part. Furthermore, the light transmitting part 25 is directed toward the inside of the PCR reaction chamber 10 from a part of the sealing surface which contacts the open top surface of the PCR reaction chamber 10, that is, the bottom surface of the lid 20. It is implemented to protrude downward. The protruding shape of the light transmitting part 25 may vary, but is preferably implemented in a cylindrical or square column shape. In addition, according to FIG. 6, the protruding shape of the light transmitting part 25 may be implemented in various ways, such that it is implemented to contact the bottom bottom surface of the PCR reaction chamber 10 (the right side of FIG. 6), or the PCR reaction. It may be implemented up to some spaced apart position upward from the bottom bottom face of the chamber 10 (left side of FIG. 6). That is, when the liquid sample is accommodated in the PCR reaction chamber 10, the light transmitting part 25 may be adjacent to or abut the surface of the liquid sample, or may pass through the surface of the liquid sample and be contained within the liquid sample. have. In addition, if the light transmitting part 25 is implemented to extend along the light path, the light transmitting part 25 may be implemented in any part of the sealing surface that contacts the open top surface of the PCR reaction chamber 10, that is, the bottom surface of the lid 20. It may be, it is preferably disposed in the center of the sealing surface, that is, the central region of the bottom surface of the cover (20). On the other hand, the liquid sample capacity of the PCR reaction chamber 10 is not limited to a specific volume, but is preferably implemented to have a liquid sample capacity of 10 μl or less to accommodate 5 to 8 μl of liquid sample.

As described above, as the PCR process proceeds, the liquid sample inside the PCR vessel may be heated, thereby generating bubbles.

Referring to FIG. 5, when a liquid sample, that is, a PCR sample and a reagent inside the PCR reaction chamber 10 of the micro PCR chip 1 according to an embodiment of the present invention is heated by a heat supply during a PCR process, Bubbles occur. However, in the case of the micro PCR chip 1 according to an embodiment of the present invention, a portion of the sealed surface protruding from the bottom surface of the lid 20, that is, contacting the open top surface of the PCR reaction chamber 10 ( According to FIG. 5, the PCR reaction chamber 10 is formed by a light transmitting part 25 of a light transmitting material protruding from the central region) toward the inside of the PCR reaction chamber 10 and extending along the light path 21. The formed bubble is pushed to the peripheral area of the edge surface of the light transmitting part 25 and is compressed and disposed in the peripheral space. Accordingly, the bubble completely deviates from the optical signal path (light transmitting part) 25 formed from the nucleic acid amplification product present in the liquid sample, and the optical signal sensitivity for measuring the nucleic acid amplification product is It has no effect at all. Therefore, when the nucleic acid amplification products are measured in real time during the real-time PCR process using the micro PCR chip 1 according to an embodiment of the present invention, the influence of bubbles generated inside the PCR reaction chamber 10 is not affected at all. The optical signal sensitivity is significantly increased. As a result, according to the micro PCR chip 1 according to the embodiment of the present invention, since the liquid sample capacity can be greatly reduced to, for example, 10 μl or less, compared to the conventional PCR vessel, the PCR vessel can be miniaturized. And at the same time, the optical signal sensitivity can be significantly increased, thereby miniaturization and portability of the PCR vessel and the real-time PCR apparatus can be achieved, and further, a large number of small amount of nucleic acid amplification products can be quickly and accurately measured simultaneously. .

According to FIGS. 7 to 9, the cover 20 of the micro PCR chip 1 according to the exemplary embodiment of the present invention includes a hole 45 penetrating through the light transmitting part 25, and the PCR reaction. A flexible packing part 40 may be further included to abut the open top surface of the chamber 10 to seal the open top surface.

The flexible packing unit 40 serves to prevent leakage of the liquid sample due to bubble generation or pressure rise due to a temperature rise inside the PCR reaction chamber 10 during a PCR process. The flexible packing part 40 is made of a material having elasticity or elasticity such as rubber or silicon to buffer the expansion force due to the bubble generation or the pressure rise, but the PCR reaction chamber 10 It is implemented to maintain the sealed state. On the other hand, since the hole 45 is implemented according to the shape of the light transmitting part 25, although it is implemented in a circular shape in Figure 7 is not limited thereto. Meanwhile, FIG. 8 illustrates a state in which the flexible packing part 40 is attached to the cover 20 but is enclosed through the light transmitting part 25, and FIG. 9 illustrates that the cover 20 of FIG. The state in which the inner space of the PCR reaction chamber 10 is sealed by coupling to the upper surface of the PCR reaction chamber 10 is illustrated.

As described above, the micro PCR chip 1 according to the embodiment of the present invention significantly increases the optical signal sensitivity by the lid 20 including the PCR reaction chamber 10 and the light transmitting part 25. It is possible to implement a PCR vessel having a multi-chamber structure that can be extremely miniaturized without affecting or affecting a large number of liquid samples.

According to FIG. 10, the micro PCR chip 1 according to the exemplary embodiment of the present invention may include two or more unit modules 50 including the PCR reaction chamber 10 and the cover 20. For example, as shown in FIG. 10, when the micro PCR chip 1 is implemented in a flat plate shape, the unit modules 50 may be arranged in a line or may be integrated in a circular space on the flat plate and implemented as two or more numbers N. FIG. In this case, for example, the unit module 50 may be implemented in 19 (19 well), 48 (48 well), 96 (96 well) and the like.

According to FIG. 11, a micro PCR chip 1 according to an embodiment of the present invention may include a first plate 100 having a flat plate shape; A second plate (200) having a flat plate shape disposed on the first plate (100) and having the PCR reaction chamber (10); And a cover 20 disposed above the second plate 200 to seal the open top surface by contacting the open top surface of the PCR reaction chamber 10 and having the light transmitting part 25. It may be implemented to include a third plate 300 to play a role.

The first plate 100 is implemented in a flat plate shape, and serves as a bottom support of the micro PCR chip 1 according to an embodiment of the present invention. The first plate 100 may be made of various materials, but in consideration of cost reduction, the first plate 100 may be made of a plastic material, for example, polycarbonate (polyarbonate, PC), polyethylene terephthalate (PET), or the like. It is preferred to be implemented with a transparent material. In addition, the surface of the first plate 100 may be embodied in various ways, but is preferably treated to have a hydrophilic surface. In addition, the first plate 100 may be preferably implemented in about 0.03 to 1.0 mm, more preferably in about 0.1 to 0.5 mm.

The second plate 200 is implemented in a flat plate shape and is disposed on the first plate 100. The second plate 200 is a region of the PCR reaction chamber 10 of the micro PCR chip 1 according to an embodiment of the present invention. Serves to form. The second plate 200 may be made of various materials, but in consideration of cost reduction, the second plate 200 may be made of a plastic material, for example, polycarbonate (polyarbonate, PC), polyethylene terephthalate (PET), or the like. It is preferred to be implemented with a transparent material. In addition, the second plate 200 may be preferably implemented as about 0.5 to 5 mm, more preferably about 1 to 2 mm.

Meanwhile, according to FIG. 11, the bottom surface space of the PCR reaction chamber 10 of the micro PCR chip 1 according to an embodiment of the present invention is provided between the first plate 100 and the second plate 200. An additional layer 150 in the form of a plate may be formed. This may be a bonding surface between the first plate 100 and the second plate 200, or may be an adhesive layer. Therefore, adhesion between the first plate 100 and the second plate 200 may be achieved by thermal bonding, ultrasonic bonding, ultraviolet bonding, or solvent bonding. In addition, the additional layer 150 may be preferably implemented in about 0.03 to 1.0 mm, more preferably in about 0.1 to 0.5 mm.

The third plate 300 is implemented in a flat plate shape, but is disposed on the second plate 200, and opens the PCR reaction chamber 10 of the micro PCR chip 1 according to an embodiment of the present invention. The open top surface is sealed to abut on the top surface, and serves as a cover 20 having the light transmitting part 50. The third plate 200 may be made of various materials, but in consideration of cost reduction, the third plate 200 may be made of a plastic material, for example, polycarbonate (polyarbonate, PC), polyethylene terephthalate (PET), or the like. It is preferred to be implemented with a transparent material. In addition, the third plate 200 may be preferably implemented as about 0.5 to 5 mm, more preferably about 1 to 2 mm.

Meanwhile, according to FIG. 12, the third plate 300 surrounds a hole between the second plate 200 and the third plate 300 to penetrate the light transmitting part 25, and the PCR. The flexible packing part 40 may be further provided to contact the open top surface of the reaction chamber 10 to seal the open top surface. The flexible packing unit 40 serves to prevent leakage of PCR samples and reagents contained in the PCR reaction chamber 10 and contamination between the plurality of chambers. The flexible packing part 40 may be made of various materials having elasticity or elasticity. For example, the flexible packing part 40 may be made of silicon, telflon, or the like. In addition, the flexible packing part 40 may be preferably implemented as about 0.1 to 2 mm, more preferably about 0.5 to 1 mm, and the circular hole diameter is preferably about 1.0 mm It can be implemented as.

The micro PCR chip 1 according to an embodiment of the present invention may further include a heat dissipation unit 60 implemented to discharge heat generated from the PCR reaction chamber 10 to the outside. According to FIG. 13, the micro PCR chip 1 according to the exemplary embodiment of the present invention has a thin plate shape as a whole and is implemented such that a plurality of unit modules 50 are integrated in a central circular region. As described above, since the high temperature heat is generated in the PCR reaction chamber 10 in the unit module 50 during the PCR process, in consideration of the heat resistance of the device and the reaction stability, according to an embodiment of the present invention The PCR chip 1 may arrange the heat dissipation parts 60 on both sides of the central circular region.

14 to 15 illustrate a real-time PCR apparatus having a single row block to which a micro PCR chip is applied according to an embodiment of the present invention.

14 to 15, the real-time PCR device 2000 according to another embodiment of the present invention includes a micro PCR chip 1 according to an embodiment of the present invention described above; One or more thermal blocks (200) implemented to thermally contact at least one surface of the micro PCR chip (1); And an optical detection module 300 implemented to detect an optical signal generated from a PCR amplification product inside the PCR reaction chamber 10 of the micro PCR chip 1.

The thermal block 200 is a module implemented to enable heat exchange in thermal contact with the micro PCR chip 1. The thermal block 200 may be formed of various materials, and may be implemented to have a light transmittance (or partially) in order to measure the optical signal of the nucleic acid amplification product. The transparent heat generating material may include all materials having heat generating property by power supply as a material having light transmittance, but preferably, indium tin oxide (ITO), a conducting polymer, carbon nano It may be selected from the group consisting of tubes (Cabon NanoTube, CNT), graphene, transparent metal oxide (TCO), and oxide-metal-oxide multilayer transparent devices. Indium tin oxide (ITO) is a mixture of indium oxide (In ₂ O ₃ ) and tin oxide (SnO ₂ ), and is generally composed of 90% indium oxide and 10% tin oxide, and is a transparent electrode It is also called ITO. Indium tin oxide has an electrical conductivity when implemented in a thin film (thin layer), and becomes yellowish gray when implemented in a lumped state, transparent and colorless. Indium tin oxide is deposited on the surface of other materials by electron beam deposition, vapor deposition, and sputtering techniques. Indium tin oxide is conventionally mainly used in liquid crystal displays, flat panel displays, plasma displays, touch screens, electronic paper, organic light emitting diodes, and solar cells. , Antistatic coatings, electromagnetic interference shielding, mainly used to make transparent conductive coatings. The conducting polymer is called a plastic through which electricity is transmitted, and has the advantage of excellent light transmittance, light weight, excellent elasticity and electrical conductivity, and easy processing. The conductive polymer is made from materials such as polyacetylene, polyparaenylene, polyphenol, polyaniline, and the like, and recently, may be made from polystyrene sulfonic acid and / or PEDOT (poly (3,4--ethylenedioxythiophene)). Carbon NanoTube (CNT) refers to tiny molecules of 1 nanometer in diameter, with long, long rings of carbons connected by hexagonal rings. Tensile force is known to be stronger than steel, more flexible, lighter, and more electrically conductive. Meanwhile, when the purified single-walled carbon nanotubes (SWNT) are solvent dispersed using a surfactant and manufactured using a vacuum filter device, a transparent conductor is formed, which has both transparency and conductivity. do. Graphene (graphene) is a material separated from graphite in the early 2000s, and is a nanomaterial composed of carbon number 6 such as carbon nanotubes and fullerenes. Graphene is known to be more than 100 times higher electrical conductivity than copper, and has a very good elasticity, and has recently been implemented as a transparent electrode and used for various purposes. Transparent Conductive Oxide (TCO) refers to a material having transparency among various metal oxides bonded with oxygen, and includes ZnO, SnO ₂ , TiO ₂ , and the like. Transparent metal oxides have high conductivity and transparency and can be used as coating materials at low cost. The oxide-metal-oxide multilayer transparent device is manufactured by a roll-to-roll sputtering process, and can be implemented to have flexibility of a metal, low resistance, and high permeability of an oxide. AZO, GZO-Ag-GZO, IZO-Ag-IZO, IZTO-Ag-IZTO, and the like. On the other hand, according to Figure 14 to 15, the thermal block 200 may be implemented in a variety of shapes, but preferably in a flat shape. The plate-shaped thermal block 200 has a large surface area in contact with the micro PCR chip 1, preferably, the plate-shaped chip, thereby providing heat evenly to the mixed solution of the PCR sample and the reagents, and thus The temperature change for each cycle can proceed rapidly. On the other hand, in order to accurately monitor the real-time PCR product, it is necessary to increase the sensitivity of the optical signal as much as possible. The thermal block 200 may be implemented to have a light transmittance as a whole, so that most of the excitation light emitted from the light source may be transmitted as it is, thereby increasing the optical signal sensitivity. However, some of the excitation light may be reflected on the column block 200 or reflected after passing through the column block 200 to act as noise of an optical signal. Therefore, preferably, the light absorbing material may be processed on the lower surface of the thermal block 200 to further increase the optical signal sensitivity. The light absorbing material may be, for example, mica, but is not limited to a material having a property of absorbing light. Therefore, the light absorbing layer absorbs a part of the light derived from the light source, and the generation of reflected light acting as noise of the optical signal can be suppressed as much as possible. Alternatively, the optical signal sensitivity may be further increased by treating an antireflective material on the upper surface of the thermal block 200. The anti-reflective material may be, for example, a fluoride such as MgF ₂ or an oxide such as SiO ₂ or Al ₂ O ₃ , but is not limited as long as the material has a property of preventing light reflection. Also, more preferably, the light absorbing material may be processed on the lower surface of the thermal block 200, and at the same time, the light reflection preventing material may be processed on the upper surface of the thermal block 200 to further increase the optical signal sensitivity. That is, for effective real-time PCR monitoring, the ratio of the optical signal to the noise should have the maximum possible value, and the ratio of the optical signal to the noise may be improved as the reflectance of the excitation light from the PCR chip is lower. For example, the reflectance of the excitation light of the existing thermal block of a general metallic material is about 20 to 80%, but the light reflectance is 0.2% to 4 when using the heat block 200 including the light absorbing layer or the antireflective layer. It can be reduced to within%, and when using the heat block 200 including the light absorbing layer 60 and the light reflection prevention layer 70 can reduce the light reflectance to 0.2% or less.

The light detection module 300 is operable to receive light emitted from the micro PCR chip 1 and a light providing unit (not shown) operably arranged to provide light to the micro PCR chip 1. It may include a light detector (not shown) disposed so as to. The light providing unit is a module for providing light to the micro PCR chip (1), the light detection unit receives the light emitted from the micro PCR chip (1) PCR products carried out in the micro PCR chip (1) This module is for measuring. Light is emitted from the light providing unit, and the emitted light passes through or reflects through the PCR reaction chamber in the micro PCR chip 1, specifically, the unit module 50 of the micro PCR chip 1. The light detector detects an optical signal generated by nucleic acid amplification in the PCR reaction chamber. Therefore, according to the real-time PCR device 1000 according to another embodiment of the present invention, the nucleic acid amplification product (fluorescent material is bound) in the PCR reaction chamber during the PCR process in the micro PCR chip (1) By monitoring in real time, it is possible to measure and analyze in real time whether the target nucleic acid included in the initial PCR sample and reagent is amplified and the degree of amplification. In addition, the light providing unit and the light detecting unit may be all disposed above or below the thermal block 200, or may be disposed respectively. However, the arrangement of the light providing unit and the light detecting unit may be various in consideration of the arrangement relationship with other modules for optimal implementation of the real-time PCR apparatus 1000 according to another embodiment of the present invention. According to 14 to 15, both the light providing unit and the light detecting unit 300 may be disposed above the thermal block 200. The light providing unit includes a light emitting diode (LED) light source or a laser light source, a first light filter for selecting light having a predetermined wavelength from the light emitted from the light source, and a light collecting unit for collecting light emitted from the first light filter. It may further include a first aspheric lens including a first optical lens, disposed to spread light between the light source and the first light filter. The light source includes all light sources capable of emitting light, and includes a light emitting diode (LED) light source or a laser light source. The first light filter selects and emits light having a specific wavelength among incident light having various wavelength bands, and may be variously selected according to the predetermined light source. For example, the first light filter may pass only light in a wavelength band of 500 nm or less of the light emitted from the light source. The first optical lens collects the incident light and increases the intensity of the emitted light. The first optical lens may increase the intensity of light irradiated onto the micro PCR chip 1 through the thermal block 200. In addition, the light providing unit may further include a first aspherical lens disposed to spread light between the light source and the first light filter. By adjusting the arrangement direction of the first aspherical lens, the light range emitted from the light source is extended to reach the measurable area. The light detector includes a second optical lens for collecting light emitted from the micro PCR chip 1, a second optical filter for selecting light having a predetermined wavelength from the light emitted from the second optical lens, and the second optical filter. An optical analyzer for detecting an optical signal from light emitted from the second optical filter, and further comprising a second aspherical lens disposed between the second optical filter and the optical analyzer to integrate light emitted from the second optical filter; And a photodiode disposed between the second aspherical lens and the optical analyzer to remove noise of light emitted from the second aspherical lens and to amplify the light emitted from the second aspherical lens. The integrated circuit may further include a PDIC. The second optical lens collects the incident light and increases the intensity of the emitted light. The second optical lens increases the intensity of light emitted from the micro PCR chip 1 through the thermal block 200 to detect the optical signal. To facilitate. The second light filter selects and emits light having a specific wavelength among incident light having various wavelength bands, and variously selects the light according to a predetermined wavelength of light emitted from the micro PCR chip 1 through the thermal block 200. Can be. For example, the second light filter may pass only light in a wavelength range of 500 nm or less among predetermined light emitted from the micro PCR chip 1 through the heat block 200. The optical analyzer is a module that detects an optical signal from light emitted from the second optical filter, and converts expression fluorescence from an PCR sample and a reagent into an electrical signal to enable qualitative and quantitative measurement. The light detector may further include a second aspherical lens disposed between the second light filter and the light analyzer to integrate light emitted from the second light filter. By adjusting the arrangement direction of the second aspherical lens, the light region emitted from the second light filter is expanded to reach the measurable region. The light detector may further include a photodiode disposed between the second aspherical lens and the optical analyzer to remove noise of light emitted from the second aspherical lens and to amplify the light emitted from the second aspherical lens. It may further include a photodiode integrated circuit (PDIC). By using the photodiode integrated device 340, it is possible to further reduce the size of the device, and to measure a reliable optical signal by minimizing noise. Furthermore, the real-time PCR apparatus 1000 according to another embodiment of the present invention adjusts the direction of light travel so that the light emitted from the light providing unit reaches the light detecting unit, and separates light having a predetermined wavelength. One or more dichroic filters may be further included. The dichroic filter is a module that reflects light at an angle selectively transmitted or selectively adjusted according to the wavelength. The dichroic filter is disposed to be inclined at an angle of about 45 degrees with respect to the optical axis of the light emitted from the light providing unit, and selectively transmits the light having a short wavelength component and reflects the long wavelength component at a right angle according to the wavelength thereof so that the heat block ( To the micro PCR chip 1 disposed on the substrate 200). Further, the dichroic filter is disposed to be inclined at an angle of about 45 degrees with respect to the optical axis of the light reflected from the micro PCR chip 1 and the thermal block 200, and selectively transmits the light according to the wavelength of the short wavelength component. And the long wavelength component is reflected at right angles to reach the photodetector. The light reaching the light detector may be converted into an electrical signal in the optical analyzer to indicate whether the nucleic acid is amplified and the degree of amplification.

16 to 18 illustrate a real-time PCR device having two column blocks to which a micro PCR chip according to an embodiment of the present invention is applied.

16 to 18, the real-time PCR device 2000 according to another embodiment of the present invention includes a micro PCR chip 1 according to the embodiment of the present invention described above; A first thermal block (100a) disposed on the substrate (400a) and implemented to be in thermal contact with the micro PCR chip (1); A second thermal block 200a disposed on the substrate 400a to be spaced apart from the first thermal block 100a and in thermal contact with the micro PCR chip 1; A chip holder 300a movable left and right and / or up and down by the driving means 500a on the first row block 100a and the second row block 200a and on which the micro PCR chip 1 is mounted; And between the first row block 100a and the second row block 200a, wherein the micro PCR chip 1 is driven by the driving means 500a by the first row block 100a and the second row. The

light detection module

700a and 800a are implemented to detect an optical signal generated from a PCR amplification product inside the PCR reaction chamber 10 of the micro PCR chip 1 when moving between blocks 200a.

According to FIG. 16, the real-time PCR apparatus 2000 according to another embodiment of the present invention may include a first row block 100a disposed on the substrate 400a; A second thermal block 200a spaced apart from the first thermal block 100a on the substrate 400a; And move up, down, and / or up and down by the driving means 500a over the first and second row blocks 100a and 200a, and the micro PCR chip 1 according to an embodiment of the present invention may be And a mounted chip holder 300a.

The substrate 400a does not change its physical and / or chemical properties due to heating and temperature maintenance of the first thermal block 100a and the second thermal block 200a, and the first thermal block 100a and the first thermal block 100a and the second thermal block 200a do not change. It includes all materials having a material such that mutual heat exchange does not occur between the two heat blocks 200a. For example, the substrate 400a may include or be made of a material such as plastic.

The first row block 100a and the second row block 200a are for maintaining a temperature for performing a denaturation step, annealing step and extension (or amplification) step for amplifying the nucleic acid. Thus, the first thermal block 100a and the second thermal block 200a may include or be operably connected with various modules for providing and maintaining the required temperature required for the respective steps. . Therefore, when the chip holder 300a on which the micro PCR chip 1 is mounted is in contact with one surface of each of the row blocks 100a and 200a, the first row block 100a and the second row block 200a are provided. Since the contact surface with the micro PCR chip 1 as a whole can be heated and temperature maintained, the sample solution in the micro PCR chip 1 can be uniformly heated and temperature maintained. In the conventional PCR apparatus using a single thermal block, the temperature change rate in the single thermal block is within a range of 3 to 7 ° C per second, whereas a real time PCR apparatus including two thermal blocks according to another embodiment of the present invention ( 2000), the rate of temperature change in each of the

thermal blocks

100a and 200a is within a range of 20 to 40 ° C. per second, thereby greatly shortening the PCR progress time.

Hot wires (not shown) may be disposed in the first row block 100a and the second row block 200a. The heating wire may be operably connected with various heat sources to maintain a temperature for performing the denaturing, annealing and extending (or amplifying) steps, and may be operably connected with various temperature sensors for monitoring the temperature of the heating wire. Can be. The heating wires are vertically and / or horizontally based on the center point of the surface of each of the heat blocks 100a and 200a in order to maintain a constant internal temperature of the first and

second heat blocks

100a and 200a. It may be arranged to be symmetrical. The arrangement of the hot wires symmetrically in the vertical direction and / or the horizontal direction may vary. In addition, a thin film heater (not shown) may be disposed in the first thermal block 100a and the second thermal block 200a. The thin-film heater is vertically and / or horizontally based on a center point of each of the

thermal block

100a and 200a in order to maintain a constant internal temperature of the first and second

thermal blocks

100a and 200a. May be spaced apart at regular intervals. The arrangement of the thin film heater that is constant in the vertical and / or horizontal directions may vary.

The first thermal block 100a and the second thermal block 200a may include a metal material, for example, aluminum or may be made of aluminum for even heat distribution and rapid heat transfer over the same area.

The first thermal block 100a may be implemented to maintain an appropriate temperature for performing the denaturation step, or the annealing and extension (or amplification) steps. For example, the first row block 100a of the real-time PCR apparatus 2000 according to another embodiment of the present invention may maintain 50 ° C. to 100 ° C., preferably in the first row block 100 a. In the case of performing the denaturation step, the temperature may be maintained at 90 ° C. to 100 ° C., preferably at 95 ° C., and 55 when the annealing and extension (or amplification) steps are performed in the first heat block 100a. ℃ to 75 ℃ can be maintained, preferably 72 ℃ can be maintained. However, the temperature of the denaturation step or the annealing and extension (or amplification) step is not limited thereto. The second row block 200a may be implemented to maintain an appropriate temperature for performing the denaturation step, or the annealing and extension (or amplification) steps. For example, the second row block 200a of the PCR apparatus according to the third embodiment of the present invention may maintain 90 ° C. to 100 ° C. when the denaturation step is performed in the second row block 200 a. Preferably, the temperature may be maintained at 95 ° C., and may be maintained at 55 ° C. to 75 ° C., preferably at 72 ° C., when the annealing and extension (or amplification) steps are performed in the second heat block. However, the temperature of the denaturation step or the annealing and extension (or amplification) step is not limited thereto. Therefore, the first heat block 100a may maintain the denaturing temperature of the PCR, and when the denaturation temperature is lower than 90 ° C., denaturation of the nucleic acid that is a template of the PCR occurs, resulting in poor efficiency and low PCR efficiency. When the denaturation step temperature is higher than 100 ° C., the enzyme used for PCR loses activity, so the denaturation step temperature may be 90 ° C. to 100 ° C., preferably 95 ° C. have. In addition, the second row block 200a may maintain annealing / extension temperature of annealing and extension (or amplification) of the PCR. If the extension (or amplification) step temperature is lower than 55 ° C., the specificity of the PCR product may be degraded, and if the annealing and extension (or amplification) step temperature is higher than 74 ° C., the PCR may not occur. Since the efficiency is lowered, the annealing and extension (or amplification) step temperature may be 55 ° C to 75 ° C, preferably 72 ° C.

The first thermal block 100a and the second thermal block 200a may be spaced apart from each other at a predetermined distance such that mutual heat exchange does not occur. Accordingly, since the heat exchange does not occur between the first heat block 100a and the second heat block 200a, the denaturation step and the nucleic acid amplification reaction may be significantly affected by a slight temperature change. Accurate temperature control of the annealing and extension (or amplification) steps is possible.

The real-time PCR apparatus 2000 according to another embodiment of the present invention may move left and right and / or up and down by the driving means 500a over the first row block 100a and the second row block 200a, and the micro And a chip holder 300a on which the PCR chip 1 is mounted. The chip holder 300a is a module in which the micro PCR chip 1 is mounted on the real time PCR device 2000. The inner wall of the chip holder 300a has the micro PCR chip 1 so that the micro PCR chip 1 does not leave the chip holder 300a when the nucleic acid amplification reaction is performed by the real-time PCR device 2000. It may have a shape or structure for fixed mounting with the outer wall of. The chip holder 300a is operably connected to the driving means 500a. In addition, the micro PCR chip 1 may be detachable to the chip holder (300a).

The driving means 500a is configured to allow the chip holder 300a on which the micro PCR chip 1 is mounted to move left and right and / or up and down over the first row block 100a and the second row block 200a. Means; By the left and right movement of the driving means 500a, the chip holder 300a on which the micro PCR chip 1 is mounted can reciprocate between the first row block 100a and the second row block 200a. In addition, by the vertical movement of the driving means 500a, the chip holder 300a on which the PCR chip 10 is mounted is in contact with and separated from the first row block 100a and the second row block 200a. Can be. The driving means 500a of the real-time PCR apparatus 2000 shown in FIG. 16 is disposed to be slidably movable in the left and right directions through the rail 510a extending in the left and right directions, and the rail 510a, and in the vertical direction. And a movable connecting member 520a, wherein one end of the connecting member 520a is disposed with the chip holder. The left and right and / or vertical movement of the driving means 500a may be controlled by a control means (not shown), which is operably disposed inside or outside the PCR device, and the control means may be modified with a modification step of PCR. It is possible to control the contact and separation between the chip holder 300a on which the micro PCR chip 1 is mounted and the first row block 100a and the second row block 200a for the annealing and extension (or amplification) steps. Can be.

17 illustrates each step of the nucleic acid amplification reaction by the movement of the chip holder of the real-time PCR device 2000 according to another embodiment of the present invention. Nucleic acid amplification reaction by the real-time PCR device 2000 is based on the following steps.

First, a nucleic acid, for example, double-stranded DNA, an oligonucleotide primer having a sequence complementary to a specific nucleotide sequence to be amplified, DNA polymerase, deoxyribonucleotide triphosphates, dNTP in the micro PCR chip 1 ), A sample solution including a PCR buffer (PCR buffer) is introduced, and the PCR chip 10 is mounted on the chip holder 300a. Thereafter or at the same time, the first heat block 100a is heated and maintained at a temperature for the modification step, for example, 90 ° C. to 100 ° C., preferably at 95 ° C. Heating and maintaining the second thermal block 200 at a temperature for annealing and extending (or amplifying), for example, 55 ° C. to 75 ° C., preferably at 72 ° C. . Thereafter, the micro PCR chip 1 is moved downward by controlling the connecting member 520a of the driving means 500a to move the chip holder 300a on which the micro PCR chip 1 is mounted in the first row. Contacting block 100a performs a first denaturation step of PCR (step x). Thereafter, the micro PCR chip 1 is moved upward by controlling the connecting member 520a of the driving means 500a to move the chip holder 300a on which the micro PCR chip 1 is mounted in the first row. Separate from block 100a to end the first denaturing step of PCR, and control the connecting member 520a of the drive means 500a to move the micro PCR chip 1 above the second row block 200a. (Y step). Thereafter, the micro PCR chip 1 is moved downward by controlling the connecting member 520a of the driving means 500a to move the chip holder 300a on which the micro PCR chip 1 is mounted to the second row. The block 100a is contacted to perform the first annealing and extension (or amplification) step of the PCR (step z). Lastly, the micro PCR chip 1 is moved upward by controlling the connecting member 520a of the driving means 500a to move the chip holder 300a on which the micro PCR chip 1 is mounted to the second row. Separate from block 100a to terminate the first annealing and extension (or amplification) step of the PCR, and control the connecting member 520a of the driving means 500a to control the micro PCR chip 1 in a first row block. The nucleic acid amplification reaction is performed by repeating steps x, y, and z after moving up to 100a (circulation step).

18 illustrates a step of observing a nucleic acid amplification reaction in real time using a real time PCR apparatus 2000 according to another embodiment of the present invention. The real-time PCR device 2000 is disposed between the first row block 100a and the second row block 200a, wherein the micro PCR chip 1 is driven by the driving means 500a by the driving unit 500a.

Optical detection modules

700a and 800a implemented to detect an optical signal generated from a PCR amplification product inside the PCR reaction chamber 10 of the micro PCR chip 1 when moving between 100a and the second row block 200a. Specifically, the light source 700a and the light detector 800a are included. That is, in the real-time PCR apparatus 2000, a light source 700a is disposed between the first row block 100a and the second row block 200a and is emitted from the light source 700a on the chip holder 300a. The light detector 800a is disposed to detect the light to be used, or the light detector 800a is configured to detect light emitted from the light source 700a between the first and second row blocks 100a and 200a. ) May be disposed, and the light source 700a may be disposed on the chip holder 300a. In addition, the light detector 800a may be disposed on the driving means 500a, and the through means 530a may be disposed on the driving means 900a to allow the light emitted from the light source 700a to pass therethrough.

By arranging the light source 700a and the light detector 800a, the nucleic acid amplification reaction can be detected in real time in the micro PCR chip 1 during the nucleic acid amplification reaction by the real-time PCR device 2000. do. In order to detect the degree of nucleic acid amplification in the micro PCR chip 1, a separate fluorescent substance may be further added to the sample solution introduced into the micro PCR chip 1. The light source 700a is disposed to be as wide as possible in the spaced space between the first column block 100a and the second column block 200a and is arranged to emit the same light as much as possible. The light source 700a may be operably connected to a lens (not shown) that collects light emitted from the light source 700a and an optical filter (not shown) that filters light of a specific wavelength band.

The nucleic acid amplification reaction by the real time PCR device 2000 detects the degree of nucleic acid amplification in the micro PCR chip 1 in real time.

After completion of the first denaturation step of the PCR, the connecting member 520a of the driving means 500a is controlled to move the micro PCR chip 1 from above the first row block 100a to the second row block 200a. The micro PCR chip 1 is moved to a second row block by moving the upper portion of the PCR or controlling the connecting member 520a of the driving means 500a after the end of the first annealing and extension (or amplification) step. When moving from the top of the 200a to the first row block 200a, the chip holder 300a on which the micro PCR chip 1 is mounted is controlled to control the connecting member 520a of the driving means 500a. A step of stopping on the spaced space between the first row block 100a and the second row block 200a is performed. Thereafter, light is emitted from the light source 700a, and the emitted light passes through the micro PCR chip 1, specifically, the PCR reaction chamber of the micro PCR chip 1, in this case, the PCR reaction. The light detector 800a detects an optical signal generated by amplification of the nucleic acid in the chamber. In this case, the light passing through the micro-PCR chip 1 of the light transmissive material passes through the driving means 500a, specifically, the penetrating portion 530a disposed on the rail 510a to the light emitting portion 800a. Can be reached. Thus, during each cycle of the PCR, the amount of target nucleic acid contained in the initial reaction sample is monitored in real time by monitoring the result of the reaction by amplification of the nucleic acid (fluorescent material bound) in the reaction channel in real time. Can be measured and analyzed.

구현예Embodiment

1. 마이크로 PCR 칩의 제조1. Preparation of Micro PCR Chips

As illustrated in FIG. 12, first to

third plates

100, 200, and 300 having a flat plate shape were prepared from a plastic material. The first plate 100 was manufactured to a thickness of 0.5 mm, and the second plate 200 was made to have a thickness of 2 mm, but was prepared by integrating 19 PCR reaction chambers 10 in a central circular region. The third plate 300 has a thickness of 2 mm, and implements a circular groove on the bottom surface of the third plate 300 to correspond to the central circular region, and protrudes toward the inside of the 19 PCR reaction chambers 10. It was prepared by forming. In addition, a flexible packing part 50 that can be coupled to correspond to the circular groove and the light transmitting part 50 of the third plate 300 was manufactured and attached to the bottom surface of the third plate 300. Thereafter, a double-sided adhesive tape was adhered to the upper portion of the first plate 100 and the second plate 200 was attached to the upper portion of the first plate 100. In this case, the first plate 100 and the second plate 200 may be attached to each other through a thermal bonding, an ultrasonic bonding, an ultraviolet bonding, a solvent bonding method, etc. in addition to the double-sided adhesive tape. Thereafter, PCR samples and reagents are injected into nineteen PCR reaction chambers 10 formed by the attachment of the second plate 200, and the third plate 300 to which the flexible packing unit 50 is attached is placed. The PCR reaction chamber 10 was sealed by attaching an upper portion of the second plate 200. According to FIG. 19, in this embodiment, the completed micro PCR chip 1 can be confirmed. 19A is an appearance of a micro PCR chip 1 according to an embodiment of the present invention, and B is an appearance in which a perspective view of the third plate 300 is reflected in the micro PCR chip 1 of FIG. FIG. C is an enlarged view showing a state where 19 unit modules 50 are arranged in the central circular region of the micro PCR chip 1 of FIG.

2. 실시간 PCR 수행2. Real time PCR

The PCR samples and reagents are related to Influenza A virus, and the genomic RNA of Influenza A virus was distributed from the Center for Disease Control. The reverse transcription reaction solution was prepared using Invitrogen's SupterScript III First-strand Synthesis System for RT-PCR kit together with the pre-generated RNA, the reverse transcription reaction was performed, and cDNA was synthesized. The composition of the reverse transcription reaction solution and cDNA synthesis conditions used in the reverse transcription reaction are shown in Tables 1 and 2 below.

Table 1

Item	density
Genomic RNA	5 ul or more
Primer (2 uM)	0.1 mM
10 mM dNTPs mix	0.5 mM
DEPC-treated water	20 ul
10X RT Buffer	1X
26 mM MgCl ₂	2.5 mM
RnaseOUT (40 U / ul)	40 U
SuperScript III RT (200 U / ul)	200 U

TABLE 2

process	Temperature and time
Denaturation	65 ℃
	ice, 1 min
Annealing	Reaction solution and mixing
cDNA synthesis	50 ℃, 90 min
Terminal reaction	85 ° C, 5 min
Remove RNA	Rnase H added, 37 ° C., 20 min

Subsequently, the primers used for the influenza A virus detection were prepared using Primer 3 with GC% of 40 to 60%, Tm value of 65 to 75 ° C, and the prepared primers manufactured by Genotech (Note). Was synthesized. Then, PCR was performed using the cDNA of the synthetic influenza A virus as a template to confirm the detection of the primer for the influenza A virus. Tables 3 and 4 show the compositions of the PCR samples and reagents used in the PCR and the PCR conditions performed. Each PCR sample and reagent were according to the composition in the table below and brought to a total volume of 16 μl.

TABLE 3

Item	volume
2X PCR Master mix (Polymerase, dNTP)	8 μl
Template (cDNA)	1.6 μl
Primer (Forward / Reverse) 10uM	1.6 μl / 1.6 μl
Distilled Water (DW)	3.2 μl

Table 4

Reaction temperature	Reaction time
Pre-denaturation (95 ℃)	8 sec
P1 (95 degreeC, 1st heat block)	3 sec
P2 (72 ° C, first heat block)	6 sec
Cycle (2 step)	30 times, within 20 minutes with CCD (5 sec)

3. 결과3. Results

PCR performance results were confirmed through a fluorescence picture of the PCR result according to FIG. 20 and a real-time PCR result graph (X-axis: cycle number, Y-axis: fluorescence) according to FIGS. 21 to 23. According to FIG. 20, the fluorescence signal for each unit module 50 of the micro PCR chip 1 is clearly identified as a white dot. In this case, the first region ① of the micro PCR chip 1 of FIG. 20 corresponds to the graph of FIG. 21, the second region ② corresponds to the graph of FIG. 22, and the third region ③ corresponds to the graph of FIG. 23. do. As a result, using the micro PCR chip 1 and the real-time PCR device 2000 according to an embodiment of the present invention it can be confirmed that the real-time PCR results can be measured accurately and quickly.

Claims

A PCR reaction chamber with an open top surface; And

A light transmissive material which contacts the open top surface of the PCR reaction chamber to seal the open top surface and protrudes toward the inside of the PCR reaction chamber from a portion of the sealing surface which is in contact with the open top surface and extends along the optical path A cover having a light transmitting portion of the cover;

Including, a micro PCR chip (Micro-Polymerase Chain Reaction chip).
The method of claim 1,

The PCR reaction chamber is a micro PCR chip, characterized in that implemented to have a liquid sample capacity of 10 μl or less.
The method of claim 2,

The PCR reaction chamber is a micro PCR chip, characterized in that for receiving 5 to 8 μl of liquid samples.
The method of claim 1,

The light transmitting part is a micro PCR chip, characterized in that disposed in the center of the sealing surface.
The method of claim 1,

The light transmitting part is a micro-PCR chip, characterized in that the contact to the bottom surface of the PCR reaction chamber, or implemented to a part spaced upwardly from the bottom bottom surface of the PCR reaction chamber.
The method of claim 1,

The cover further includes a hole that penetrates through the light transmitting part and a flexible packing part which contacts the open top surface of the PCR reaction chamber to seal the open top surface. chip.
The method of claim 1,

Micro PCR chip comprising two or more unit modules consisting of the PCR reaction chamber and the cover.
The method of claim 1,

Micro PCR chip, characterized in that it has a flat plate shape.
The method of claim 1,

A flat plate-shaped first plate;

A second plate having a flat plate shape disposed on the first plate, the plate having the PCR reaction chamber; And

A third plate disposed on an upper portion of the second plate, the third plate serving to cover a top end surface of the PCR reaction chamber to seal the open top surface, and having a light transmitting part;

Micro PCR chip comprising a.
The method of claim 9,

And a hole surrounding the light transmitting part between the second plate and the third plate, and a flexible packing part which contacts the open top surface of the PCR reaction chamber to seal the open top surface. Made, micro PCR chip.
The method of claim 1,

Micro PCR chip, characterized in that further comprises a heat dissipation unit (60) implemented to discharge heat generated from the PCR reaction chamber to the outside.
Micro PCR chip according to claim 1;

One or more thermal blocks implemented to thermally contact at least one side of the micro PCR chip; And

An optical detection module implemented to detect an optical signal generated from a PCR amplification product inside a PCR reaction chamber of the micro PCR chip;

Including, real-time PCR device.
Micro PCR chip according to claim 1;

A first thermal block disposed on a substrate and configured to be in thermal contact with the micro PCR chip;

A second thermal block disposed on the substrate and spaced apart from the first thermal block, and configured to be in thermal contact with the micro PCR chip;

A chip holder movable left and right and / or up and down by a driving means over the first row block and the second row block, and on which the micro PCR chip is mounted; And

A PCR amplification product disposed between the first row block and the second row block, wherein the micro PCR chip is moved between the first row block and the second row block by the driving means; An optical detection module implemented to detect an optical signal originating from the optical signal;

Including, real-time PCR device.