KR101322624B1

KR101322624B1 - Field effect transistor-based detection device for biomolecules containing adsorptive media and detection method using the same

Info

Publication number: KR101322624B1
Application number: KR1020070057859A
Authority: KR
Inventors: 심저영; 유규태; 정원석; 한정임
Original assignee: 삼성전자주식회사
Priority date: 2007-06-13
Filing date: 2007-06-13
Publication date: 2013-10-29
Also published as: KR20080109478A

Abstract

Disclosed are a field effect transistor-based biomolecule detection device using an adsorption medium capable of surface adsorption of biomolecules in a non-covalent manner, and a detection method thereof. This detection device does not require surface fixation or pretreatment of the biomolecules to be detected and has a lower detection limit than conventional field effect transistor based detection devices. In addition, since the detection device depends on the biomolecule concentration of the sample, the detection target molecule can also be quantified.

Adsorption media, beads, FETs, field effects, unfixed, biomolecule detection

Description

Field effect transistor based biomolecule detection device using adsorption medium and its method {FIELD EFFECT TRANSISTOR-BASED DETECTION DEVICE FOR BIOMOLECULES CONTAINING ADSORPTIVE MEDIA AND DETECTION METHOD USING THE SAME}

1 is a side view of the biomolecule detection apparatus of the present invention using an adsorption medium coated with polyethyleneimine (PEI) as one specific embodiment of the present invention.

FIG. 2 is a diagram showing a measurement channel and a standard channel in the biomolecule detection device of FIG. 1 filled with a PEI coated adsorption medium in one specific embodiment of the present invention.

FIG. 3 is a diagram illustrating signal changes occurring when a DNA sample is injected into the measurement channel as shown in FIG. 2 and when the sample is washed with a buffer solution.

4 is a diagram showing the change in FET signal according to the concentration difference when injected into the measurement channel shown in FIG. 2 19 mer oligodioxynucleotide having a different concentration of 20 μM, 50 μM.

FIG. 5 is a graph observing whether an increase in the FET signal size due to concentration of the sample occurs when the 400 bp PCR product at the concentration of 1 ng / μL is added to the beads placed on the FET. The graph was divided from a to e according to time.

6A to 6E are enlarged views of the graph divided from a to e in FIG.

The present invention relates to a biomolecule detection apparatus and method for detecting the presence or concentration of biomolecules using a field effect transistor.

Among devices for detecting biomolecules by electrical signals, transistor-based biosensors include a transistor. Transistor-based biosensors are fabricated using semiconductor processes, and have the advantage of fast electrical signal conversion and easy integration into integrated circuits and microelectromechanical systems (MEMS) processes. Has been going on.

Among the transistor-based biosensors, a method of measuring a biological response using a field effect transistor (hereinafter, referred to as a “FET”) is typical. For these FET-based biosensors, small detectors typically used in lab-on-a-chip or suitable for point-of-care products are the final product. Most FET-based biosensors of the prior art measure surface charge density and are typically present in the Debye length, and measure the electrical signal of biomolecules adsorbed on the gate surface. Prior patents include US Pat. No. 4,238,757. This patent relates to a biosensor that measures antigen-antibody reactions with a current in the semiconductor inversion layer due to surface charge density changes to detect proteins in biomolecules. US Pat. No. 4,777,019, on the other hand, relates to adsorption of biological monomers on the gate surface to measure the degree of hybridization with the complementary monomers by FET.

However, these techniques had to immobilize the biomolecules to be detected, and there was a problem that the sensor response was slow. It was also difficult to integrate into unmanned microscopic detection device technologies such as lab-on-a-chip. First of all, there was a fundamental problem to check whether the immobilization treatment affected the measurement results.

It is an object of the present invention to provide a method for detecting biomolecules in a sample by adsorbing the biomolecules on a surface of a medium in a non-covalent manner without fixing the biomolecules or a probe for detecting such biomolecules on a detection device surface. Conventionally, in the absence of surface fixation of biomolecules or probes, it was difficult to detect low concentrations of biomolecule samples. However, in the present invention, the present invention can dramatically quantify biomolecules such as DNA at low concentrations by dramatically increasing the adsorptive sites. It is a feature that makes it possible.

In order to achieve this object, the present invention provides a biomolecule detection apparatus and a detection method using an adsorption medium, the configuration is formed on a semiconductor substrate, the surface of the adsorption site of the source and drain regions, the detection target biomolecules separated from each other And a standard electrode capable of applying a constant voltage between any one of the source and drain regions and the substrate, and means for measuring an electrical signal generated by the applied voltage.

In one specific embodiment of the present invention, the adsorption medium having the adsorption site uses a material selected from the group consisting of glass, silicon, and plastic, and can be charged or stacked interaction for adsorption of the biomolecules to be detected. It is characterized by the surface being coated with a material which can perform stacking interaction. In one specific embodiment of the present invention, the adsorption medium is in the form of beads.

As the biomolecule to be detected according to the present invention, the biomolecule to be detected may be deoxyribonucleic acid (DNA), ribonucleic acid (RNA), protein, carbohydrate, peptide-nucleic acid (PNA), carbohydrate and conjugates thereof ( conjugate), and in one embodiment of the present invention, DNA is detected using a glass material adsorption medium coated with polyethyleneimine.

In an aspect of the present invention, the electrical signal measured by the biomolecule detection device is characterized in that the source-drain current or the source-drain voltage.

The present invention also provides a method for detecting biomolecules using an adsorption medium, the detection method of the present invention is a method for detecting biomolecules using a field effect transistor, (a) the biomolecules can be adsorbed in a non-covalent manner. Inducing adsorption of the biomolecules to be detected by reacting a sample containing the biomolecules with an adsorption medium having a location on the surface; (b) positioning the adsorption medium having completed step (a) between the source and drain regions of the field effect transistor and (c) measuring an electrical signal between the source and drain regions; The effect transistor is characterized in that the gate electrode layer is absent.

On the other hand, in another aspect of the present invention after performing the steps (a) to (c)

(d) reacting the adsorption medium not reacted with the sample in step (a) with a buffer solution containing no biomolecules, and performing steps (b) to (c) for the adsorption medium reacted with the buffer solution. And performing (e) comparing the electrical signal measured in the step (c) with the electrical signal measured in the step (d). Using this method, the concentration of biomolecules can be determined by comparison with a control sample (buffer solution) that does not contain biomolecules.

In another aspect of the present invention, there is provided a method for detecting biomolecules using an adsorption medium, which can prevent drift of a detection signal. Placing an adsorption medium on the surface of the field effect transistor between a source and a drain region of the field effect transistor, wherein the adsorption medium has a surface on which the adsorbable medium can adsorb in a non-covalent manner; (b) reacting by flowing a buffer solution containing no biomolecule into the adsorption medium located in step (a); and (c) measuring an electrical signal between the source and drain regions to correct signal drift. And the gate effect layer is absent from the field effect transistor.

In one embodiment of the present biomolecule detection method, the measurement of the electrical signal in step (c) is performed by applying a voltage between any one of the source or region and the substrate and measuring the signal generated by the voltage. It is characterized by.

Hereinafter, the configuration of the present invention will be described in detail.

According to the present invention, the adsorption reaction of the biomolecule to be detected occurs on the surface of an adsorption medium having a site capable of adsorption of biomolecules including DNA, and then the solution containing the adsorption medium is transformed into a field effect transistor ( The principle is to locate between the source and drain regions on a field effect transistor, FET, hereinafter referred to as " FET " and measure the change in the electrical signal of the transistor that occurs accordingly.

The detection apparatus of the present invention uses a small-scale modification to a conventional field effect transistor as an electric signal generator. One specific embodiment of a modified field effect transistor used in the present invention is shown in FIG. The transistor of FIG. 1 is fabricated in a CMOS process, the configuration of the transistor being a substrate (p-type substrate in FIG. 1) made of a doped semiconductor material, formed spaced apart on the substrate and doped with opposite polarity to the substrate. (Indicated by " n ⁺ " in FIG. 1) and a source and drain region and a standard electrode (indicated by a black box with a handle in FIG. 1). In such a modified field effect transistor, there is no gate electrode layer included in a conventional transistor, and a standard electrode is instead included to apply a constant voltage corresponding to the gate voltage. The current between the source and the drain causes a specific doped region of the substrate to flow into a channel (indicated by " channel " in FIG. 1). In other words, the modified field effect transistor used in the detection device of the present invention has a difference in deformation of the gate portion as compared with a conventional field effect transistor. An appropriate number of insulating layers can be placed on the substrate of the present invention, which can be adjusted by those skilled in the art as needed.

The biomolecules to be detected of the present invention include all biomolecules capable of adsorbing to the adsorption medium at an appropriate strength. Non-limiting examples of such biomolecules to be detected include deoxyribonucleic acid (DNA), ribonucleic acid (RNA), proteins, carbohydrates, peptide-nucleic acid (PNA), carbohydrates and conjugates between them. There are types such as glycoproteins, lipid proteins, and protein-DNA complexes.

Biomolecules such as proteins, nucleic acids, carbohydrates, and the like contain many sites that can be charged on the surface and thus can interact electrostatically with inorganic ions. The aqueous solution containing such charged biomolecules and their counterions increases the concentration of the electrolyte and thus increases the ionic strength. On the other hand, since nucleic acids can be stabilized through π-π interactions between neighboring nitrogen bases, the base planes are stacked side by side. This is called base stacking interaction. Since π-π interaction, which is the essence of stacking, is shared by all aromatic planar ring molecules, aromatic side chains such as phenylalanine and tryptophan are known to have stacking interactions. Biomolecules, such as DNA or proteins, can cause opposite charges or stacking interactions on the surface of adsorption media (e.g. aromatics such as ethidium bromide, indole and pyrene). Molecules) to adsorb to the adsorption medium surface.

Biomolecules, such as DNA and proteins, are large in size, and when charged, carry a large number of corresponding ions and thus greatly influence the ionic strength of the solution in which they exist. As compared with the case where the adsorption medium to which the biomolecule is adsorbed is placed between the source and the drain region, and the case where the buffer solution containing the simple inorganic salt is located, the ionic strength is large when the biomolecule adsorption medium solution is placed. As a result, the current flowing through the channel of the modified FET or the source-drain applied voltage characteristic when the voltage is applied is very different from that of the buffer solution. Therefore, the electrical signal characteristics of the field effect transistor vary depending on the presence of biomolecules in the aqueous solution. In actual measurement, when a constant voltage is applied to the standard electrode, an aqueous solution of the same adsorption medium (hereinafter referred to as "measurement medium") that reacts with the sample but does not react with the sample is deformed. The effect on the electrical signal of the FET is measured and compared.

The device of the present invention detects an electrical signal based on the reversible interaction (electrostatic attraction, stacking interaction, etc.) between the biomolecule to be detected and the adsorption medium, so that the biomolecule needs to be immobilized on the substrate. There is no inconvenience to immobilize the sample in advance. Although the present invention is not a method of permanently fixing the biomolecule on the surface of the adsorption medium, the biomolecules can be accumulated by adsorption of low concentration samples because the biomolecules can be accumulated at the adsorption sites when the sample is repeatedly added to a low concentration. The advantage is that detection is possible.

In addition, the configuration of the present invention provides an advantage that the detection device can be recycled only by washing with a buffer solution. The adsorption of the present invention is low enough to withstand the washing by the buffer solution close to the biomolecular conditions of the biomolecule due to the low concentration of the inorganic salts, but is enough to dissociate the adsorbed biomolecules when washed with a high concentration of salts. Since it has the proper strength, it is convenient to change only the composition of the washing solution. In the present invention, for convenience, a channel for filling a standard bead and measuring an electrical signal (hereinafter referred to as a "standard channel") and a channel for filling and measuring a measurement bead (hereinafter referred to as a "measurement channel") are distinguished, but a separate FET device for each channel It is not necessary to have In the present invention, the channel can be alternately used as the standard channel and the measurement channel while washing with one FET-based detection device.

The FET device of the present invention is divided into a standard channel and a measurement channel which are distinguished temporally or spatially, and the standard channel is filled with an adsorption medium without adsorption of biomolecules or with a surface treated adsorption medium. When the standard channel is filled with the surface treated adsorption medium, only the buffer solution containing no biomolecule may be flowed to measure the electrical signal. In this manner, the drift of the electrical signal may be corrected.

In one embodiment of the present invention, there is provided an adsorption medium in which a biomolecule to be detected is located between a source and a drain region, and the biomolecule can be adsorbed without having to be immobilized on a substrate, and the adsorption medium and an aqueous solution containing the same flow. A measuring device with a partition ("filter" in Figure 2) is provided so as not to exit. 2 is a schematic diagram showing detection of the presence of biomolecules with such a measuring device in one specific embodiment of the present invention. In FIG. 2, the standard medium without the addition of the sample and the measurement medium for measuring the sample are displayed in different colors to distinguish the shapes filled in the biomolecule detection device. Each was marked.

The material of the adsorption mediator of the present invention may be any surface treatment such that the biomolecule to be detected can be adsorbed or the adsorption site is provided on the original surface itself. Preferred examples include plastic materials such as glass, silicone and polyethylene. The adsorption medium of the present invention may be any shape and size suitable for adsorption of the biomolecule to be measured. One specific embodiment of the adsorption medium is a bead. Surface treatment of the adsorption medium means that the surface is coated with a material capable of inducing adsorption by interacting with a biomolecule to be detected, such as a material capable of charging or stacking interaction. Examples of positively charged coating materials include monomers or polymer materials having amino (NH ₂ ) groups or imine (-NH) groups, and examples of negatively charged coating materials include monomers or polymer materials having carboxy (COOH) groups. Can be mentioned. Typical materials capable of stacking interactions are aromatic molecules, such as ethidium bromide and pyrene. In one embodiment of the present invention, the DNA to be detected is adsorbed onto glass beads coated with a positively charged polyethylene imine.

As described above, the biomolecule is adsorbed to the measurement medium to detect the electrical signal through the measurement channel. On the other hand, the standard medium without biomolecule adsorption is placed on the standard channel to detect and compare the same electrical signal. Both the measurement medium and the standard medium are located in suspended form in solution between the source and drain regions. When the suspension containing the adsorption medium is properly positioned, a voltage is applied to the standard electrode, which corresponds to the application of a gate voltage in a conventional FET device. Examples of detectable electrical signals are current between source and drain or voltage between source and drain.

Example

Hereinafter, the present invention will be described in more detail with reference to Examples and Experimental Examples. The examples and experimental examples are intended to help the understanding of the invention to the last, and are not intended to limit the scope of the invention in any form.

Example 1 Manufacture of DNA Detection Apparatus

The biomolecule detection apparatus and detection method of the present invention were performed using the biomolecule to be detected as DNA. 19 mer oligonucleotide was used as the DNA to be detected, and its base sequence is 5'-TGGTAAGATACCGTCACAG-3 '. Glass beads having an average diameter of 100 μm were adopted as adsorption media and polyethyleneimine was coated on the surface of the beads using a polyethyleneimine-silane compound. The beads weigh about 150 μg per thousand.

Deformed field effect transistor (FET) devices that generate electrical signals for detection are fabricated using standard CMOS processes. An insulating layer is stacked on the p-type doped semiconductor substrate, and there is no gate electrode layer stacked on the insulating layer, but a gate electrode may be applied by installing a standard electrode.

Meanwhile, the modified FET device was equipped with a polytetrafluoroethylene (PTFF) filter having a pore size of 0.45 μm, as shown in FIG. 2, to trap the bead suspension.

Experimental Example 1 Observation of Potential Change According to DNA Sample Adsorption

It was confirmed whether the change of the potential according to DNA sample adsorption can be observed using the sample of Example 1 and a detection apparatus. The concentration of 19 mer DNA to be detected in the sample was 50 μM. Whether DNA adsorbed on the beads was confirmed using DNA labeled with fluorescent dye Cy3.

The measurement channel was filled with a buffer solution suspended in polyethyleneimine coated glass beads and the standard channel was filled with a buffer solution suspended in glass beads not coated with polyethyleneimine. The composition of the buffer is as follows: pH is adjusted to around 3.8-4.2 by adding HCl to 0.01 mM KCl solution. Once the beads were filled, a standard voltage of 2.4 V was applied to the standard electrode to measure the applied source-drain potential difference. In order to measure the change in the potential difference according to washing, 500 μL of the culture buffer was flowed at a flow rate of 0.5 μL per minute to wash the beads of the standard channel and the measuring channel every 10 minutes. 200 μL of a 50 μM DNA sample was added to the beads, incubated at room temperature for 30 minutes, and the electrical signals were measured.

3 is a graph measuring the potential difference while washing as described above. In FIG. 3, the graph labeled "no sample" represents the source-drain potential difference of the standard channel, and the graph labeled "sample" represents the potential difference of the measurement channel, respectively. When the sample DNA added to the measurement channel is adsorbed (marked "up" in Fig. 3), a significant potential difference decrease (approximately 100 mV) appears, and it can be confirmed that the potential difference increases temporarily even after washing, and then recovers to the level before washing again. have. In contrast, in the case of the standard channel (graph labeled “no sample” in FIG. 3), when the sample DNA is added, the potential difference increases (about 80 mV), and the increased potential value is reduced to the original state by washing as in the case of no beads The aspect is shown. The potential difference increases when the second sample DNA is added to the measurement channel (near 12000 seconds in the graph of FIG. 3) and the increased value approaches the potential value before the second sample DNA is added by washing. Due to this, the DNA adsorption sites of polyethyleneimine are all saturated, and it seems that the DNA adsorption is impossible. In this case, even if additional sample DNA is added, the added amount will be removed by washing.

Through this experimental example, it can be seen that the electrical signal change according to the adsorption of the DNA, the biomolecule to be detected, can be measured. In particular, the electrical signal has a robust characteristic that its value does not change even after washing. I could see that.

Experimental Example 2 Whether or not it depends on the measured potential difference DNA adsorption amount

If the magnitude of the signal of the biomolecule detection device depends on the concentration in the sample of the biomolecule to be detected, not only the presence of the biomolecule but also the concentration in the sample can be measured. The inventors tested whether the difference in the concentration of DNA changes the magnitude of the measured potential difference. Using the apparatus of Example 1 was measured similarly to Experimental Example 1, the change in the potential value was observed by varying the concentration of the DNA sample to be added to 50 μM or 20 μM.

Figure 4 is a graph showing the magnitude of the potential value according to the concentration of the sample DNA. The meaning of "sample" and "no sample" is the same as in FIG. 3. When the DNA sample was added, the 20 and 50 μM concentrations decreased by 33 mV and 85 mV, respectively, but as the adsorption sites were filled, the potential drop was 24 mV and 12 mV, respectively. Shrunk. Although the potential difference of 50 μM was greater when the first sample was added, the potential change was smaller than that of the 20 μM when the second DNA was added, which remained in the beads after the addition of 50 μM DNA and 20 μM samples under experimental conditions. It is considered that this is due to the difference in free adsorption sites.

Through this experimental example, it can be seen that it is possible to detect the concentration-dependent electrical signal in the sample of the biomolecule.

Experimental Example 3 Signal Detection Through Concentration of Low Concentration Samples

In the case of 50 μM and 19 mer DNA measured in Experimental Examples 1 and 2, the concentration in the sample was about 300 ng / μL. When a much smaller sample was repeatedly added to the detection apparatus of the present invention and concentrated at the adsorption site, it was tested whether a low concentration sample could be detected. The measurement method was similar to the above Examples and Experimental Examples, but the beads were PEI coated beads of silicon material having a diameter of 15 μm, and washing with a buffer solution was performed by adding a total of 50 μL at a flow rate of 0.25 μL per minute.

Concentration was tested on samples containing 1 ng / μL of 400 bp polymerase chain reaction (PCR) product. 5 is a graph in which the potential value is measured while the sample is repeatedly added to the measurement channel. In the case of the sample of concentration, the measurement potential value was about 1 mV without concentration, which was indistinguishable from the signal noise level of 1 to 2 mV, and the concentration value was about 3 mV after 20 concentrations. However, continuous injection of 40 samples of 1 ng / μL 400 bp PCR product resulted in a potential difference of about 8 mV, indicating a reliable level of detection of signal noise. In the control experiment in which only the buffer solution was injected relatively repeatedly, the measured potential value remained about 1 mV even after 20 repeated injections, indicating that the concentration effect of the present invention was dependent on the presence of DNA in the sample. Each portion of FIG. 5 is enlarged and shown in FIGS. 6A to 6E.

As seen in this experimental example, the detection device of the present invention enables signal amplification through concentration, even in low concentration samples, so that biomolecules can be obtained even for samples having a concentration lower than the detection limit measured by the FET-based biosensor according to the prior art. Can be detected.

The biomolecule detection device of the present invention has a characteristic that is completely different from the existing FET-based biosensors because it is a detection method using a non-covalent adsorption medium without fixing or pretreatment of the detection target biomolecule. In addition, it is possible to quantify the electrical signal that depends on the concentration of biomolecules in the sample, and because it provides a large adsorption surface area, there is an advantage that can be applied to biomolecule samples of lower concentration than the existing detection limit. In addition, a simple cleaning can regenerate the detection device, saving detection costs.

Claims

A source region and a drain region formed on the semiconductor substrate and spaced apart from each other,

Adsorption media with adsorption sites on the biomolecules to be detected,

A standard electrode capable of applying a constant voltage between any one of the source region and the drain region and the substrate;

Means for measuring an electrical signal generated by the applied voltage,

And said adsorption mediator is movable relative to the region between said source region and said drain region.

The method of claim 1,

The adsorption medium is a detection device of biomolecules using the adsorption medium, characterized in that the material is selected from the group consisting of glass, silicon, plastic.

3. The method of claim 2,

The selected material is glass, characterized in that the detection device of biomolecules using the adsorption medium.

The method of claim 1,

The adsorption medium is a detection device of biomolecules using the adsorption medium, characterized in that the bead made of glass, silicon or plastic material.

The method of claim 1,

The adsorption site is a biomolecule detection device using an adsorption medium, characterized in that the composition is covered with a chargeable material.

The method of claim 5,

The charged material is polyethyleneimine, characterized in that the detection device of biomolecules using the adsorption medium.

The method of claim 1,

The adsorption site is a biomolecule detection device using the adsorption medium, characterized in that the composition is coated with a material that can cause stacking interaction (stacking interaction).

The method of claim 1,

The biomolecule to be detected is one or more substances selected from deoxyribonucleic acid (DNA), ribonucleic acid (RNA), protein, carbohydrates, peptide-nucleic acid (PNA), carbohydrates and conjugates thereof. An apparatus for detecting biomolecules using an adsorption medium, characterized in that.

9. The method of claim 8,

The detection target biomolecule is a deoxyribonucleic acid, characterized in that the biomolecule detection device using an adsorption medium.

10. The method of claim 9,

The deoxyribonucleic acid is a product of a polymerase chain reaction (PCR), characterized in that the detection device of biomolecules using the adsorption medium.

10. The method of claim 9,

The adsorption medium is a detection device of biomolecules using the adsorption medium, characterized in that the glass material coated with polyethyleneimine.

The method of claim 1,

The electrical signal is at least one of a source-drain current or a source-drain voltage, characterized in that the detection device of the biomolecule using the adsorption medium.

In the detection method of biomolecules using a field effect transistor,

(a) inducing adsorption of the biomolecule to be detected by reacting a sample containing the biomolecule with a adsorption medium having a surface on which the biomolecule can adsorb in a non-covalent manner;

(b) placing the adsorption medium having completed step (a) between a source region and a drain region of the field effect transistor; And

(c) measuring an electrical signal between the source region and the drain region,

The field effect transistor has no gate electrode layer,

And the adsorption medium is movable relative to a region between the source region and the drain region.

14. The method of claim 13,

(d) reacting the adsorption medium not reacted with the sample in step (a) with a buffer solution containing no biomolecules, and performing steps (b) to (c) for the adsorption medium reacted with the buffer solution. Steps to perform and

(e) comparing the electrical signal measured in the step (c) and the electrical signal measured in the step (d), characterized in that the electrical detection method of the biomolecule using the adsorption medium.

In the detection method of biomolecules using a field effect transistor,

(a) placing an adsorption medium on the surface between the source region and the drain region of the field effect transistor, wherein the adsorption medium has a surface on which the biomolecule can adsorb in a non-covalent manner;

(b) reacting by flowing a buffer solution containing no biomolecule to the adsorption medium located in step (a); and

(c) measuring the electrical signal between the source region and the drain region to correct signal drift, wherein the field effect transistor is free of a gate electrode layer, wherein the biomolecule of the biomolecule using the Detection method.

The method according to claim 13 or 14,

The source region and the drain region are formed on a semiconductor substrate,

The measurement of the electrical signal in the step (c) is made by applying a voltage between any one of the source region or the drain region and the substrate and measuring the signal generated by the voltage. Method of detecting biomolecules.

17. The method of claim 16,

The signal generated by the voltage is at least one of a source-drain current or a source-drain voltage, characterized in that the biomolecule detection method using the adsorption medium.

14. The method of claim 13,

The adsorption medium of step (a) is characterized in that the material selected from the group consisting of glass, silicon, plastic, biomolecule detection method using the adsorption medium.

14. The method of claim 13,

The biomolecule adsorption site of step (a) is characterized in that the composition is coated with a material that can be charged, biomolecule detection method using the adsorption medium.

20. The method of claim 19,

The method of detecting a biomolecule using the adsorption medium, characterized in that the chargeable material of step (a) is polyethyleneimine.

14. The method of claim 13,

The biomolecule adsorption site of step (a) is characterized in that the composition is coated with a material that can cause stacking interaction, biomolecule detection method using the adsorption medium.

14. The method of claim 13,

The biomolecule to be detected in step (a) is at least one material selected from deoxyribonucleic acid (DNA), ribonucleic acid (RNA), protein, carbohydrate, peptide-nucleic acid (PNA), carbohydrate and conjugates thereof. A biomolecule detection method using an adsorption medium.

23. The method of claim 22,

The detection target biomolecule is a deoxyribonucleic acid, characterized in that the biomolecule detection method using the adsorption medium.

24. The method of claim 23,

The deoxyribonucleic acid is a product of a polymerase chain reaction (PCR), characterized in that the biomolecule detection method using the adsorption medium.

25. The method of claim 24,

The adsorption medium of step (a) is a glass material, characterized in that the polyethyleneimine is coated, biomolecule detection method using the adsorption medium.