KR20100113698A - A biosensor based on carbonnanotube-field effect transistor and a method for producing thereof - Google Patents

Abstract

PURPOSE: A biosensor and manufacturing method of carbon nanotube-field effect transistor base is provided to detect target bio-materials using a biosensor. CONSTITUTION: A biosensor and manufacturing method of carbon nanotube-field effect transistor base comprises substrates(1,2), an insulating layer, a source electrode(3), a drain electrode(4), a channel and a detection area(6). The source electrode and a drain electrode are formed on an insulating layer. The middle part of the channel is cut between the source electrode and the drain electrode. A detection target is fixed on a detection area around the channel whose middle part is cut.

Description

Carbon nanotube-field effect transistor based biosensor and its manufacturing method {A BIOSENSOR BASED ON CARBONNANOTUBE-FIELD EFFECT TRANSISTOR AND A METHOD FOR PRODUCING THEREOF}

A substrate, an insulating layer, a source-and-drain electrode formed on the insulating layer, a channel having a middle cut shape positioned between the source electrode and a drain electrode, and a detection material covering the upper part with the middle cut channel as the center A biosensor having this detection area to be fixed, a manufacturing method thereof, and a method for detecting a biomaterial by the biosensor are disclosed. In more detail, in the present invention, when detecting a biomaterial using a carbon nanotube transistor using a field effect, the contact resistance is changed by fixing a receptor in a detection region made of a conductive material and selectively coupling the detector with a detection target material, thereby The present invention relates to a biosensor for detecting a target biomaterial by using a change in the amount of current flowing from an electrode to a drain electrode, a method for manufacturing the same, and a method for detecting the target biomaterial using the same.

A biosensor is a system that converts a signal into a recognizable signal such as color, fluorescence, or electrical signal by using a biological element or mimicking a biological system when obtaining information from an object to be measured. It can be configured in various forms according to the substance to be measured, the biological element fixed to the sensor, and the type of signal converter. The signal conversion methods are electrochemical, thermal, optical, and mechanical. A variety of physicochemical techniques such as) are used.

Biosensors vary according to the substance to be measured, the biological elements immobilized on the sensor, and the type of signal transducer. The first biosensor was known as a Glucose sensor manufactured by Clark using a dialysis membrane to measure glucose in 1962. In the early days, the enzyme was mostly fixed by an enzyme to a signal transducer, but recently, with the rapid development of molecular biology, Sensors manufactured using monoclonal antibodies or antibody-enzyme conjugates have been developed and used. In addition, research on the development of chip sensors such as DNA chips and protein chips for processing a large amount of genetic information at high speed is encouraging. This is concentrated.

Biochip refers to immobilization of biomolecules such as DNA and protein on a small substrate made of glass, silicon, or nylon. In this case, immobilization of DNA to immobilize DNA chip and protein The set is called a protein chip. Biochips can also be broadly divided into microarray chips and microfluidics chips. Microarray chips are biochips that can arrange and attach thousands or tens of thousands or more of DNA or proteins at regular intervals, and process the analyte to analyze their binding patterns, such as DNA chips and protein chips. Microfluidics chips, also called lab-on-a-chips, are biochips that inject a small amount of analyte and react with various biomolecular probes or sensors immobilized on the chip. DNA chips can be classified into oligonucleotide chips, cDNA chips and PNA chips according to the type of probe to be immobilized. Oligonucleotide chip technology is a new method for investigating large-scale genetic diversity and attaches a large number of synthetic oligonucleotides at precise locations in a small space of the support to hybridize with very small amounts of target sequences. You can now search for. Such oligonucleotide chips are expected to contribute to drug resistance screening diagnosis, mutation screening, single nucleotide polymorphism (SNP), disease diagnosis, or genotyping.

The application fields of biosensor can be classified into six categories as follows.

① Clinical diagnosis / medical field: It accounts for about 90% of the total biosensor market. Most glucose sensors for blood glucose measurement are rapidly increasing, but the demand for point-of-care testing (POCT) is rapidly increasing, and biosensors that can measure various biomaterials such as lactic acid, cholesterol, and urea are expected to increase.

② Environment: Detects environmental substances such as environmental hormones, BOD of wastewater, heavy metals and pesticides. Research on sensors that can detect even low concentrations with selectivity to various environmental hormones such as dioxin is being conducted at various angles.

③ Food: It is used to detect harmful substances such as residual pesticides, antibiotics, pathogens and heavy metals, and it is applied to food safety inspection.

④ Military: Biosensor that can detect biochemical weapons of mass destruction such as sarin and anthrax. To cope with biological weapons, miniaturization is essential for rapid measurement time and field use.

⑤ Industrial Use: Control the growth conditions of microorganisms in fermentation process or monitor specific chemicals from chemical / petrochemical, pharmaceutical and food process.

⑥ For research purposes: Kinetic analysis of binding between biomaterials and measurement of single molecule behavior.

A field effect transistor is an element that converts a voltage signal input to a gate into a current signal output from a source electrode or a drain electrode. The field effect is that when a field is applied to a semiconductor, carriers (free electrons or holes) in the semiconductor are negative (-) carriers, that is, electrons (+) carriers on the (+) side, depending on the applied electric field. In other words, it refers to a phenomenon in which holes form a conductive channel through which electricity can flow.

When a voltage is applied between the source electrode and the drain electrode, charged particles existing in the channel move between the source electrode and the drain electrode along the electric field direction, and are output as a current signal from the source electrode or the drain electrode. At this time, the intensity of the output current signal is proportional to the density of the charged particles. When a voltage is applied to a gate provided on the upper side, the lower side, or the lower side of the channel through the insulator, the density of the charged particles present in the channel changes, so that the current signal can be changed by converting the gate voltage using this.

Carbon nanotubes can exhibit electrical conductivity as good as copper, thermal conductivity as good as diamond, and strength at 100 times better than steel at 1/6 weight and high strain against fracture. Carbon nanotubes discovered by Dr. Iijima, Japan, in 1991 have been observed to have a number of unusual quantum mechanical phenomena due to their quasi one-dimensional quantum structures. Their diameters are very small, ranging from a few tens of nanometers (nm), It is hollow. Due to the very unique one-dimensional carbon structure of the carbon nanotubes exhibits excellent mechanical, thermal, and electrical properties, it is being evaluated as a next-generation new material material. Among other advantages, the application to field effect transistors, flat panel display devices, electronic devices, etc. is being studied throughout the industry by utilizing the excellent mechanical properties and high electrical and thermal conductivity. Increasingly, attempts are being made.

Among them, in the application of transistor devices, in 1998, researchers at Delft University in the Netherlands implemented transistors operating at room temperature using carbon nanotubes (Sander J. Tans et al ., Nature 1998, 393, 49). According to this result, the carbon nanotube-based electronic device having excellent physical and electrical properties is 100 times faster than the conventional silicon-based electronic device, and the integration speed is high, and the power loss is low. It was. This result is the first case that shows the applicability in future electronic devices based on carbon nanotubes.

Since then, the application of various nano-devices based on carbon nanotubes has been published in numerous papers, patents, etc. in many research institutes around the world. Researchers of the group of Harvard University are using carbon nanotubes in 2009 as a field-effect-transistor biosensor channel, the results of measuring the change in the surface charge of the biomaterials with high sensitivity introduced (Charles M. Liber such. Science , 2001, 293, 1289). Later, as technology developed, large changes in charge on the surface were measured by enzymatic reactions. Then, small changes in surface charge of protein-protein bonds were measured. In 2005, researchers at Chungnam National University and the Institute of Chemical Research introduced the concept of biosensors using carbon nanotube field effect transistors (CNT-FETs). This is because CDI-Tween20 is a linker attached to the surface of the carbon nanotubes so that the DNA aptamer is attached to the carbon nanotubes. By using, specific target molecules were measured at the level of 10 nM, thereby implementing a high-performance CNT-FET biosensor (Hye-Mi So et al. , J. AM. Chem. Soc., 2005, 34, 11906). As a result of the continuous research, it was announced that the closer the coupling distance between the carbon nanotube surface and the biomaterial required for detection is, the higher the sensitivity could be obtained, and successfully detected 1.8 nM IgE using the CNT-FET sensor. Thereby increasing the industrial applicability (Kenzo Maehashi et al., Anal. Chem., 2007, 79, 782).

Korean Patent Laid-Open Publication No. 2007-53545 discloses that when a target molecule hybridizes to a probe, conductivity is increased by carbon nanotubes attached to the target molecule, thereby easily detecting hybridization of the target molecule. A biochip made of an insulating layer positioned between these electrodes is disclosed.

Korean Patent No. 10-455284 discloses growing a nanometer diameter carbon nanotube on a non-conductive substrate, and then transferring a charge of a polarity opposite to the net charge of various receptors that bind to the target biomolecule. As a patent for the conventional micro ( ^10-6 ) level array technology can be arranged or highly integrated at the nano ( ^10-9 ) level in a desired pattern by hooking and fixing each receptor arbitrarily at a predetermined position on the chip. A nanoarray comprising a substrate, and a plurality of carbon nanotubes arranged on the substrate, and selectively attaching a receptor that binds to the target biomolecule onto the carbon nanotubes at a desired position by applying an electric field to the carbon nanotubes. A biomolecule detection sensor of the type is disclosed.

In addition, Korean Patent Laid-Open Publication No. 2007-22165 has a field-effect transistor having a substrate, a source electrode and a drain electrode formed on the substrate, and a channel serving as a current path between the source electrode and the drain electrode. A sensor for detecting a signal, the field effect transistor detects an interaction sensing gate for fixing a specific substance selectively interacting with the detection target material, and detects this interaction as a change in the characteristics of the field effect transistor. The invention is characterized by having a gate to which a voltage is applied.

However, despite many research efforts, the application of biosensors using carbon nanotubes has not been published in the case where the detection material has a low concentration such as 1nM or less.

Accordingly, an object of the present invention is to provide a biosense suitable for the detection of biomolecules having a concentration of 1 nM or less.

Another object of the present invention is to provide a method for manufacturing a biosensor having the above characteristics.

Yet another object of the present invention is to provide a method for detecting a target biomaterial using a biosensor having the above characteristics.

In order to solve the above problems, the present invention, when detecting a bio-material using a carbon nanotube transistor using a field effect, by fixing the receptor in the detection region consisting of a conductive material to selectively contact with the detection target material Disclosed is a biosensor for detecting a target biomaterial by using a change in resistance and a change in the amount of current flowing from a source electrode to a drain electrode.

More specifically, the present invention relates to a substrate, an insulating layer, a source electrode and a drain electrode formed on the insulating layer, a channel having a middle cut shape positioned between the source electrode and the drain electrode, and a channel having the middle cut off. The present invention relates to a biosensor having a detection area to be covered with a detection target material to be covered.

The substrate used in the biosensor in the device of the present invention is selected from the group consisting of various non-conductive polymers such as, but not limited to, silicon, glass, molten silica, quartz, plastic, polydimethylsiloxane (PDMS), and combinations thereof.

The insulating layer of the present invention may be composed of an electrical insulating material, the electrical insulating material is, for example, silicon dioxide (SiO ₂ ), silicon nitride (Si ₃ N ₄ ), Teflon ( ^?? ), polydimethyl methacryl PDMS-Polydimethylsiloxane, polymethylmethacrylate (PMMA). The insulating layer may be formed on any one of the bottom, top and side of the channel.

The source electrode and the drain electrode are composed of gold, silver, titanium, platinum, and the like.

The intermediate channel is carbon nanotube and preferably has semiconducting properties.

In the present invention, the detection region to which the target protein is fixed is composed of a metal layer and a semiconductor layer, and includes, but is not limited to, gold (Au), titanium (Ti), platinum (Pt), chromium (Cr), and copper. (Cu), aluminum (Al), palladium (Pd), and nickel (Ni) and combinations thereof, and may be selected from the group consisting of, but not limited to, p or n doped silicon (Si). ), Zinc oxide (ZnO), gallium / arsenic (GaAs), gallium / nitrogen (GaN), indium / phosphorus (InP), and the like. In the present invention, this region serves as a gate electrode.

The biosensor detects biomolecules by including a receptor fixed to the detection area. The receptor refers to a substance that can interact with a specific substance by specific binding. When the target material interacts with the receptor fixed to the detection region by specific binding, the work function of the electrode is changed, which changes the contact resistance between the carbon nanotube and the detection region. The change in contact resistance affects the flow of current, and the detection target substance is detected using the change.

Many specific materials can be immobilized on the interaction sensing gate. The interaction sensing gate to which a specific material is immobilized can be preferably used in a biosensor for detecting a substance that interacts with the functional substance. In addition, labeling a substance that interacts with a specific substance further for the purpose of amplifying or identifying a detected signal with an enzyme or a substance having an electrochemical reaction or a luminescence reaction, a polymer having a charge, a particle, or the like may be used. These methods are widely used as a labeling measurement method in the area of DNA analysis using an immunoassay, an intercalator, or the like.

Although the "interaction" of a specific substance and a detection target substance is not specifically limited, Usually, it is based on the force which acts between the molecule | numerator which arises from at least one of a covalent bond, a hydrophobic bond, a hydrogen bond, a van der Waals bond, and the electrostatic force bond. Action. However, the term "interaction" as used herein is to be interpreted in a broad sense, and in any sense is limited.

Should not be interpreted as Covalent bonds include coordination bonds and dipole bonds. In addition, coupling by electrostatic power includes electric repulsion in addition to electrostatic coupling. Moreover, the coupling | bonding reaction, the synthetic | combination reaction, and the decomposition reaction resulting from the said action are also contained in interaction.

Specific examples of interactions include binding and dissociation between antigen and antibody, binding and dissociation between protein receptor and ligand, binding and dissociation between adhesion molecule and partner molecule, binding and dissociation between enzyme and substrate, binding between apo-enzyme and coenzyme And dissociation, nucleic acids and proteins binding thereto

Binding and dissociation between the nucleic acids and nucleic acids, the binding and dissociation between nucleic acids and nucleic acids, the binding and dissociation between proteins in the information transmission system, the binding and dissociation between glycoproteins and proteins, or the association and dissociation between sugar chains and proteins, cell and biological tissues and proteins The binding and dissociation of the liver, the binding and dissociation between the cells and biological tissues and the small molecule compound, the interaction between the ions and the ion-sensitive substance, and the like, but are not limited to this range. For example, immunoglobulins or derivatives thereof F (ab ') 2, Fab', Fab, receptors or enzymes and derivatives thereof, nucleic acids, natural or artificial peptides, artificial polymers, sugars, lipids, inorganic substances or organic ligands, viruses , Cells, drugs, etc.

The receptors (receptors) is a biological material that binds to the target biomaterial and serves as a probe to detect it, nucleic acids (DNA, RNA, PNA, LNA and hybrids thereof), proteins (enzymes, substrates, antigens, antibodies) , Ligands, aptamers, and the like), viruses, and infectious diseases. Preferably it is characterized in that the protein related to the disease.

According to one embodiment of the present invention, immediately before and after attaching the receptor to the carbon nanotubes, the bonding aid for increasing the adhesion between the carbon nanotubes and the receptor can be treated. The binding aid serves to maintain the bond between the carbon nanotubes and the receptor even after releasing the electric field applied to the carbon nanotubes.

Such binding aids are preferably chemical substances having a functional group such as aldehyde, amine or imine at the end of the carbon group; Monolayers such as SiO 2, Si 3 N 4, and the like; Membranes such as nitrocellulose and the like; Or a polymer such as polyacrylamide gel, PDMS, or the like.

According to an embodiment of the present invention, the hydrophobic material Teflon, PDMS (Polydimethylsiloxane), polymethyl methacrylate (PMMA), silicon dioxide (SiO ₂ ), and silicon nitride are disposed between the source electrode and the detection region, and the drain electrode and the detection region. (Si ₃ N ₄ ), preferably Teflon, to prevent the target biomaterial from contacting the source and drain electrodes.

The field effect transistor of the present invention formed as described above can detect a low concentration of biomaterial of 1 nM or less, as confirmed in the following examples, because of the Schottky barrier effect due to the wider Schottky contact area. Presumably due to the gating effect of the compound. That is, the Schottky barrier having a contact resistance of the contact portion between the CNT between the sock end of the Au layer where the detection target material is to be positioned and the electrode layer of the portion where the electrode is formed and the length of about 1 mm is conventionally used. It is considered that the biomaterial is detected with high sensitivity due to the wider Schottky barrier and chemical gating effect.

The Schottky barrier and the chemical gating effect will be briefly described. The Schottky barrier is a potential barrier of rectifying characteristics at the contact surface between the metal and the semiconductor. The difference with the p-n contact is that the contact voltage is relatively low and the depletion area of the metal is reduced. Not all metal and semiconductor contacts form a Schottky barrier. However, in the present invention, carbon nanotubes have a p-type semiconductor characteristic, and when the carbon nanotubes come into contact with a metal, a Schottky barrier is formed on the contact surface, and a bio-material is detected on the Au island. It is estimated that the Schottky barrier is changed to increase or decrease the electrical signal, with the addition of a chemical gating effect to detect the biomaterial. The Schottky barrier is divided into ohmic contact and rectified contact according to the type of semiconductor and the relative work function difference between the metal and the semiconductor.

① ΦM> ΦS (n-type semiconductor): rectifying contact

② ΦM <ΦS (n-type semiconductor): ohmic contact

③ ΦM> ΦS (p-type semiconductor): ohmic contact

④ ΦM <ΦS (p-type semiconductor): rectifying contact

Chemical gating effect (Chemical gating effect) is used and the like molecule or material that has an electric charge on the surface as a gas or is a simulation method for use in a field-effect field-effect transistor using a chemical substance. For example, when a device made of carbon nanotubes is exposed to NH ₃ , when NH ₃ is adsorbed on the carbon nanotubes and provides electrons, the number of holes, which are existing transporters, is reduced, and at the same time, the household appliances are removed from the Fermi level. Drop, resulting in reduced conductivity. Similarly, in the case of biomolecules, accessing carbon nanotubes with a specific charge on the surface changes the conductivity of carbon nanotubes.

A method of manufacturing a carbon nanotube-field effect transistor according to the present invention is as follows.

Preparing a substrate; Forming an insulating layer on the substrate; Depositing carbon nanotubes on the insulating layer so that the carbon nanotubes are cut off in the middle; Depositing a conductive material to form a source electrode and a drain electrode; Deposition of a detection region to be fixed to the upper portion centered on the middle channel to be fixed to the metal and semiconducting material: and connected to the power source through the conductive nanowires so that charge can be applied respectively It consists of steps.

In another embodiment, the detection region may be formed, and then a teflon may be disposed between the detection region, the source electrode, and the drain electrode to block the target biomaterial to be detected from contacting the source electrode and the drain electrode by using the hydrophobicity of the teflon.

In depositing carbon nanotubes, the carbon nanotubes are deposited in the form of a network or Langmuir-Blodgett film. Carbon nanotubes are formed by chemical vapor deposition (CVD), laser ablation, or arc-discharge, or formed by coating carbon nanotube paste on a substrate. It is deposited using a dielectrophorsis or a filtering method. The carbon nanotubes may be single wall nanotubes, double wall nanotubes, or multiwall nanotubes or bundle nanotubes. The carbon nanotubes may be used in the form of a network structure formed through a filter method or a film having excellent alignment and orientation using the Langmuir-Blozet method.

The part where the middle portion of the carbon nanotube is cut off is formed to be 10-2000 μm, preferably 1000-1500 μm. According to the experiments of the present inventors, it was confirmed that the biosensor of the present invention showed the best sensitivity in the length of this range.

The distance between the source electrode and the detection region and the drain electrode and the detection region is 0.5-2.0 mm to form a wide Schottky contact area. By enlarging the Schottky contact area, it is estimated that the device of the present invention can achieve a high sensitivity detection of biomaterials with a chemical gating effect.

 The deposition of metal on the source and drain electrodes can be carried out by physical vapor deposition (PVD), e-beam evaporation or thermal evaporation, preferably thermal evaporation. evaporation).

The metal used for the electrode is as described above, preferably gold (Au) or titanium (Ti).

Including a receptor capable of specifically binding to and interacting with a detection target material in the detection area of the biosensor having the above characteristics may change the work function of the electrode by interaction, thereby contacting the carbon nanotubes with the detection area. Will change the resistance. The change in contact resistance affects the flow of current, and the detection target material is detected using the change.

The method of fixing the receptor to the detection region may be made of a physical and chemical bond, for example, the thiol of the receptor may be fixed to the detection region composed of gold.

As described above, the biosensor according to the present invention has a wider Schottky contact area, and makes it possible to detect biomaterials of various contents with high sensitivity even at low concentrations of 1 nM or less.

Hereinafter, the present invention will be described in detail with reference to the accompanying drawings. However, the following examples are merely illustrative of the present invention, and the contents of the present invention are not limited to the following examples.

The carbon nanotube-field effect transistor of the present invention was fabricated as follows.

A silicon wafer was prepared for use as a substrate, and a silicon oxide film was deposited thereon to form an insulating layer. Carbon nanotubes were deposited on the insulating layer so that the middle was cut to 1500 mu m. Carbon nanotubes were formed in the form of Langmuir-Blodgett films and single-walled nanotubes were used. Carbon nanotubes were also grown using chemical vapor deposition. Gold was deposited to form source and drain electrodes. Gold was deposited to form a detection area to which the detection target material covering the upper part was centered around the broken carbon nanotubes. At this time, the distance between the gold forming the detection region, the sour electrode and the drain electrode was 1 mm. Finally, each was connected to a power source via conductive nanowires so that charge could be applied.

1 shows a schematic diagram of a biosensor manufactured by an embodiment of the present invention. 1 shows a biomaterial capable of specifically binding to the receptor together with a receptor to be fixed to the detection region. FIG. 2 is a schematic manufacturing schematic diagram of a biosensor of the present invention using single-walled carbon nanotubes as a channel passage on a SiO ₂ / Si substrate, and depositing gold between electrodes and broken carbon nanotubes to which a detection material is immobilized. It is shown. FIG. 3 (a) is an Atomic Force Microscopy (AFM) image of a carbon nanotube connected between an electrode and a gold layer to which a detection material is attached in the device fabricated by FIG. The height of the cross section is shown, and FIG. 3 (b) is an SEM image of network carbon nanotubes. Figure 3 (c) is a SEM image showing that the shape of the carbon nanotubes of the device to be manufactured can be formed in a film form aligned and directed through the Langmuir-Blodge method. 4 is a graph showing that a current flowing in a channel of a device made of a network carbon nanotube manufactured in FIG. 2 according to an embodiment of the present invention changes according to an applied gate voltage, and is a metal-semiconductor of a carbon nanotube field effect transistor. It can be seen that the IV characteristics of.

Referring to the method for detecting the target biomaterial using the biosensor of the present invention manufactured as described above are as follows.

FIG. 5 (a) shows the preparation for measuring the change of current using the biosensor according to the present invention in which the detection region, the source electrode and the drain electrode are blocked using a Teflon cell. Figure 5 (b) is a schematic diagram showing the binding of biotin, a probe substance immobilized on a device protected with bovine serum albumin (Bovineserumalbumin (BSA) protein) and the target protein straptavidin protein to form a specific binding with each other.

In Figure 5 (a) and (b) after installing the Teflon cell in the carbon nanotube-based field effect transistor, while applying a bias voltage (Vds) of 0.1 V between the source and drain electrodes, the phosphate buffer solution (PBS, 10mM, pH = 7.4) and the change in current of the device was measured while filling the different protein solutions.

  FIG. 6 is a graph showing a drop in conductance in real time of a mechanism of interaction of a specific recognition reaction of biotin by avidin through the structure of FIG. 6 (a) shows that there is no change in the electrical signal when applied to the device using bovine serum albumin protein that does not have specific reactivity with the biotin molecule, and (b)-(e) of FIG. When reacted with a strapnavidin protein that forms a specific reaction with biotin at the concentration, the conductance drops even at a concentration of at least 1 pM.

As described above, in order to manufacture a biomaterial detection sensor, a gold layer is present between the source electrode and the drain electrode, and a carbon nanotube having an intermediate cut is formed as a material connecting the channel between the two metal layers. In addition to the wider Schottky contact area, the structure also has a relatively large amount of semiconducting carbon nanotubes, which can be used to improve the Schottky contact area between metal-semiconductor nanotubes, their contact resistance and contact resistance between nanotubes. It can be seen that it is possible to detect a low concentration of bio-materials below 1nM.

Although the preferred embodiment according to the present invention has been described above, this is merely illustrative, and those skilled in the art may understand that other equivalent embodiments are possible therefrom. Therefore, the true technical protection scope of the present invention should be defined by the appended claims.

1 is a schematic view illustrating a carbon nanotube-field effect transistor based biosensor according to an embodiment of the present invention.

2 is a schematic diagram illustrating a method of manufacturing a carbon nanotube field effect transistor based biomaterial detection sensor according to an embodiment of the present invention.

FIG. 3 (a) is an AFM image in which the carbon nanotubes connecting the electrode and the gold layer in which the detection material is to be formed in the device manufactured in FIG. (b) is an SEM image of network carbon nanotubes. Figure 3 (c) is a SEM image showing that the shape of the carbon nanotubes of the device to be manufactured can be formed in the form of an aligned and directed film using the Langmuir-Bjet method.

4 is a graph showing that a current flowing in a carbon nanotube channel of a network structure in a device manufactured according to an embodiment of the present invention changes according to an applied gate voltage.

Figure 5 (a) schematically shows a protein detection method performed according to an embodiment of the present invention using a Teflon cell. FIG. 5 (b) is a schematic diagram showing the binding of the biotin, a probe substance immobilized on a device protected with bovine serum albumin protein, and the strap avidin protein, a target protein to form a specific binding with each other.

FIG. 6 is a graph showing the device's conductance drop for specific recognition reactions by biotin and strapavidin. 6 (a) shows that there is no change in the electrical signal when applied to the device using bovine serum albumin protein that has no specific reactivity with the biotin molecule, and (b) to (e) are specific at various concentrations, respectively. It is a graph showing the drop in conductance even at the lowest concentration of 1 pM when reacting the strap avidin protein forming the reaction.

<Description of the symbols for the main parts of the drawings>

1: substrate (Si) 2: substrate (SiO ₂ )

3: source electrode (Au) 4: drain electrode (Au)

5: carbon nanotube two-dimensional structure

6: Gold in the Biomaterial Detection Zone (Au)

Claims (15)

The substrate, the insulating layer, the source electrode and the drain electrode formed on the insulating layer, the channel of the intermediate shape located between the source electrode and the drain electrode, and the detection target material covering the upper portion centered on the channel disconnected intermediate A carbon nanotube-field effect transistor based biosensor having a detection region to be fixed. The method of claim 1, Hydrophobic materials such as teflon, PDMS (polydimethylsiloxane), polymethyl methacrylate (PMMA), silicon dioxide (SiO ₂ ), and silicon nitride (Si ₃ N ₄ ) are disposed between the source electrode and the detection electrode and the drain electrode and the detection region. Carbon nanotube-field effect transistor based biosensor comprising a. 3. The method of claim 2, Carbon nanotube-field effect transistor based biosensor, characterized in that the hydrophobic material is Teflon. The method according to claim 1 or 2, The carbon nanotubes may be formed by chemical vapor deposition (CVD), laser ablation, arc-discharge, carbon nanotube paste, CNT paste, electrophoresis, or filtering. Carbon nanotube-field effect transistor-based biosensor, characterized in that the film is formed using a network or a Langmuir-Blodgett method using the method). The method according to claim 1 or 2, Carbon nanotube-field effect transistor based biosensor, characterized in that the detection region is a metal or semiconducting material. The method according to claim 1 or 2, The biomaterial is selected from the group consisting of nucleic acids (DNA, RNA, PNA, LNA and hybrids thereof), proteins (enzymes, substrates, antigens, antibodies, ligands, aptamers, etc.), viruses and infectious diseases. Carbon nanotube-field effect transistor based biosensor The method according to claim 1 or 2, A carbon nanotube-field effect transistor-based biosensor, characterized in that the length of the middle of the carbon nanotube is cut off 10-2000㎛. The method according to claim 1 or 2, The detection material is a carbon nanotube-field effect transistor based biosensor, characterized in that the protein related to the disease. The method according to claim 1 or 2, A carbon nanotube-field effect transistor based biosensor, comprising a bonding aid that increases adhesion between the carbon nanotubes and the receptor before and after attaching the receptor to the carbon nanotubes. The method according to claim 1 or 2, A carbon nanotube-field effect transistor based biosensor, characterized in that the distance between the detection region and the source electrode and the detection region and the drain electrode is 0.5-2.0mm apart. Preparing a substrate; Forming an insulating layer on the substrate; Depositing carbon nanotubes on the insulating layer so that the carbon nanotubes are cut off in the middle; Depositing a conductive material to form a source electrode and a drain electrode; Depositing a detection region on which the detection target material, which covers the upper portion of the channel, which is interrupted, to be fixed, is made of metal and semiconducting material; and A method of manufacturing a carbon nanotube-field effect transistor-based biosensor, comprising connecting to a power source through conductive nanowires so that electric charges can be applied to a source electrode and a drain electrode, respectively. The method of claim 11, Hydrophobic materials such as teflon, polydimethylsiloxane (PDMS), polymethyl methacrylate (PMMA), silicon dioxide (SiO ₂ ) and silicon nitride (Si ₃ N ₄ ) are provided between the detection region and the source electrode and the drain electrode to be detected. A method of manufacturing a carbon nanotube-field effect transistor based biosensor, characterized in that the target biomaterial is blocked from contacting the source electrode and the drain electrode. The method of claim 11 or 12, The hydrophobic material is a Teflon carbon nanotubes-field effect transistor based biosensor manufacturing method. The method of claim 11 or 12, The deposition of metal on the source and drain electrodes is based on carbon nanotube-field effect transistors, characterized by physical vapor deposition (PVD), e-beam evaporation or thermal evaporation. Method of manufacturing a biosensor. A method of detecting biomaterials using the biosensor of any one of claims 1 to 10.

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