Patent Application
20200070403
This application claims the benefit of Korean Patent Application No. 10-2018-0103035, filed on Aug. 30, 2018, in the Korean Intellectual Property Office, the disclosure of which is incorporated herein in its entirety by reference.
This application includes a sequence listing submitted as an ASCII text file named 8F45696.TXT created Nov. 4, 2019 and of size 16 kB, which is incorporated by reference herein.
One or more embodiments relate to a method of producing a device including nanoparticles.
With the advent of the era of Internet of Things in which objects are interconnected with other objects or people, the role of wearable devices has been further emphasized. Accordingly, there has recently been a rapid increase in the demand for technology for flexible and high-performance materials and devices. To achieve such purposes, research has been conducted on various flexible and high-performance nanoparticle materials such as carbon nanotubes, graphene, and metal nanowires. Because these materials have very small forms on a nanoscale, there is a need to develop efficient manufacturing processes capable of precisely manufacturing devices in sizes of micrometers, millimeters, and centimeters for actual application of these materials to the devices.
Among various device manufacturing processes, particularly coating processes or printing processes such as screen printing and inkjet printing, solution processes enable mass production, allow various materials to be stacked, significantly decrease the number of processes, and reduce manufacturing costs by eliminating the waste of raw materials. Due to these properties, coating processes or printing processes have received attention as manufacturing processes for next-generation wearable devices.
However, nanoparticle materials such as carbon nanotubes, graphene, and metal nanowires exhibit low dispersion stability in water-based inks, and thus many problems arise in manufacturing of devices by printing. To improve dispersion stability, a method of applying a functional group to a nanomaterial by chemical treatment to produce a single-walled carbon nanotube ink has been reported. When a functional group is applied to carbon nanotubes by chemical treatment, the structure of the carbon nanotubes is deformed, thereby deteriorating the original electrical and electrochemical characteristics of the nanotubes.
Thus, in fields where electrical and electrochemical characteristics are important, a widely used method is the dispersal of nanoparticle materials such as carbon nanotubes or metal nanowires in water using a surfactant, to prepare a colloidal composition which is used as an ink. Examples of the surfactant may include sodium cholate, sodium dodecyl sulfate, and the like. Although surfactants are required to prepare colloidal solutions, they may act as foreign substances that interfere with the action of a device such as an electrode manufactured using a surfactant. For example, a surfactant present between printed carbon nanotubes may deteriorate electrical characteristics of a thin film and may partially dissolve and flow out when brought into contact with water again. Thus, washing with water (washing process) or chemical post processing such as acid-treatment has been used to remove surfactants included in nanoparticle materials. However, according to the above-described processes, printed carbon nanotubes may partially dissolve and flow out, the structure of the carbonaceous materials may be deformed, or the substrate may be damaged, and there may be problems wherein the device does not achieve desired performance or application thereof is limited.
Meanwhile, carbonaceous nanoparticle materials such as carbon nanotubes and graphene are more likely to be used as device materials for manufacturing biosensors since they have a superior ability to bind to phages or antibodies than metal nanoparticle materials. The present inventors have disclosed methods of manufacturing biosensors using a graphitic material, which is a carbonaceous nanomaterial, in Korean Patent No. 1694942, entitled “Biosensor and wearable device for detecting information of living bodies comprising hybrid electronic sheets” and Korean Patent Application No. 2016-0150329, entitled “enzyme film and biosensor having high sensitivity and specificity comprising the same”. In this disclosure, reported is a method of manufacturing a nanomaterial film by hydrodynamic immobilization via dialysis using a membrane. In this case, a colloidal material is also prepared by adding a graphitic material to a solution including a surfactant and stabilizing the same. Although an enzyme-integrated film may be realized by applying a hydrodynamic process to the entire structure of an enzyme and an electrode instead of using a conventional stacking method, there are problems in that the processing time in terms of days is long, and technical difficulties in mass production via automation of all or part of the manufacturing process.
One or more embodiments include a method of producing a nanoparticle device including: printing a colloidal composition on a hydrogel in a pattern, the colloidal composition including nanoparticles and a surfactant; and forming a nanoparticle device by removing the surfactant included in the colloidal composition through pores inside the hydrogel, and a nanoparticle device produced according to the production method.
Additional aspects will be set forth in part in the description which follows and, in part, will be apparent from the description, or may be learned by practice of the presented embodiments of the disclosure.
According to one or more embodiments, a method of producing a nanoparticle device includes: printing a colloidal composition including nanoparticles and a surfactant on a hydrogel in a pattern; and forming a nanoparticle device by removing the surfactant included in the colloidal composition through pores inside the hydrogel without damaging the printed pattern, and a nanoparticle device is produced according to the production method. According to one or more embodiments, a method of printing an electrode device includes the above-described operations.
In the printing of the colloidal composition on the hydrogel in the pattern, the colloidal composition may refer to an aqueous solution in which nanoparticles are dispersed or dissolved. The colloidal composition may be prepared by adding the nanoparticles to a solution including a surfactant and stabilizing the same due to a low dispersibility of the nanoparticles therein.
As used herein, the term “colloidal composition” refers to a composition directly printed, in a liquid phase, on a hydrogel to form a pattern and used in an inkjet printing process. Throughout the specification, the term “printing” may refer to printing using an inkjet printer, stencil printing, or the like. In an example embodiment, the colloidal composition may be mounted on an inkjet printer and printed on a hydrogel through a nozzle, or the like, of the printer. In an example embodiment, the colloidal composition including the nanoparticles and the surfactant is distinguished from that laminated on a substrate in the form of a sheet or film by a method such as lithography.
According to an example embodiment, the colloidal composition may be printed on the hydrogel, e.g., printed on the hydrogel by inkjet printing, transferred to the substrate, and dried, to form a device. Also, for example, the device may be a flexible electrode device, a transparent electrode device, a biosensor device, a strain sensor device, a pressure sensor device, a memory device, a logic device, an energy device, or an electrochemical device.
Also, the surfactant may include a bio-compatible surfactant compatible with a biomaterial such as a peptide or a phage. Examples of the surfactant may include sodium cholate (SC), sodium dodecyl sulfate (SDS), sodium deoxycholate (DOC), Nonidet P-40, Triton X-100, Tween 20®, polyethylene glycol (PEG) 600, sodium lauryl sulfate (SLS), ammonium-oleate, cetyltrimethyl ammonium bromide (CTAB), hydrolyzed tetraethyl orthosilicate (TEOS), or any mixture thereof.
As used herein, the term “nanoparticle” refers to a particle, at least one dimension of which is 100 nm or less, i.e., a particle having 1/ten million meters in size, belonging to nanotechnology used to manufacture a novel structure, material, machine, or device via manipulation of matter on an atomic and molecular scale and study a structure thereof. For example, the nanoparticles may be: graphitic materials such as graphene, highly oriented pyrolytic graphite (HOPG), graphene oxide, reduced graphene oxide, single-walled carbon nanotubes, double-walled carbon nanotubes, multi-walled carbon nanotubes, and fullerene; metallic nanoparticles such as metal nanowires, silver nanoparticles, platinum nanoparticles, gold nanoparticles, metal nanobeads, and magnetic nanoparticles; oxide nanoparticles such as silicon oxide, tungsten oxide, zinc oxide, neodymium oxide, titanium oxide, cerium oxide, and iron oxide; a nitride nanoparticle such as boron nitride and titanium nitride; a sulfide nanoparticle such as molybdenum disulfide (MoS2) and tungsten disulfide (WS2), or any mixture thereof. The metal of the metal nanobeads may be Au, Ag, Pt, Pd, Ir, Rh, Ru, Al, Cu, Te, Bi, Pb, Fe, Ce, Mo, Nb, W, Sb, Sn, V, Mn, Ni, Co, Zn, La, Ce, Y, Ti, Sc, Lu, Yb, Tm, Er, Ho, Dy, Tb, Gd, Eu, Sm, Pm, Nd, or Ce.
Meanwhile, as used herein, the term “graphitic material” refers to a material having a surface in which carbon atoms are arranged in a hexagon structure, i.e., a graphene surface, and any material having a graphitic surface may be regarded as the graphitic material regardless of physical, chemical, or structural properties. For example, the graphitic materials may include graphene sheets, HOPG sheets, carbon nanotubes such as single-walled carbon nanotubes, double-walled carbon nanotubes, and multi-walled carbon nanotubes, or fullerene. The graphitic materials may be metallic, semiconductor, or hybrid materials, e.g., a mixture of graphene sheets and single-walled carbon nanotubes.
As used herein, the term “hydrogel”, also referred to as hydrated gel, and having a network structure in which water-soluble polymers are three-dimensionally cross-linked via physical bonds (hydrogen bonds, van der Waals forces, hydrophobic interactions, or polymer crystals) or chemical bonds (covalent bonds), means a material that is not dissolved in an aqueous environment and contains a large amount of water due to pores formed therein. The hydrogel made from various water-soluble polymers may have various chemical compositions and physical properties. Also, the hydrogel may be easily processed and modified into various forms according to application. The hydrogel available in an example embodiment may be, for example, agarose gel, collagen, silicone, dextran, methylcellulose, hyaluronic acid, polyethylene oxide, polyvinyl pyrrolidone, polyvinyl alcohol, sodium polyacrylate, polyethylene glycol, acrylate polymer, acrylamide polymer, methacrylate polymer, or any mixture thereof. More particularly, the hydrogel may be 0.1 wt % to 50 wt %, 0.1 wt % to 10 wt %, 0.1 wt % to 5 wt %, 0.5 wt % to 20 wt %, 0.5 wt % to 10 wt %, 1 wt % to 10 wt %, 2 wt % to 30 wt %, 2 wt % to 10 wt %, or 2 wt % to 5 wt % agarose gel. A hydrogel available in another example embodiment may have a tensile strength, as a mechanical strength, of 20 kPa to 1000 kPa, 10 kPa to 800 kPa, 50 kPa to 300 kPa, or 100 kPa to 500 kPa.
In an example embodiment, the pores inside the hydrogel may have a diameter of 1 nm to 10 μm. More particularly, the diameter of the pores may be 1 nm to 10 μm, 10 nm to 10 μm, 100 nm to 10 μm, 500 nm to 10 μm, 1 μm to 10 μm, 200 nm to 5 μm, 500 nm to 5 μm, 200 nm to 1 μm, or 500 nm to 2 μm. That is, the diameter of the pore may be smaller than that of the nanoparticle and greater than a molecule of the surfactant. Thus, the surfactant may be diffused into water through the pores inside the hydrogel and the nanoparticles may form the nanoparticle device without damaging the printed pattern.
According to one or more embodiments, a composition for removing a surfactant dispersed in a nanoparticle aqueous solution, the composition including a hydrogel having pores with a diameter of 1 nm to 10 μm. The hydrogel included in the composition is used to prepare the nanoparticle device by removing the surfactant through the pores inside the hydrogel without damaging the pattern after printing the colloidal composition including the nanoparticle and the surfactant on the hydrogel in the pattern.
In an example embodiment, the colloidal composition may further include a peptide having the ability to bind to a carbonaceous material or a phage displaying a peptide having the ability to bind to a carbonaceous material. More particularly, the colloidal composition may include a solution containing the peptide or the phage displaying the peptide and a colloidal solution including the nanoparticle. In addition, the solution containing the peptide or the phage displaying the peptide may be a solution in which the peptide or the phage is dispersed. For example, the solution in which the phage is dispersed may include the phage at a concentration of 1×1010 number/ml to 1×1015 number/ml. The solution in which the peptide is dispersed may include the peptide at a concentration of 0.2 mg/ml to 4 mg/ml. Also, the colloidal solution may be a solution including carbon nanotubes (e.g., single-walled carbon nanotubes) at a concentration of 1×1010 number/ml to 1×1015 number/ml. The solution in which the peptide or the phage is dispersed may be mixed with the colloidal solution, in a volume ratio of, for example, 1:8 to 8:1. More particularly, the nanoparticle and the phage may be mixed in a molar ratio of 20:1 to 1:20.
By using the nanoparticles of the device according to an example embodiment, a binding affinity between the carbonaceous materials, as the nanoparticles, or a binding affinity between the nanoparticles and the substrate may be enhanced. More particularly, the peptide or the phage promotes binding between the nanoparticles, contributing to structurization/stabilization of the nanoparticles. This is a concept distinguished from functionalization of the graphitic material may indicate enabling formation of a network structure of the graphitic material. The nanoparticle may improve stability, particularly, in an aqueous solution, compared with a case in which the peptide or the phage displaying the peptide is not used.
Therefore, in an example embodiment, the peptide or the phage binding to the nanoparticle may serve as a binder composition or a bio-adhesive. Throughout the specification, the term “bio-adhesive” or “binder composition” may mean that the peptide or phage promoting binding between nanoparticles, e.g., the graphitic materials, or contributing adhesion properties between the graphitic material and the substrate. More particularly, because the phages displaying the peptide and having the ability to bind to the carbonaceous material specifically binds to the carbonaceous material, the phages may be introduced into interfaces between the elements of an energy device or an electrochemical device to improve adhesive properties or interfacial properties. For example, when the composition is introduced between a current collector and an active material of an energy device, the active material is adhered with a stronger force to the current collector, thereby increasing a thickness of the active material. Also, for example, when the composition is introduced into an active material of an energy device, interface separation of the active material may be prevented. Thus, the colloidal composition further including the peptide or the phage according to an example embodiment may improve adhesive properties between a current collector and an active material or between an active material and a separator of an electrochemical device or improve interfacial properties of the active material. Accordingly, the colloidal composition further including the peptide or the phage may be used for an electrode, a flexible device, an energy device, or an electrochemical device. Examples of the energy device may include a flexible battery, an alkaline battery, a dry battery, a mercury cell, a lithium battery, a nickel-cadmium battery, a nickel-hydrogen battery, and a secondary battery such as a lithium-ion secondary battery or a lithium-ion polymer secondary battery.
In another example embodiment, because the carbonaceous material or the graphitic material is not charged, additional functionalization is required to attach an enzyme for a biosensor or the like thereto. However, the peptide or the phage with the ability to bind to the carbonaceous material or the graphitic material is charged, an enzyme may be integrally bound into the network structure of the carbonaceous material or the graphitic material by electrolyte coating or the like. Thus, the phage or peptide may form junctions of a plurality of carbonaceous materials or graphitic materials. Also, the peptide may be formed of two peptides linked via a linker and link two carbonaceous materials or graphitic materials. More particularly, in a network structure of a plurality of graphitic materials, each of the two peptides linked via the linker may bind to each of the graphitic materials. The linker may be a peptide linker. The peptide linker may be one of various linkers known in the art, for example, a linker including a plurality of amino acids. According to an example embodiment, the linker may be a polypeptide including, e.g., 1 to 10 amino acids or 2 to 8 amino acids. The peptide linker may include Gly, Asn, and Ser residues, and may also include neutral amino acids such as Thr and Ala. Appropriate amino acid sequences for the peptide linker are well known in the art.
The peptide may be any peptide having the ability to bind to a graphitic material, e.g., a carbonaceous material. For example, the peptide according to the present disclosure may have an amino acid sequence selected from SEQ ID NOS: 1 to 12. The peptide may include a conservative substitution of the disclosed peptide. As used herein, the term “conservative substitution” refers to a substitution of a first amino acid residue with a second different amino acid residue. In this regard, the first and second amino acid residues refer to those having side chains with similar biophysical properties. The similar biophysical properties may include the ability to provide or accept hydrophobicity, charge, polarity, or hydrogen bond. Examples of the conservative substitution may include basic amino acids (arginine, lysine, and histidine), acidic amino acids (glutamic acid and aspartic acid), polar amino acids (glutamine and asparagine), hydrophobic amino acids (leucine, isoleucine, valine, and methionine), hydrophilic amino acids (aspartic acid, glutamic acid, asparagine, and glutamine), aromatic amino acid (phenylalanine, tryptophan, tyrosine, and histidine), and small amino acids (glycine, alanine, serine, and threonine). General amino acid substitutions that do not alter specific activity are known in the art. Thus, in the peptide, for example, X1 may be W, Y, F, or H, X2 may be D, E, N, or Q, and X3 may be I, L, or V. Also, the peptide may be a peptide or a peptide set including at least one amino acid sequence selected from SEQ ID NOS: 5 to 11. Besides, the peptide may be a peptide that is not derived from the phage, e.g., a peptide having an amino acid sequence of SEQ ID NO: 12. The peptide may be a peptide formed of two peptides linked via a linker (e.g., SEQ ID NO: 10 or SEQ ID NO: 11). The peptide may further include a partial sequence of a coat protein of the phage, for example, 1 to 10 amino acid residues (e.g., SEQ ID NO: 9). A continuous amino acid sequence of the coat protein of the phage may be linked to an N-terminal or a C-terminal of an amino acid sequence of the peptide or peptide set. Thus, for example, the peptide or peptide set may have a sequence length of 5 to 60 amino acids, 7 to 55 amino acids, 7 to 40 amino acids, 7 to 30 amino acids, 7 to 20 amino acids, or 7 to 10 amino acids. The peptide or peptide set may be an assembled, (e.g., self-assembled) peptide or peptide set. For example, the peptide or peptide set may have an α-helix structure or a β-sheet structure. The peptide or peptide set may improve binding between the graphitic materials such that the graphitic materials have a mesh structure.
The peptide binding to the graphitic material may be selected from peptide libraries by a phage display method. By the phage display method, the peptide may be genetically linked to, is inserted into, or replaces the coat protein of the phage to be displayed on the surface of the phage and the peptide may be encoded by genetic information in a virion. The peptide may be selected by screening the displayed protein and various variants produced by DNA encoding the peptide, which is called “biopanning”. In summary, a biopanning technique includes reacting phages displaying various variants with an immobilized target (e.g., a graphitic material), washing unbound phages, and eluting phages specifically binding to the target by destroying binding interactions between the phages and the target. After a portion of the eluted phages may be left for DNA sequencing and peptide identification, the remainder may be amplified in vivo and a sub-library for the next round may be generated to repeat this process.
Also, the peptide may be displayed on the coat protein of the phage. Thus, for example, the phage having the ability to bind to the graphitic material may include the peptide displayed on the coat protein of the phage or a fragment thereof.
The terms “phage” and “bacteriophage” are used interchangeably and may refer to a virus that infects bacteria and replicates in bacteria. The phage or bacteriophage may be used to display a peptide selectively or specifically binding to a graphitic material or a volatile organic compound. The phage may be genetically engineered to display the peptide having the ability to bind to the graphitic material on the coat protein of the phage or a fragment thereof. As used herein, the term “genetic engineering” or “genetically engineered” refers to introducing at least one genetic modification into the phage to display the peptide having the ability to bind to the graphitic material on the coat protein of the phage or a fragment thereof, or a phage manufactured thereby. The genetic modification includes introducing a foreign gene encoding the peptide. In addition, the phage may be filamentous phage, e.g., M13 phage, F1 phage, Fd phage, If1 phage, Ike phage, Zj/Z phage, Ff phage, Xf phage, Pf1 phage, or Pf3 phage.
As used herein, the term “phage display” refers to displaying a functional foreign peptide or a protein on the surface of phage or phagemid particles. The surface of the phage may refer to the coat protein of the phage or a fragment thereof. In addition, the phage may be a phage prepared by linking the C-terminal of the functional foreign peptide to the N-terminal of the coat protein of the phage, inserting the peptide into a continuous amino acid sequence of the coat protein of the phage, or substituting a portion of the continuous amino acid sequence of the coat protein with the peptide. The insertion or substitution of the peptide may take place at an amino acid position of 1st to 50th, 1st to 40th, 1st to 30th, 1st to 20th, 1st to 10th, 2nd to 8th, 2nd to 4th, 2nd to 3rd, 3rd to 4th, or 2nd from the N-terminal of the coat protein in the amino acid sequence of the coat protein. Also, the coat protein may be p3, p6, p8, or p9. In an example embodiment, the phage may be M13 phage genetically engineered to have the ability to bind to the nanoparticle, the M13 phage may be a phage displaying a peptide having at least one amino acid sequence selected from SEQ ID NO: 1 and SEQ ID NO: 9, and the peptide may be displayed on the coat protein P3, P6, P7, P8 or P9 of the M13 phage.
In another example embodiment, the graphitic material may have a network structure, and the enzyme may be located on the network structure, in the network structure, and/or below the network structure. In addition, the network structure may be formed by a bound complex of the graphitic material and the peptide or a bound complex of the graphitic material and the phage. Thus, the internal structure of the graphitic material may be a percolated network structure. As used herein, the term “percolated network” may refer to a lattice structure formed of random conductive or non-conductive connections.
In the printing of the colloidal composition on the hydrogel in the pattern, the pattern may be any pattern designed for a desired purpose, e.g., a pattern for an electrode including a line pattern, a pattern for a strain sensor, a pattern for a pressure sensor, a pattern for a biosensor, a pattern for a memory, a pattern for a logic device, a pattern for an energy device, a pattern for an electrochemical device, a film, a sheet, or a 3D pattern. As used herein, the term “3D pattern” refers to the pattern for an electrode, the pattern for a strain sensor, the pattern for a pressure sensor, the pattern for a biosensor, the pattern for a memory, the pattern for a logic device, the pattern for an energy device, the pattern for an electrochemical device, the film, the sheet, or the like formed on the surface of or inside a 3D structure. In an example embodiment, formation of the 3D pattern may be freely adjusted according to an easily adjustable shape of the hydrogel. It is easy to form a pattern on a 3D surface due to characteristics of the colloidal composition and the printing method.
In addition, the printing of the colloidal composition in the pattern may be performed by repeating the printing twice or 20 times, i.e., multi-stacking the same colloidal composition or different colloidal compositions. The printing may be performed in different directions, the colloidal compositions of the respective layers may be different, and the patterns of the respective layers may also be different. By changing the direction of printing, performance of the device may vary. More particularly, a multilayered structure may be formed by repeating the printing twice to 10 times, 4 times to 10 times, or 4 times to 6 times. The repeating of the printing to a multilayered structure is referred to as “multi-stacking” throughout the specification. The multi-stacking enables molding in various shapes and stacking a 3D patterns as well as films. In addition, when an order of the layers is important as in the case of a biosensor, utilization thereof may increase.
According to one or more embodiments, the removing of the surfactant included in the colloidal composition through pores inside the hydrogel without damaging the printed pattern may further include contacting the hydrogel with a liquid for faster removal thereof. More particularly, the hydrogel may be immersed in a liquid, e.g., distilled water, to the extend lower than a height of the hydrogel, for 10 minutes to 5 hours, 10 minutes to 2 hours, 20 minutes to 2 hours, 30 minutes to 2 hours, 30 minutes to 1 hour, or 20 minutes to 1 hour. Accordingly, the surfactant included in the composition to improve dispersity may be removed without damaging the pattern.
According to one or more embodiments, the method of producing the nanoparticle device may further include transferring the nanoparticle device formed on the hydrogel to a substrate. The transferring of the nanoparticle device to the substrate may be performed by contacting the substrate with an upper surface of the hydrogel. The transferring is performed based on the principle of difference in interfacial energy between the hydrogel and the substrate. As used herein, the term “contact transfer” refers to a method of transferring via direct contact with the substrate as described above. According to a contact transfer method, the pattern formed on the hydrogel may become upside-down. In the case of a multi-stacked structure according to an example embodiment, an uppermost layer will be a lowermost layer in a final device. In an example embodiment, the method may further include drying the transferred composition. In another example embodiment, the method may further include immobilizing an enzyme on the dried composition. The enzyme may be an analyte binding material. As used herein, the terms “analyte binding material” and “analyte binding reagent” are used interchangeably and may refer to a material specifically binding to an analyte. The analyte binding material may include a redox enzyme. The redox enzyme may refer to an enzyme that oxidizes or reduces a substrate and may include, for example, oxidase, peroxidase, reductase, catalase, or dehydrogenase. Examples of the redox enzyme may include blood glucose oxidase, lactate oxidase, cholesterol oxidase, glutamate oxidase, horseradish peroxidase (HRP), alcohol oxidase, glucose oxidase (GOx), glucose dehydrogenase (GDH), cholesterol esterase, ascorbic acid oxidase, alcohol dehydrogenase, laccase, tyrosinase, galactose oxidase, or bilirubin oxidase. The enzyme may be included in the graphitic material in a state of being immobilized on or in the mesh structure. The term “immobilized” may refer to a chemical or physical bond between an enzyme and a graphitic material. The method may further include treating a polymeric material on the formed device. The composition according to an example embodiment may be reformed with a positively charged polymer or a negatively charged polymer, although there is no need for a separate reforming process for the composition. For example, the positively charged polymer may be poly(allyamine) (PAH), polydiallyldimethylammonium (PDDA), polyethylenei mine ethoxylated (PEIE), or poly(acrylamide-co-diallyldimethylammonium) (PAMPDDA). Also, the negatively charged polymer may be, for example, poly(4-styrenesulfonate) (PSS), poly(acrylic acid) (PAA), poly(acryl amide) (PAM), poly(vinylphosphonic acid), poly(2-acrylamido-2-methyl-1-propanesulfonic acid) (PAAMP), poly(anetholesulfonic acid) (PATS), or poly(vinyl sulfate) (PVS).
The substrate may be a conductive or insulating substrate. A material of the substrate may include a metal, a semiconductor, an insulator, a polymer, an elastomer, or the like. For example, the substrate may be a quartz substrate or a gold substrate. According to an embodiment, the substrate may be a transparent flexible substrate. For example, the transparent flexible substrate may be a substrate formed of polydimethylsiloxane (PDMS), polyethersulfone (PES), poly(3,4-ethylenedioxythiophene), poly(styrenesulfonate), polyimide, polyurethane, polyester, perfluoropolyether (PFPE), polycarbonate, or any combination of the polymers. In an example embodiment, a flexible electronic device may be prepared by detaching the nanoparticle pattern using a flexible polymer substrate and drying the nanoparticle pattern. In an example embodiment, the nanoparticle pattern may be transferred to a flexible stretchable substrate such as a polymer glove for experiments. The pattern designed according to an example embodiment may be printed on the hydrogel, transferred to the quartz substrate, and dried to form an electrode, e.g., an electrode device, more particularly, a transparent electrode.
Thus, according to one or more embodiments, a transparent electrode includes the device produced according to the production method of the present disclosure. Although metals have been line-patterned due to low conductivity of a transparent electrode, carbon nanotubes cannot be line-patterned by existing methods in which a surfactant is removed by washing/acid-treatment. However, a transparent electrode may be manufactured using carbon nanotubes by enabling line patterning using the production method according to the present disclosure.
According to one or more embodiments, the transferring of the nanoparticle device to the substrate may include: separating the nanoparticle device from the hydrogel by adding a liquid in which the nanoparticle device formed on the hydrogel is able to float; and transferring the nanoparticle device to the substrate by contacting the substrate with a surface of the floating nanoparticle device facing the hydrogel. Throughout the specification, such a transferring method is referred to as “floating transfer method”. The pattern prepared according to an example embodiment may be printed on the hydrogel in a multilayered structure, floating on water, and transferred to the substrate to form an electrode. For example, a biosensor electrode may be prepared by printing an ink including a carbonaceous material and a biomaterial, printing polyethyleneimine (PEI) thereon to form an intermediate layer, and printing a GOx enzyme thereon. The prepared biosensor electrode is transferred to a commercial electrode by floating the biosensor electrode on water, and thus an electrode may be configured to satisfy requirements for a device, in which the order of printing and the surface layer are important, and the upper and lower layers of the biosensor electrode may not be inverted. Thus, according to the method of producing a nanoparticle device according to the present disclosure, a multi-layer is formed by stacking another functional layer onto the composition or immobilizing an enzyme onto the composition, and the multi-layer is transferred to the substrate with the stacking order maintained. In addition, in the case of forming an electrode on a substrate having a nanometer or micrometer scale pattern, it may be difficult to form a desired shape due to the shape of the pattern and characteristics of inkjet printing. When a desired pattern is printed on the hydrogel and transferred by floating, the electrode may be formed and transferred without being affected by the shape of the substrate, and thus a high-performance device may be prepared.
According to one or more embodiments, a biosensor includes the nanoparticle device produced according to the production method. The biosensor may further include a test cell for accommodating a sample, a substrate, and an enzyme electrode, and the test cell may include a channel having an inlet or an outlet for introducing or discharging the sample.
The biosensor according to an example embodiment may include a test cell including a channel formed on a substrate with a working electrode (WE), a counter electrode (CE), and a reference electrode (RE) located thereon. The test cell has an inlet for introducing a sample or an outlet for discharging the sample. The sample may be introduced through the inlet and the analyte included in the sample may participate in a redox-reaction with an enzyme to cause an electrochemical potential gradient. The term “chemical potential gradient” may refer to a concentration gradient of a redox-active material. When the gradient is present between two electrodes, a potential difference may be detectable when a circuit is opened, and when the circuit is closed, a current may flow until the gradient is reduced to zero. The chemical potential gradient may mean a gradient of potential formed by a potential different or current flow between the electrodes generated by asymmetric distribution of the redox enzyme (e.g., analyte binding material). In a biosensor according to an example embodiment, a strong peak of the redox reaction is observed in a working electrode on which the enzyme electrode is transferred, and the redox peak slightly occurs or does not occur in the other electrodes. Thus, in the biosensor according to an example embodiment, the migration of electrons due to the redox reaction between an analyte and an enzyme may be direct electron transfer (DET) on a working electrode with an enzyme electrode transferred thereon in the absence of a medium.
As used herein, the term “analyte” may refer to a material of interest that may be present in a sample. A detectable analyte may include materials involved in a specific-binding interaction with one or more analyte-binding materials, which participate in a sandwich, competitive, or replacement assay configuration. Examples of the sample may include blood, body fluid, cerebrospinal fluid, urine, excreta, saliva, tear, or sweat. Examples of the analyte may include antigens such as peptides (e.g., hormone) or heptens, proteins (e.g., enzyme), carbohydrates, proteins, drugs, agricultural chemicals, microorganisms, antibodies, and nucleic acids participating in sequence-specific hybridization with complementary sequences. More particular examples of the analyte may include glucose, cholesterol, lactate, hydrogen peroxide, catechol, tyrosine, and galactose.
A biosensor according to an example embodiment may further include a meter for determination of an analyte. As used herein, the term “determination of an analyte” refers to qualitative, semi-quantitative and quantitative processes for evaluating a sample. In a qualitative evaluation, a result indicates whether or not the analyte is detected in the sample. In a semi-quantitative evaluation, the result indicates whether or not the analyte is present above some predefined threshold. In a quantitative evaluation, the result is a numerical indication of the amount of the analyte present.
The meter may include an electronic device that measures a potential difference or current at a predetermined time after a sample is introduced, and converts a measurement value into a numerical indication. The measuring of the potential difference or current may be determining of an oxidation current reaction voltage value by using cyclic voltammetry (CV). According to the CV, a potential of a first electrode (e.g., a working electrode) is circulated at a predetermined rate to measure a current. The converting of the measurement value may be performed by referring to a look-up table that is used to convert a value of a current or potential into a value of an analyte dependent on a specific device structure and a correction value with respect to the analyte. Also, the meter may further include a display showing results and a frame including at least one controlling interface (for example, a power button or a scroll wheel). The frame may include a slot for receiving a biosensor. The frame may include a circuit inside to apply a potential or current to an electrode of the biosensor when a sample is provided. A suitable circuit for the meter may be a suitable voltage meter that measures a potential crossing the electrode. Also, provided is a switch that is opened when the potential is measured or is closed when the current is measured. The switch may be a mechanical switch (for example, relay), or a field-effect transistor (FET) switch, or a solid-state switch. The circuit may be used to measure a potential difference or a current difference. As understandable to one of ordinary skill in the art, other circuits including more simple or complicated circuits may be used to apply a potential difference, a current, or both.
According to one or more embodiments, a wearable device includes the biosensor. The wearable device may be used for detecting bioinformation. The wearable device may be a patch, a watch, or a contact lens. The biosensor may exhibit remarkable electrochemical properties on a transparent flexible substrate and an electrode harmless to the human body. Further, the biosensor does not need a mediator harmful to the human body and has high sensitivity enough to detect a small amount of an analyte in a sample.
According to one or more embodiments, a nanoparticle device is produced according to the production method of the present disclosure. The nanoparticle device prepared according to the production method according to the present disclosure has a high degree of homogeneity of the nanoparticles over the entire pattern due to excellent dispersibility, has a high binding affinity between nanoparticles by removing the surfactant, and has excellent electrical activity due to high accuracy of the pattern. Thus, the nanoparticle device may be applied to implementation of 3D pattern which could not be realized by conventional methods, implementation of a nanoparticle device on a polymer glove, or the like, and line pattering of nanoparticles such as carbon nanotubes. Also, because dialysis is performed in a liquid, freestanding is required and thus addition of a biomaterial such as a phage is required according to conventional membrane dialysis methods. However, the device according to the present disclosure is different therefrom because addition of a biomaterial such as a phage is optional. Also, because washing or heat/acid treatment is not required to remove the surfactant, a device may be provided without damaging a pattern.
The above and other aspects, features, and advantages of certain embodiments of the disclosure will be more apparent from the following description taken in conjunction with the accompanying drawings, in which:
A method of producing a nanoparticle device according to the present disclosure may be economical by using a hydrogel, may be easy to design a mass production process, and may reduce manufacturing time to 1/100 to 1/10 of conventional technology. In addition, a nanoparticle device may be produced in various designs by stably realizing a 3D pattern and stacking a pattern and may have excellent uniformity of nanoparticles and excellent electrical activity by removing a surfactant without damaging the pattern.
The nanoparticle device according to the present disclosure may have excellent homogeneity, high binding affinity and excellent electrical activity due to accuracy of a pattern and may be applied to stacking of pattern which could not be implemented by conventional methods.
Hereinafter, the present disclosure will be described in more detail with reference to the following examples. However, these examples are for illustrative purposes only, and the present disclosure is not intended to be limited by these examples.
According to an embodiment of the present disclosure, an agarose-based hydrogel was prepared according to the following method.
A homogenous agarose aqueous solution was prepared at a concentration of 0.8 wt % to 20 wt % using a microwave oven. The solution was cooled to a temperature of 60° C. or less by storing the solution at room temperature, and then poured into a mold and maintained at room temperature for 3 hours or more for hardening. The hydrogel prepared in this manner is shown in
According to an embodiment of the present disclosure, an acrylamide-based hydrogel was prepared according to the following method.
As a raw material, an acrylamide/bisacrylamide aqueous solution was prepared at a ratio of 19:1 to 37.5:1. Water was added thereto to prepare an aqueous solution at a concentration of 0.1% to 25% based on acrylamide. 10% ammonium persulfate solution was prepared as a hardener. After mixing the acrylamide/bisacrylamide aqueous solution and the ammonium persulfate solution, both prepared as described above, tetramethylethylenediamine, as a catalyst, was added to the mixture and mixed. The mixture was poured into a mold and maintained at room temperature for 30 minutes or more for hardening. The acrylamide-based hydrogel prepared in this manner is shown in
First, an aqueous solution was prepared by adding sodium-cholate, as a surfactant, to distilled water at a concentration of 1% or 2% w/v, and a colloidal solution was prepared by stabilizing single-walled carbon nanotubes (manufacturer: Nanointegris, SuperPure SWNTs, solution, concentration: 250 μg/mL or 1000 μg/mL), as a graphitic material, with the sodium-cholate by dialysis of the single-walled carbon nanotubes for 48 hours.
In this regard, assuming that an average length and an average diameter of the carbon nanotubes (CNTs) were 1 μm and 1.4 nm, respectively, the number of the single-walled carbon nanotubes in the colloidal solution is calculated according to the following equation.
According to Equation 1, the number of the single-walled carbon nanotubes included in 1000 μg/ml of the colloidal solution was 3×1014 CNT/mL. The number of the single-walled carbon nanotubes per unit volume was adjusted using the sodium-cholate aqueous solution having the same concentration as that of the dialyzed solution.
4-1. Preparation of Biomaterial
As M13 phages having a strong binding affinity to the graphitic surface, a M13phage (GP1) displaying a peptide SWAADIP (SEQ ID NO: 7) having a strong binding affinity to the graphitic surface and a phage (GP2) displaying NPIQAVP (SEQ ID NO: 8) were prepared according to the following method.
First, an M13HK vector was prepared by site-directed mutation of the 1381st base pair C of an M13KE vector (NEB, product # N0316S, SEQ ID NO: 13) to G.
Here, the prepared M13KE vector (NEB, product # N0316S) was a cloning vector consisting of a 7222 bp DNA (Cloning vector M13KE), and genetic information thereof is available from the Internet (https://www.neb.com/˜/media/NebUs/Page %20Images/Tools %20and %20Resource s/Interactive %20Tools/DNA %20Sequences %20and %20Maps/Text %20Documents/m13kegbk.txt). Base sequences of oligonucleotides used for the site-directed mutation are as follows:
Phage display p8 peptide libraries were prepared from the prepared M13HK vector using restriction enzymes BspHI (NEB, product # R0517S) and BamHl (NEB, product # R3136T).
The base sequences of oligonucleotides used for the preparation of the phage display p8 peptide libraries are as follows:
The nucleotide sequences of the prepared phage display p8 peptide libraries have a diversity of 4.8×107 plaque-forming units (PFU) and each sequence has a copy number of about 1.3×105. Then, the prepared phage display p8 peptide libraries were bound to a graphitic surface by biopanning to screen a phage displaying a peptide to be used as the biomaterial according to the present disclosure. The biopanning was conducted as follows.
First, a fresh surface of a highly oriented pyrolytic graphite (HOPG, SPI, product #439HP-AB) that has a graphitic surface was obtained before an experiment by attaching a tape thereto and detaching the tape therefrom to minimize defects caused by oxidation of a sample surface. In this regard, a HOPG substrate with a relatively large grain size of 100 μm or smaller was used.
Then, the prepared 4.8×1011 (4.8×107 diversities, 1000 copies per each sequence) phage display p8 peptide libraries were prepared in 100 μL of Tris-buffered saline (TBS) and conjugated with the HOPG surface in a shaking incubator for 1 hour at 100 rpm. 1 hour later, the solution was removed and the HOPG surface was washed 10 times with TBS. The washed HOPG surface was reacted with pH 2.2 Tris-HCl as an acidic buffer for 8 minutes to elute non-selectively reacting peptides and then XL-1 blue E. coli culture in mid-log state was eluted for 30 minutes. A portion of the eluted culture was left for DNA sequencing and peptide identification and the remainder was amplified to prepare sub-libraries for the next round. The above procedure was repeated using the prepared sub-libraries. Meanwhile, the left plaques were subjected to DNA analysis to identify the p8 peptide sequence. As a result, the phage (GP1) displaying the peptide SWAADIP (SEQ ID NO: 7) and the phage (GP2) displaying the peptide NPIQAVP(SEQ ID NO: 8), wherein the peptides have strong ability to bind to a graphitic surface, were obtained.
4-2. Preparation of Ink Solution Including Biomaterial
M13 phage (GP1) having a strong binding affinity to the surface of the graphitic material was dispersed in Tris-Buffered saline (TBS) at a concentration of 6×1013 number/mL. The colloidal solution prepared in Preparation Example 2 was mixed with the M13 phage solution at a volume ratio of 2:1 to mix the graphitic material with the M13 phage (GP1) at a molar ratio of 10:1. In this regard, the number of M13 particles included in the M13 phage solution was calculated according to the following equation. A269 nm and A320 nm indicate absorbances of the solution at wavelength of 269 nm and 320 nm, respectively.
Single-walled carbon nanotubes having an average length of 15 μm were dispersed in a 2 wt % aqueous solution of sodium-cholate using a homogenizer. The solution was dispersed by a tip sonicator at a power of 1% for 15 minutes. The solution was centrifuged using a centrifuge at a relative centrifugal force of 90,000 g for 15 minutes, and a supernatant was extracted therefrom to prepare an ink solution including a carbonaceous nanomaterial with a high aspect ratio.
Each of the ink solutions prepared according to Preparation Examples 3 to 5 was printed on the hydrogel prepared in Preparation Example 1 in multiple layers to prepare an electrode for analysis of characteristics. Images of ejecting solutions are shown in
Each of the ink solutions prepared according to Preparation Examples 3 to 5 was printed on the hydrogel prepared in Preparation Example 2 in multiple layers to prepare an electrode for analysis of characteristics. Subsequently, the hydrogel used as a substrate was immersed in water for 30 minutes or more to remove a surfactant and other materials used to prepare the ink solution, thereby preparing a pattern for transfer. A circular pattern prepared using the ink solution of Preparation Example 3 is shown in
Each of the patterns formed on the hydrogel and prepared in Preparation Examples 6 and 7 was dried at room temperature for 30 minutes to be transferred to a final substrate. After the surface was dried, the printed pattern was transferred from the hydrogel to the substrate by contacting the substrate with the dried surface of the pattern and detaching the substrate therefrom. An image of a square pattern prepared in Preparation Example 6 and transferred to a quartz substrate is shown in
Each of the ink solutions prepared according to Preparation Examples 3 to 5 was printed on the hydrogel prepared in Preparation Example 2 in multiple layers to prepare an electrode for analysis of characteristics. Subsequently, a polydimethylsiloxane solution was poured thereonto and hardened to transfer the printed pattern to a moldable polymer. An image of the pattern transferred by this method is shown in
The pattern formed on the hydrogel and prepared in Preparation Example 6 was dried at room temperature for 30 minutes to be transferred to a final substrate. After the surface was dried, water was added thereto until the surface was immersed in water to separate the pattern from the surface of the hydrogel. Imagers before and after the separation are shown in
The ink solution prepared in Preparation Example 4 was printed on the hydrogel prepared in Preparation Example 1 by inkjet printing. The printed pattern was transferred to a commercial electrode (Manufactured by Dropsense, 250BT) according to the method described in Preparation Example 7, and an image thereof is shown in
The ink solution prepared in Preparation Example 4 was printed on the hydrogel prepared in Preparation Example 1 by inkjet printing. The hydrogel used as a substrate was immersed in water to remove a surfactant and other materials used to prepare the ink solution. The 5 w/v % polyethyleneimine (PEI) aqueous solution was printed on the printed electrode. By immersing the hydrogel in water, PEI was attached to the electrode by charge interaction, and the excess PEI was removed through the hydrogel substrate. A 25 mg/mL GOx aqueous solution was printed on the electrode. By immersing the hydrogel in water, GOx was attached to the electrode by charge interaction, and excess GOx was removed through the hydrogel substrate. The electrode was dried at room temperature for 30 minutes to be transferred to a final substrate. After the surface was dried, water was added thereto until the surface was immersed in water to separate the prepared electrode from the surface of the hydrogel. The separated electrode was transferred to a commercial electrode and an image thereof is shown in
Evaluation of Electrical Characteristics of Pattern Prepared Using Ink Solution Including Carbonaceous Material with High Aspect Ratio
The ink solution prepared in Preparation Example 5 was printed 5 times or 10 times on the hydrogel prepared in Preparation Example 1 by inkjet printing. The printed pattern was contact transferred to a quartz substrate according to the method described in Preparation Example 8 to prepare a pattern for evaluation of electrical characteristics. Then, sheet resistance was measured by the van der Pauw method and the results are shown in
As a result, as shown in
Evaluation of Optical Characteristics of Pattern Formed Using Ink Solution Including Carbonaceous Material with High Aspect Ratio
The ink solution prepared in Preparation Example 5 was printed 5 times or 10 times on the hydrogel prepared in Preparation Example 1 by inkjet printing. The printed pattern was transferred to a quartz substrate according to the method described in Preparation Example 8 to prepare a pattern for evaluation of optical characteristics. Then, absorbance was measured in a wavelength range of 230 nm to 990 nm and converted using Equation 3 below to calculate transmittance, and the results are shown in
Transmittance(%)=10−Absorbance(@ar 550 nm) Equation 3
Measurement of Electrochemical Activity of GOx Enzyme Electrode Prepared Using Ink Solution Including Biomaterial
A negative voltage of −0.6 V to −0.2 V was applied to the glucose sensor prepared in Preparation Example 11 in 10 mM PBS buffer (pH=7.4, 79383, Sigma Aldrich) solution at a scan rate of 200 mV/s, and the results are shown in
As shown in
FAD+2H++2e−->FADH2
Based on this reaction, it may be seen that the enzyme present in the biosensor electrode prepared using a bio-adhesive may efficiently exchange electrons directly with the electrode.
Evaluation of Reactivity, to Glucose, of GOx Enzyme Electrode Prepared Using Ink Solution Including Biomaterial
CV was performed while a voltage was applied to the glucose sensor prepared in Preparation Example 11 at a scan rate of 200 mV/s in 10 mM PBS buffer (pH=7.4, 79383, Sigma Aldrich) solution including 10 μM to 500 μM of glucose, and the results are shown in
As a result, as shown in
Evaluation of Real-time Monitoring Characteristics and Specificity of GOx Enzyme Electrode Prepared Using Ink Solution Including Biomaterial for Glucose
After applying a voltage of −0.4 V was applied to a working electrode of the GOx enzyme-based biosensor prepared in Preparation Example 11, and current flowing from each electrode was measured. Particularly, 200 μM glucose was injected 5 times in divided amounts, and 1 mM uric acid was injected twice in divided amounts. The results are shown in
As a result, as shown in
Evaluation of Reactivity and Specificity of All-printed Enzyme Electrode to Glucose
CV was performed while a voltage was applied to the enzyme electrode prepared in Preparation Example 12 at a scan rate of 200 mV/s in 10 mM PBS buffer (pH=7.4, 79383, Sigma Aldrich) solution including 0 μM to 1000 μM of glucose, and the results are shown in
As a result, as shown in
CV was performed while a voltage was applied to the enzyme electrode prepared in Preparation Example 12 at a scan rate of 200 mV/s in each of 10 mM PBS buffer (pH=7.4, 79383, Sigma Aldrich) solution including 0 μM of glucose, 10 mM PBS buffer solution including 1000 μM of glucose, and 10 mM PBS buffer solution including 1000 μM of acetaminophene, and the results are shown in
As a result, as shown in
Application of Nanoparticle Device Transferred to Polymer Glove to Produce Strain Sensor
The ink solution prepared in Preparation Example 3 was printed on the hydrogel prepared in Preparation Example 1 by inkjet printing. The printed pattern was transferred to a polymer glove according to the method described in Preparation Example 8 to prepare a nanoparticle device, and the results are shown in
As a result, as shown in
| Number | Date | Country | Kind |
|---|---|---|---|
| 10-2018-0103035 | Aug 2018 | KR | national |
