KR102322684B1 - Bio sensor, method for manufacturing the same, and ion detection method using the same - Google Patents

Abstract

The present invention relates to a biosensor capable of detecting a specific ion or molecule with a high-sensitivity electronic signal by forming a phospholipid bilayer on a field effect transistor including a channel layer and binding a proteomic that passes through the phospholipid bilayer, a method for manufacturing the same, and a method for manufacturing the same It relates to a method for detecting ions using a field effect transistor comprising a channel layer, comprising a phospholipid bilayer formed on the transistor, and at least one proteome penetrating the phospholipid bilayer, wherein the proteome selectively permeates only a specific ion or molecule characterized in that

Description

Biosensor, manufacturing method thereof, and ion detection method using the same

The present invention relates to a biosensor, a method for manufacturing the same, and a method for detecting ions using the same, and more particularly, by forming a phospholipid bilayer on a field effect transistor including a channel layer, and binding a protein penetrating the phospholipid bilayer The present invention relates to a biosensor capable of detecting ions or molecules with high-sensitivity electronic signals, a method for manufacturing the same, and a method for detecting ions using the same.

Since the advent of graphene, the unique mechanical, optical and electrical properties of two-dimensional materials have been attracting attention. Among them, two-dimensional materials composed of a combination of chalcogen metal and transition metal have been studied in various bioelectronics.

Until now, various studies through bioelectronics have detected and quantified on a laboratory scale through chemical reactions using surface treatment on various materials. The downside is that it cannot be used.

In addition, when a biosensor is manufactured by antigen-antibody reaction, there are various causes of noise, a small selection range, and difficulty in detecting a desired signal with high sensitivity.

In order to solve this problem, the production of a platform that can be utilized as a variety of bio-nanoelectronics using a membrane protein and a phospholipid bilayer is required.

One object of the present invention is to form a phospholipid bilayer on a field effect transistor including a channel layer and bind a proteomic that passes through the phospholipid bilayer to detect a specific ion or molecule with a high-sensitivity electronic signal, and manufacturing thereof to provide a way

Another object of the present invention is to provide a method for detecting ions using the sensor.

A biosensor for one purpose of the present invention includes a field effect transistor including a channel layer; a phospholipid bilayer formed on the transistor; and at least one proteome penetrating the phospholipid bilayer.

It is preferred that the proteomic selectively permeate only specific ions or molecules.

The channel layer is preferably containing molybdenum disulfide (MoS _2), the surface of this molybdenum disulfide (MoS ₂₎ may be modified to a hydrophilic treatment is an oxygen plasma.

As another example, an aluminum oxide (Al ₂ O ₃ ) layer may be deposited on _{the surface of the molybdenum disulfide (MoS 2 ).}

On the other hand, the proteome is α-helix, β-sheet structure gramicidin (Gramicidin), alamethicin (Alamethicin), potassium channel (Potassium ion channel), bacteriorhodopsin (Bacteriorhodopsin) containing any one or more selected from Preferably, the ion ^{contains any one or more selected from H +} , Na ⁺ , Ca2 ⁺ , K ⁺ , Cl ^- , and the molecule contains any one or more selected from dopamine and glucose it is preferable

On the other hand, the biosensor manufacturing method for another object of the present invention comprises the steps of manufacturing a field effect transistor including a channel layer; preparing an endoplasmic reticulum using phospholipids; including one or more proteomic bodies in the endoplasmic reticulum; and culturing the endoplasmic reticulum containing the proteomic on the transistor to form a phospholipid bilayer.

In this case, the proteomic may be formed to penetrate the phospholipid bilayer.

In addition, the channel layer preferably includes _{molybdenum disulfide (MoS 2 ).}

And, in the step of manufacturing the transistor, oxygen plasma treatment of the surface of the _{molybdenum disulfide (MoS 2 ) may be further included.}

As another example, in manufacturing the transistor, the method may further include depositing an aluminum oxide (Al ₂ O _{3 ) layer on the surface of the molybdenum disulfide (MoS 2 ).}

Specifically, the manufacturing of the transistor is preferably performed through a photolithography process.

In addition, the proteome includes at least one selected from α-helix, β-sheet structure, gramicidin, alamethicin, potassium ion channel, and bacteriorhodopsin. , can selectively permeate only specific ions or molecules.

On the other hand, in another embodiment of the present invention, there is an ion detection method, which includes the steps of contacting the biosensor with an ion-containing solution; and observing a change in electrical conductivity of the biosensor.

According to the present invention, a phospholipid bilayer is formed on the transistor of the biosensor, and the phospholipid bilayer includes one or more proteomic substances penetrating the phospholipid bilayer, so that the phospholipid bilayer has low permeability to charged ions and large molecules through the proteomic Since only specific ions or molecules are selectively permeated to change the electrical properties of the channel, there is an advantage in that high-sensitivity electronic signals can be obtained with respect to ions or molecules penetrating the proteomic body.

In addition, according to the present invention, when the phospholipid bilayer is formed on the two-dimensional nanostructure, the space between the phospholipid bilayer and the two-dimensional nanostructure is uniformly formed, so that a uniform signal can be obtained, and a high-sensitivity electronic signal can be obtained. have.

Figure 1 is a view showing a biosensor according to an embodiment of the present invention, Figure 2 is a schematic diagram simulating the formation of a phospholipid bilayer and proteomic on the field effect transistor of the present invention.
3 is an image of a _{molybdenum disulfide (MoS 2} ) thin film synthesized on a sapphire substrate.
4 is a view showing the Raman spectrum results of the _{molybdenum disulfide (MoS 2} ) thin film prepared according to an embodiment of the present invention.
5 is a view showing the contact angle measurement results of Examples 1 and 2, which are non-surface-modified molybdenum disulfide (MoS _{2 ) thin films, and surface-modified thin films.}
6 is an image showing the result of forming a fluorescent material-tagged phospholipid bilayer on the surface of a molybdenum disulfide (MoS _{2 ) thin film.}
7 is a view showing the results of observing the recovery process by culturing the endoplasmic reticulum labeled with fluorescence on the surface-modified thin film, and photobleaching a portion where the phospholipid bilayer is formed.
FIG. 8 is a view showing a result of measuring a change in drain current according to a gate voltage using a reference electrode (Ag/AgCl) according to embodiments of the biosensor of the present invention.
9 is a diagram showing the results of measuring the change in current according to pH change after contacting an ion-containing solution with a device without a phospholipid bilayer, a device including a phospholipid bilayer, and a device including a phospholipid bilayer including a proteome am.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. Since the present invention can have various changes and can have various forms, specific embodiments are illustrated in the drawings and described in detail in the text. However, this is not intended to limit the present invention to the specific disclosed form, it should be understood to include all modifications, equivalents and substitutes included in the spirit and scope of the present invention. In describing each figure, like reference numerals have been used for like elements.

The terms used in the present application are used only to describe specific embodiments and are not intended to limit the present invention. The singular expression includes the plural expression unless the context clearly dictates otherwise. In the present application, terms such as “comprise” or “have” are intended to designate that a feature, step, operation, component, part, or combination thereof described in the specification is present, and includes one or more other features or steps. , it should be understood that it does not preclude the possibility of the existence or addition of , operation, components, parts, or combinations thereof.

Unless defined otherwise, all terms used herein, including technical and scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Terms such as those defined in commonly used dictionaries should be interpreted as having a meaning consistent with the meaning in the context of the related art, and should not be interpreted in an ideal or excessively formal meaning unless explicitly defined in the present application. does not

Figure 1 is a view showing a biosensor according to an embodiment of the present invention, Figure 2 is a schematic diagram simulating the formation of a phospholipid bilayer and proteomic on the field effect transistor of the present invention.

1 and 2 , the biosensor of the present invention may include a field effect transistor, a phospholipid bilayer, and a proteomic (shown in FIG. 2 ).

The field effect transistor includes a substrate, a source electrode, a drain electrode, and a gate electrode like a general transistor, and includes a channel layer, and a phospholipid bilayer is formed on the transistor.

Here, the source electrode and the drain electrode may be formed of one or more metals selected from the group consisting of platinum, gold, chromium, copper, aluminum, nickel, palladium, and titanium.

In addition, the channel layer, for example, graphene, graphene oxide, molybdenum disulfide (MoS ₂ ) It is preferable to include a two-dimensional nanostructure, such as, in particular, molybdenum disulfide (MoS ₂ ) It is most preferable to include , but is not limited thereto.

For example, if the channel layer comprises a molybdenum disulfide (MoS _2), molybdenum disulfide (MoS ₂₎ so that the phospholipid bilayer on can be formed, the molybdenum disulfide is treated the oxygen plasma surface (MoS ₂₎ as a hydrophilic It is preferred to be modified.

As another example, the molybdenum disulfide (MoS ₂₎ the surface has a layer of aluminum oxide (Al ₂ O ₃₎ may be deposited on, which causes the modification to the hydrophilic surface of the molybdenum disulfide (MoS ₂₎ the phospholipid bilayer is the channel layer surface can be effectively formed in

Meanwhile, the phospholipid bilayer may be formed on a transistor, specifically, on a channel layer of the transistor.

Also, as shown in FIG. 2 , the phospholipid bilayer may include one or more proteases penetrating the phospholipid bilayer.

At this time, the proteome is α-helix, β-sheet structure gramicidin (Gramicidin), alamethicin (Alamethicin), potassium channel (Potassium ion channel), bacteriorhodopsin (Bacteriorhodopsin) containing any one or more selected from It is preferred, but not limited thereto.

Specifically, the proteomic acts as an ion channel that selectively permeates only a specific ion or molecule, and the ion permeating the proteome includes at least one selected ^{from H +} , Na ⁺ , Ca2 ⁺ , K ⁺ , Cl ^- and the molecule penetrating the proteomic may include any one or more selected from dopamine and glucose.

In the biosensor of the present invention, a phospholipid bilayer is formed on a transistor, and the phospholipid bilayer includes one or more proteomic substances penetrating the phospholipid bilayer. Alternatively, since only molecules are selectively transmitted to change the electrical properties of the channel, there is an advantage in that high-sensitivity electronic signals can be obtained with respect to ions or molecules passing through the proteomic body.

In addition, when the phospholipid bilayer is formed on the two-dimensional nanostructure, the space between the phospholipid bilayer and the two-dimensional nanostructure is uniformly formed, so that a uniform signal can be obtained, and a high-sensitivity electronic signal can be obtained.

On the other hand, the method for manufacturing a biosensor for another object of the present invention comprises the steps of manufacturing a field effect transistor including a channel layer; preparing an endoplasmic reticulum using phospholipids; including one or more proteomic bodies in the endoplasmic reticulum; and forming a phospholipid bilayer by culturing the endoplasmic reticulum containing the proteomic on the transistor, wherein the proteome may be formed to penetrate the phospholipid bilayer.

First, a step of manufacturing a field effect transistor including a channel layer is performed.

Specifically, the step of manufacturing the transistor may be performed by photolithography and electron beam deposition. In this case, the channel layer preferably includes a two-dimensional nanostructure such as graphene, graphene oxide, molybdenum disulfide (MoS ₂ ), and the like, and particularly preferably includes molybdenum disulfide (MoS ₂ ).

For example, in the step of manufacturing the transistor, in order to modify the surface of the channel layer to be hydrophilic, the method may further include treating _{the surface of molybdenum disulfide (MoS 2} ) with oxygen (O _{2 ) plasma.}

Specifically, in the oxygen (O ₂ ) plasma treatment step, particles with high energy collide with the surface of the channel layer to cause defects in the sulfur (S) region with a mass smaller than molybdenum (Mo), and the defect region contains oxygen As it oxidizes in the environment, it exhibits hydrophilicity.

As another example, in the step of manufacturing the transistor, the step of depositing an aluminum oxide (Al ₂ O _{3 ) layer on the surface of the molybdenum disulfide (MoS 2} ) may be further included, which is an atomic layer deposition (ALD, Atomic Layer Deposition). ) can be used to

That is, as the surface of the channel layer is modified to be hydrophilic, the phospholipid bilayer can be successfully formed on the surface of the channel layer.

Next, the step of preparing the endoplasmic reticulum using phospholipids proceeds.

Specifically, DOPC (1,2-dioleoyl-sn-glycero-3-phosphocholine) can be used as the phospholipid, and the mixture is vacuum dried with nitrogen gas for about 1 to 2 hours with nitrogen gas until a thin film is formed, and the dried phospholipid After rehydration in PBS solution, the suspension can be subjected to freeze-thaw to prepare monolayer vesicles.

Then, it can be extruded in a 200-nm polycarbonate filter to prepare vesicles of uniform size.

Next, the step of including one or more proteases in the endoplasmic reticulum proceeds.

Specifically, it is preferable to mix the proteomic in the endoplasmic reticulum suspension in a molar ratio of, for example, 95:1 to 105:1, in which case the proteome is α-helix, β-sheet structure of Gramicidin. , Alamethicin (Alamethicin), potassium channel (Potassium ion channel), may include any one or more selected from bacteriorhodopsin (Bacteriorhodopsin), the protein is preferably a membrane protein that selectively permeates only a specific ion or molecule.

Thereafter, the step of forming a phospholipid bilayer by culturing the endoplasmic reticulum containing the proteomic on the transistor is performed.

At this time, the culture is preferably performed for about 2 to 3 hours at room temperature, and the endoplasmic reticulum is _{ruptured on the surface of the molybdenum disulfide (MoS 2} ) thin film, and is converted into a planar phospholipid bilayer through self-assembly.

In addition, the proteome is formed to penetrate the converted phospholipid bilayer, thereby serving as a channel for selective ion detection.

As shown in FIG. 2, the biosensor of the present invention has a proteomic channel inserted in the phospholipid bilayer, so it is possible to detect a proton signal and selectively permeate only a specific ion or molecule through passive transport of the proteome. An electrical change is detected by transmission. Therefore, the biosensor of the present invention can be used as a bioelectronic platform for selective ion detection.

That is, another aspect of the present invention may include an ion detection method, which includes contacting the biosensor with an ion-containing solution; and observing a change in electrical conductivity of the biosensor.

The ion is preferably an ion capable of penetrating the proteome, and by selectively permeating a specific ion through passive transport of the proteome and observing the change in electrical conductivity, there is an advantage in that it can be detected with high sensitivity for a specific ion.

Hereinafter, various embodiments and experimental examples of the present invention will be described in detail. However, the following examples are only some examples of the present invention, and the present invention should not be construed as being limited to the following examples.

Molybdenum disulfide (MoS) ₂ ) thin film production

A sapphire substrate having a size of 10.5 mm × 10.5 mm, molybdenum (VI) oxide (MoO ₃ ) and sulfur (S) powder were prepared. A quartz boat containing 2 mg of molybdenum (VI) oxide (MoO ₃ ) and a sapphire substrate was placed in the center of the furnace of the CVD system, and 30 mg of sulfur (S) powder was placed at the edge of the furnace near the gas outlet. The furnace was heated to a temperature of 300° C. into the sample chamber under argon (Ar) gas flowing at a flow rate of 200 sccm, and maintained for about 10 minutes.

Next, the furnace was heated to a temperature of 700 ℃ under argon (Ar) gas flowing at a flow rate of 20 sccm, molybdenum disulfide (MoS ₂ ) was maintained for about 10 minutes for the growth of the thin film. Thereafter, the CVD system was rapidly cooled at room temperature to prepare a molybdenum disulfide (MoS ₂ ) thin film (see FIG. 3 ).

_{The characteristics of the prepared molybdenum disulfide (MoS 2} ) thin film were confirmed through the Raman spectrum, and the results are shown in FIG. 4 .

4, in the case of the molybdenum disulfide (MoS ₂ ) thin film, two prominent peaks (E ¹ _{2 g} peak and A _{1 g} peak) appeared, and the E ¹ _{2 g} peak (383.1 cm ^-1 ) is Mo and S atoms Means horizontal vibration between, and A _1g peak (408.1 cm ^-1 ) means vertical vibration between Mo and S atoms. Molybdenum disulfide (MoS ₂ ) thin film produced as these two peaks are confirmed (MoS ₂ ) It was found that it was synthesized with high quality while maintaining the structure.

Molybdenum disulfide (MoS) ₂ ) surface modification for thin films

Example 1: Oxygen (O ₂ ) plasma treatment

In order to modify the surface of the molybdenum disulfide (MoS ₂ ) thin film from hydrophobicity to hydrophilicity, using an inductively coupled plasma (ICP) mode (SBTEK), the surface of the _{molybdenum disulfide (MoS 2} ) thin film was treated with _{oxygen (O 2 ) plasma.} , specifically, molybdenum disulfide (MoS ₂₎ power the film 60W, and oxygen (O ₂₎ gas flow rate of 30 sccm surface-modified molybdenum disulfide to the plasma treatment for 5 seconds under the conditions (MoS _2), to obtain a thin film (example 1).

Example 2: Aluminum oxide (Al ₂ O ₃ ) deposition

Atomic layer deposition (ALD, Atomic Layer Deposition) of 30nm of aluminum oxide having a thickness of using (Al ₂ O ₃₎ dielectric layer, molybdenum disulfide (MoS ₂₎ was deposited on the surface of the thin film surface-modified molybdenum disulfide (MoS ₂₎ thin film (Example 2) was obtained.

In order to confirm the surface energy of Examples 1 and 2 prepared above, using a Droplet Analyzer (SDL200TEDZD), ~1 μl of deionized water was dropped on the surface of Examples 1 and 2 to measure the contact angle. The contact angle measurement was performed under the conditions of room temperature and relative humidity of 5-6%.

5 is a view showing the contact angle measurement results of Examples 1 and 2, which are non-surface-modified molybdenum disulfide (MoS _{2 ) thin films, and surface-modified thin films.}

As shown in FIG. 5, in the case of the non-surface-modified molybdenum disulfide (MoS ₂ ) thin film, the contact angle was measured to be about 89° and the surface had a property close to hydrophobicity, but in Examples 1 and 2 in which the surface was modified case, measured at 51° and 57.6°, respectively, confirming that the surface was changed from hydrophobicity to hydrophilicity.

Surface-modified molybdenum disulfide (MoS) ₂ ) Thin film and phospholipid composite structure

DOPC (1,2-dioleoyl-sn-glycero-3-phosphocholine) and the fluorescent substance Rho-PE (1,2-dioleoyl-sn-glycero-3-phosphoethanolamine-N-(lissamine rhodamine B sulfonyl) ammonium salt) A solution containing chloroform was prepared (Ananti Polar Lipids). DOPC was mixed with Rho-PE at a concentration of 0.01% in a glass vial, and the mixture was vacuum dried with nitrogen gas for about 1 hour until a thin film was formed. The dried phospholipids were rehydrated at a concentration of 1 mg/1 mL in a 10 mM phosphate-buffered saline (PBS) solution. Thereafter, the suspension was subjected to a freeze-thaw method to prepare a fluorescently tagged monolayer ER, and then extruded through a 200-nm polycarbonate filter to obtain ERs of uniform size.

Next, in order to form a molybdenum disulfide (MoS ₂ ) thin film and a phospholipid complex structure, the surface-modified molybdenum disulfide (MoS ₂ ) thin film, Examples 1 and 2, was cultured in vesicle suspension at room temperature for about 3 hours.

As a result, the endoplasmic reticulum _{ruptured on the surface of the molybdenum disulfide (MoS 2} ) thin film and converted into a planar phospholipid bilayer through self-assembly.

6 is an image showing the result of forming a fluorescent material-tagged phospholipid bilayer on the surface of a molybdenum disulfide (MoS _{2 ) thin film.}

Referring to FIG. 6 , in the case of the non-surface-modified molybdenum disulfide (MoS ₂ ) thin film, a phospholipid bilayer was not formed on the surface, so that no fluorescent portion was found, and in Examples 1 and 2, phospholipids along the surface of the thin film It was confirmed that the double layer was formed and the fluorescent part was clearly displayed.

Therefore, in the case of the surface-modified Examples 1 and 2, it _{is considered that the phospholipid and molybdenum disulfide (MoS 2} ) thin film composite structure was stably formed.

In addition, in order to confirm the fluidity and uniformity of the phospholipid molecules, the recovery process was observed by culturing the endoplasmic reticulum labeled with fluorescence on the surface of Examples 1 and 2, and photobleaching a portion where the phospholipid bilayer was formed. 7 is shown.

As shown in Fig. 7a, the photobleached portion of the phospholipid bilayer exhibited a fluorescence intensity of 50 - 80% within 240 seconds, confirming that the phospholipid was recovered.

In particular, referring to FIG. 7b showing the fluorescence intensity at the independent photobleaching sites of Examples 1 and 2, the fluorescence intensity at the photobleaching site of both films was recovered in 7 to 13 minutes.

That is, it is judged that the phospholipid bilayer exhibits high mobility, and the in-plane phospholipid molecular diffusion coefficient of the sample using Example 1 measured by the FRAP test was 1.53 μm ² /s within a 10% error range, and Example 2 was The diffusion coefficient of the sample used was measured to be ^{3.75 μm 2 /s.}

That is, it was found that the phospholipid molecules had excellent fluidity and uniformity on the surfaces of Examples 1 and 2.

biosensor manufacturing

_{A field effect transistor including a molybdenum disulfide (MoS 2} ) thin film as a channel layer was manufactured by using photolithography and electron beam deposition using 5 nm thick chromium and 50 nm thick silver electrodes.

Thereafter, in order to change the surface energy of the channel layer, after oxygen (O ₂ ) plasma treatment, the endoplasmic reticulum was cultured on the transistor to form a phospholipid bilayer to prepare a biosensor (FIG. 8 (a)).

_{As another example, after depositing an aluminum oxide (Al 2} O ₃ ) layer on the surface of the channel layer of the prepared field effect transistor, the endoplasmic reticulum is cultured on the transistor to form a phospholipid bilayer to form a biosensor (FIG. 8 (b) ) was prepared.

Thereafter, the drain current according to the gate voltage was measured using a reference electrode (Ag/AgCl) in water, and the results are shown in FIG. 8 .

As shown in FIG. 8 , in the case of the device including the phospholipid bilayer of the present invention (w lipid), the shape of the curve was similar to that of the device without the phospholipid bilayer (w/o lipid), but when the gate voltage was increased It can be seen that the drain current of , shows a relatively reduced value.

Preparation of biosensors containing proteomic

Gramicidin A (Sigma-Aldrich), a protein, is mixed in the ER suspension obtained above in a molar ratio of 100: 1, and the surface-modified molybdenum disulfide (MoS ₂ ) proteomic on a field effect transistor including the thin film as a channel layer. A phospholipid bilayer was formed by culturing the endoplasmic reticulum containing the endoplasmic reticulum to prepare a biosensor containing one or more proteomic bodies penetrating the phospholipid bilayer (see FIG. 2).

Ion detection characteristics of biosensors

After bringing an ion-containing solution into contact with a device not containing a phospholipid bilayer, a device containing a phospholipid bilayer, or a device containing a phospholipid bilayer containing a proteomic (blue line), the current change according to the pH change was measured and the results were reported. It is shown in Figure 9.

Referring to FIG. 9 , it can be seen that in the device in which the phospholipid bilayer was not formed (black line), the current changed greatly according to the change in pH, but after the phospholipid bilayer was formed (red line), the change in current according to the pH was very weak. could

Thereafter, when the proteomic channel was inserted into the phospholipid bilayer (blue line), it was confirmed that the ions passed through and the current changed according to the change in pH.

That is, by inserting a proteomic channel into the phospholipid bilayer, a proton signal can be detected and only specific ions can be selectively permeated through passive transport of the proteome, and an electrical change is detected by the permeation of these ions. Therefore, it is determined that the biosensor of the present invention can be used as a bioelectronic platform for selective ion detection.

Although the above has been described with reference to the preferred embodiments of the present invention, those skilled in the art can variously modify and change the present invention without departing from the spirit and scope of the present invention as set forth in the following claims. You will understand that you can.

Claims (13)

Molybdenum disulfide (MoS ₂ ) A field effect transistor comprising a channel layer deposited on the surface of the aluminum oxide (Al ₂ O _{3 ) layer;}
a phospholipid bilayer formed on the transistor; and
At least one proteome penetrating the phospholipid bilayer;
The proteomic will selectively permeate only a specific ion or molecule, the biosensor.
delete delete delete According to claim 1,
The proteomic is characterized in that it contains any one or more selected from α-helix, β-sheet structure, gramicidin, alamethicin, potassium ion channel, and bacteriorhodopsin. to the biosensor.
According to claim 1,
The ions include any one or more selected ^{from H +} , Na ⁺ , Ca ²⁺ , K ⁺ , Cl ^-,
The molecule is dopamine (Dopamine), glucose (Glucose), characterized in that it comprises any one or more selected from the biosensor.
Manufacturing a field effect transistor including a channel layer containing molybdenum disulfide (MoS _{2 );}
Depositing an aluminum oxide (Al ₂ O ₃ ) layer on the surface of the molybdenum disulfide (MoS _{2 );}
preparing an endoplasmic reticulum using phospholipids;
including one or more proteomic bodies in the endoplasmic reticulum; and
Forming a phospholipid bilayer by culturing the endoplasmic reticulum containing the proteomic on the transistor;
The proteome is formed to penetrate the phospholipid bilayer, the biosensor manufacturing method.
delete delete delete 8. The method of claim 7,
The manufacturing of the transistor is a biosensor manufacturing method, characterized in that performed through a photolithography process.
8. The method of claim 7,
The proteomic includes at least one selected from α-helix, β-sheet structure gramicidin, alamethicin, potassium ion channel, and bacteriorhodopsin (Bacteriorhodopsin),
A method for manufacturing a biosensor, characterized in that only a specific ion or molecule is selectively permeated.
[Claim 7] Contacting the biosensor according to any one of claims 1 to 6 with an ion-containing solution; and
Containing, ion detection method; observing a change in the electrical conductivity of the biosensor.

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