WO2010059687A2 - Semi-conducteur pour mesurer des interactions biologiques - Google Patents

Semi-conducteur pour mesurer des interactions biologiques Download PDF

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Publication number
WO2010059687A2
WO2010059687A2 PCT/US2009/064938 US2009064938W WO2010059687A2 WO 2010059687 A2 WO2010059687 A2 WO 2010059687A2 US 2009064938 W US2009064938 W US 2009064938W WO 2010059687 A2 WO2010059687 A2 WO 2010059687A2
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Prior art keywords
semiconductor
matrix
gate region
binding
resistance
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PCT/US2009/064938
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English (en)
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WO2010059687A3 (fr
Inventor
Avraham Rasooly
Minghui Yang
Hugh A. Bruck
Yordan Kostov
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The United States Of America, As Represented By The Secretary, Department Of Health And Human Services
University Of Maryland, College Park
University Of Maryland, Baltimore County
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Application filed by The United States Of America, As Represented By The Secretary, Department Of Health And Human Services, University Of Maryland, College Park, University Of Maryland, Baltimore County filed Critical The United States Of America, As Represented By The Secretary, Department Of Health And Human Services
Priority to EP20090828144 priority Critical patent/EP2350644B1/fr
Priority to US13/128,851 priority patent/US8614466B2/en
Publication of WO2010059687A2 publication Critical patent/WO2010059687A2/fr
Publication of WO2010059687A3 publication Critical patent/WO2010059687A3/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • G01N33/54373—Apparatus specially adapted for solid-phase testing involving physiochemical end-point determination, e.g. wave-guides, FETS, gratings
    • G01N33/5438—Electrodes

Definitions

  • FIELD The present application relates to semiconductors, and, particularly, to electrical detection of biomolecules in a semiconductor.
  • BSC Biological semiconductors
  • Nanomaterials are increasingly being adapted for biosensing. Once such nanomaterial can be fabricated using single-walled carbon nanotubes (SWNT).
  • SWNT single-walled carbon nanotubes
  • the SWNTs are molecular wires with unique electrical properties attractive for solid- state nanoelectronics including logic gates, digital memory, digital switching and integration into logic circuits transistor arrays.
  • Individual SWNTs are quantum wires so their conductivity depends on how conduction electrons interact with the atoms within the SWNTs.
  • the electrical conductance of a single nanotube was shown to be highly sensitive to its environment, and varies significantly with changes in electrostatic charges and surface adsorption of many molecules. Using chemical vapor deposition (CVD) to grow individual tubes, it was shown that there is a large conductance change in response to the electrostatic, chemical and biological molecules when they are utilized as gates for field-effect transistors
  • CVD chemical vapor deposition
  • SWNTs chemical and biological sensors.
  • SWNTs interconnected in a submonolayer network also fabricated by CVD were shown to exhibit semiconductor-like behavior in which the conductance can be gated and surface interactions with biomolecules can be used for biosensing.
  • a semiconductor includes first and second electrodes with a gate region there between.
  • the gate region includes a multi-layered network of electrically conductive material with capture biomolecules for binding target biomolecules.
  • the network can be within a three-dimensional matrix. This allows capture biomolecules to be positioned internally within the matrix and on an outer surface of the matrix.
  • the multi-layered network can be formed by depositing of a variety of carbon-based materials, such as carbon nanotubes (CNT), graphene, or buckeyballs or using any metallic nanowires or conductive polymer nanowires.
  • CNT carbon nanotubes
  • the semiconductors can be fabricated at or near the percolation threshold. At the percolation threshold, small changes in the molecular complexes can result in large changes in conductivity increasing the sensitivity of detection.
  • biomolecular interactions are detected using the semiconductor.
  • a sample (such as a liquid sample) can be introduced, which can include target biomolecules to be detected. If the target biomolecules present in the sample are introduced into the semiconductor, a binding pair is formed between a capture biomolecule and the target biomolecule. The binding pair changes a resistance in the gate region of the semiconductor by disrupting the continuity of the network. An automatic measurement of resistance can then be performed in order to detect the biomolecular interactions. A quantitative determination of biomolecular activity can be made based on a comparison between the measured resistance and a control resistance measurement.
  • a semiconductor is fabricated by immobilizing capture molecules on surfaces of electrical conductors. A solution is created that is used to form a gate region of the semiconductor. Electrodes are then deposited on opposing sides of the gate region. The resultant semiconductor can then operate as a transistor.
  • the apparatus and method provide several advantages.
  • many (similar or different) biological semiconductors can be easily deposited on the same surface enabling simultaneous multi-sample (e.g., analyzing multiple patients for the same target) or multi-target (e.g., analyzing the same patient for multiple different targets) analysis on the same chip.
  • the biological semiconductor does not require specialized fabrication facilities or experience, which lowers the overall cost and broadens the practical applications in which the semiconductors can be used.
  • the semiconductor can be stored for long periods of time before use because of its stability.
  • the semiconductor offers fast, continuous and nearly instantaneous detection of biological activity.
  • FIGS. IA and IB show schematic profile views of a semiconductor in a first state prior to injection of target biomolecules and a second state with captured target biomolecules disrupting conductivity of the semiconductor.
  • the semiconductor includes a network of carbon nanotubes that form a three-dimensional matrix having width, depth, and length. Specific binding molecules are present on the nanotubes throughout the matrix (i.e., interior and exterior) for binding the target biomolecules. Although only two dimensions are shown in FIGS. IA and IB, it is understood that the network also extends perpendicular to the page.
  • the disruption of the network is illustrated between FIG. IA (prior to binding of the target) and FIG. IB (after binding of the target) when the three-dimensional continuity of the network is disrupted to increase resistance.
  • FIG. 2 shows an exemplary mold having a blank top portion and a bottom portion with a circuit including sixteen semiconductors fabricated in parallel.
  • FIG. 3 shows a system for continuous monitoring of a circuit including or more biological semiconductor.
  • FIG. 4 is a flowchart of a method for detecting biomolecular interactions in the semiconductor.
  • FIG. 5 illustrates additional process features that can be performed.
  • FIG. 6 is a flowchart of a method for fabricating the semiconductor of FIG. 1.
  • FIG. 7 shows data from example injections of target biomolecules into a plurality of biological semiconductors, illustrating changes in resistance of the network.
  • FIGS. 8 A and 8B illustrate percolation curves of a single- walled carbon nanotube and signal-to-baseline levels versus concentration levels of single-walled carbon nanotubes according to a first example.
  • FIG. 9 shows signal-to-baseline levels versus measured proteins, according to the first example.
  • FIG. 10 is an illustration showing that quantitative measurements in FIG. 9 correspond to traditional quantitative measurement methods using labeling and optical sensing, according to the first example.
  • FIGS. HA-C show a transistor made according to another example without electrodes on the chip.
  • FIGS. 12A and 12 B illustrate percolation curves of a single-walled carbon nanotube according to another example.
  • FIG. 13 shows electrical characteristics of staphylococcal enterotoxin B (SEB) actuation of a semiconductor according to another example.
  • FIG. 14 shows that quantitative measurements in FIG. 13 correspond to traditional quantitative measurement methods using labeling and optical sensing assay analysis of captured SEB on a semiconductor chip, according to a second example.
  • SEB staphylococcal enterotoxin B
  • Analyte or Target an atom, molecule, group of molecules or compound of natural or synthetic origin (such as, but not limited to, a drug, hormone, enzyme, growth factor antigen, antibody, hapten, lectin, apoprotein, polypeptide, cofactor) sought to be detected or measured that is capable of binding specifically to at least one binding partner (such as, but not limited to, a drug, hormone, antigen, antibody, hapten, lectin, apoprotein, cofactor).
  • a drug, hormone, enzyme, growth factor antigen, antibody, hapten, lectin, apoprotein, polypeptide, cofactor sought to be detected or measured that is capable of binding specifically to at least one binding partner (such as, but not limited to, a drug, hormone, antigen, antibody, hapten, lectin, apoprotein, cofactor).
  • the analytes may include, but are not limited to, antigens from or antibodies to infectious agents (such as HIV, HTLV, Helicobacter pylori, hepatitis, measles, mumps, or rubella), drugs (such as cocaine, benzoylecgonine, benzodiazepine, tetrahydrocannabinol, nicotine, ethanol theophylline, phenytoin, acetaminophen, lithium, diazepam, nortriptyline, secobarbital, phenobarbitol, methamphetamine, theophylline, etc), hormones (such as testosterone, estradiol, estriol, 17-hydroxyprogesterone, progesterone, thyroxine, thyroid stimulating hormone (TSH), follicle stimulating hormone (FSH), luteinizing hormone (LH), transforming growth factor alpha, epidermal growth factor (EGF), insulin- like growth factor (ILGF) I and II, growth hormone release inhibiting
  • Analytes vary in size. Merely by way of example, small molecule analytes can be, for instance, ⁇ 0.1 nm (such as cotinine or penicillin, each with a molecular weight of less than about 1,000 Daltons). However, analytes may be larger, including for instance immunoglobulin analytes (such as IgG, which is about 8 nm in length and about 160,000 Daltons). Analytes can be polyvalent or monovalent. Examples of analytes are disclosed, for example, in U.S. Patent No. 4,299,916; U.S. Patent No. 4,275,149; U.S. Patent No. 4,806,311; U.S. Patent No. 6,001,558; and PCT Publication No. 98/39657.
  • a sample containing an analyte can be any biological fluid, such as, but not limited to, serum, blood, plasma, cerebral spinal fluid, sputum, urine, nasal secretions, sweat, saliva, pharyngeal exudates, bronchoalveolar lavage fluids, or vaginal secretions.
  • Fluid homogenates can also be utilized as samples, such as cellular homogenates or fecal suspensions. Samples can also be non-biological fluids such as environmental samples, plant extracts, soil extracts or water samples. Typically a sample is in a liquid or an aqueous form, or may be an aqueous extract of a solid sample.
  • Antibody a protein consisting of one or more polypeptides substantially encoded by immunoglobulin genes or fragments of immunoglobulin genes.
  • the recognized immunoglobulin genes include the kappa, lambda, alpha, gamma, delta, epsilon and mu constant region genes, as well as the myriad immunoglobulin variable region genes.
  • Light chains are classified as either kappa or lambda.
  • Heavy chains are classified as gamma, mu, alpha, delta, or epsilon, which in turn define the immunoglobulin classes, IgG, IgM, IgA, IgD and IgE, respectively.
  • the basic immunoglobulin (antibody) structural unit is generally a tetramer.
  • Each tetramer is composed of two identical pairs of polypeptide chains, each pair having one "light” (about 25 kD) and one "heavy” chain (about 50-70 kD).
  • the N-terminus of each chain defines a variable region of about 100 to 110 or more amino acids primarily responsible for antigen recognition.
  • the terms "variable light chain” (V L ) and “variable heavy chain” (V H ) refer, respectively, to these light and heavy chains.
  • Antibodies can exist as intact immunoglobulins or as a number of well- characterized fragments produced by digestion with various peptidases.
  • pepsin digests an antibody below the disulfide linkages in the hinge region to produce F(ab)' 2 , a dimer of Fab which itself is a light chain joined to V H -C H 1 by a disulfide bond.
  • the F(ab)' 2 may be reduced under mild conditions to break the disulfide linkage in the hinge region thereby converting the F(ab)' 2 dimer into an Fab' monomer.
  • the Fab' monomer is essentially an Fab with part of the hinge region (see, Fundamental Immunology, W. E.
  • antibody fragments are defined in terms of the digestion of an intact antibody, it will be appreciated that Fab' fragments may be synthesized de novo either chemically or by utilizing recombinant DNA methodology.
  • the term antibody as used herein also includes antibody fragments either produced by the modification of whole antibodies or synthesized de novo using recombinant DNA methodologies.
  • Embodiments of the assay that use antibodies can use any form of the antibodies, such as the intact immunoglobulin or fragments thereof that retain desired specific binding characteristics.
  • Antibodies can be monoclonal or polyclonal, but often will be monoclonal.
  • such monoclonal antibodies can be prepared from murine hybridomas according to the classical method of Kohler and Milstein ⁇ Nature 256:495-497, 1975) or derivative methods thereof. Briefly, a mouse is repetitively inoculated with a few micrograms of the selected analyte compound (or a fragment thereof) over a period of a few weeks. In some instances, it will be beneficial to use an adjuvant or a carrier molecule to increase the immunogenicity and/or stability of the analyte in the animal system. The mouse is then sacrificed, and the antibody-producing cells of the spleen isolated.
  • the spleen cells are fused by means of polyethylene glycol with mouse myeloma cells, and the excess un- fused cells destroyed by growth of the system on selective media comprising aminopterin (HAT media).
  • HAT media aminopterin
  • the successfully fused cells are diluted and aliquots of the dilution placed in wells of a microtiter plate where growth of the culture is continued.
  • Antibody-producing clones are identified by detection of antibody in the supernatant fluid of the wells by immunoassay procedures, such as ELISA, as originally described by Engvall (Meth. Enzymol. 70:419-439, 1980), and derivative methods thereof. Selected positive clones can be expanded and their monoclonal antibody product harvested for use. Detailed procedures for monoclonal antibody production are described in Harlow and Lane ⁇ Antibodies, A Laboratory Manual, CSHL, New York, 1988).
  • Monoclonal antibodies to different analytes are commercially available.
  • a monoclonal antibody to estriol-3 is produced by Fitzgerald Industries International (Concord, MA; Cat. # 10-E37, Clone # M612039); likewise, Omega Biological, Inc. (Bozeman, MT) produces a monoclonal antibody to methamphetamine (Cat. # 100-11-183, Clone Met 2).
  • Rabbit anti-SEB can be purchased from Toxin Technology (Sarasota, FL).
  • Antigen a chemical or biochemical structure, determinant, antigen or portion thereof that is capable of inducing the formation of an antibody.
  • Avidin/Streptavidin The extraordinary affinity of avidin for biotin allows biotin-containing molecules in a complex mixture to be discretely bound with avidin.
  • Avidin is a glycoprotein found in the egg white and tissues of birds, reptiles and amphibia. It contains four identical subunits having a combined mass of 67,000-68,000 daltons. Each subunit consists of 128 amino acids and binds one molecule of biotin. Extensive chemical modification has little effect on the activity of avidin, making it especially useful for protein purification.
  • streptavidin Another biotin-binding protein is streptavidin, which is isolated from Streptomyces avidinii and has a mass of 60,000 daltons. In contrast to avidin, streptavidin has no carbohydrate and has a mildly acidic pi of 5.5. Another version of avidin is NeutrAvidin Biotin Binding Protein (available from Pierce Biotechnology) with a mass of approximately 60,000 daltons.
  • the bond formation between biotin and avidin is very rapid, and once formed, is unaffected by extremes of pH, temperature, organic solvents and other denaturing agents.
  • streptavidin SA
  • avidin is meant to refer to avidin, streptavidin and other forms of avidin that have similar biotin binding characteristics.
  • Binding affinity a term that refers to the strength of binding of one molecule to another at a site on the molecule. If a particular molecule will bind to or specifically associate with another particular molecule, these two molecules are said to exhibit binding affinity for each other. Binding affinity is related to the association constant and dissociation constant for a pair of molecules, but it is not critical to the invention that these constants be measured or determined. Rather, affinities as used herein to describe interactions between molecules of the described methods and devices are generally apparent affinities (unless otherwise specified) observed in empirical studies, which can be used to compare the relative strength with which one molecule (such as an antibody or other specific binding partner) will bind two other molecules (such as an analyte and an analyte-tracer conjugate). The concepts of binding affinity, association constant, and dissociation constant are well known.
  • Binding domain the molecular structure associated with that portion of a receptor that binds ligand. More particularly, the binding domain may refer to a polypeptide, natural or synthetic, or nucleic acid encoding such a polypeptide, the amino acid sequence of which represents a specific (binding domain) region of a protein, which either alone or in combination with other domains, exhibits specific binding characteristics that are the same or similar to those of a desired ligand/receptor binding pair. Neither the specific sequences nor the specific boundaries of such domains are critical, so long as binding activity is exhibited.
  • binding characteristics necessarily includes a range of affinities, avidities and specificities, and combinations thereof, so long as binding activity is exhibited.
  • the capture biomolecules disclosed herein may bind a binding domain of a target analyte.
  • Binding partner any molecule or composition capable of recognizing and specifically binding to a defined structural aspect of another molecule or composition. Examples of such binding partners and corresponding molecule or composition include antigen/antibody, hapten/antibody, cellular receptor/ligand, lectin/carbohydrate, apoprotein/cofactor and biotin/avidin (such as biotin/streptavidin).
  • binding partner e.g., protein, nucleic acid, antibody, etc.
  • a binding partner e.g., protein, nucleic acid, antibody, etc.
  • a reaction that is determinative of the presence and/or identity of one or other member of the binding pair in a mixture of heterogeneous molecules (e.g., proteins and other biologies).
  • heterogeneous molecules e.g., proteins and other biologies.
  • An enzyme would specifically bind to its substrate, a nucleic acid would specifically bind to its complement, an antibody would specifically bind to its antigen.
  • nucleic acids that specifically bind (hybridize) to their complement include, antibodies specifically bind to their antigen, and the like.
  • the binding may be by one or more of a variety of mechanisms including, but not limited to ionic interactions, and/or covalent interactions, and/or hydrophobic interactions, and/or vander Waals interactions, etc.
  • Biological interaction A specific binding interaction that could or does occur in or with a living cell.
  • a biological interaction includes any interaction between binding pairs, such as protein binding (e.g., protein-protein binding or nucleic acid-protein binding), nucleic acid binding (e.g., protein-DNA, DNA-DNA, DNA-RNA, etc.), cellular receptor binding (e.g., a cell surface receptor or intracellular receptor that binds to a cellular ligand, such as a hormone).
  • protein binding e.g., protein-protein binding or nucleic acid-protein binding
  • nucleic acid binding e.g., protein-DNA, DNA-DNA, DNA-RNA, etc.
  • cellular receptor binding e.g., a cell surface receptor or intracellular receptor that binds to a cellular ligand, such as a hormone.
  • Biotin binding protein A protein (such as a specific binding protein) that binds biotin with sufficiently great affinity for an intended purpose.
  • biotin binding proteins are well known in the art, and include avidin, streptavidin, NeutrAvidin, and monoclonal antibodies or receptor molecules that specifically bind biotin.
  • Capture biomolecule An organic molecule that is capable of production substantially by a living cell, and can specifically bind a target biomolecule by a biological interaction. Capture biomolecules can undergo non-cellular modifications (such as addition of functional groups) that cannot be added in a cell and still be considered a biomolecule.
  • Example capture biomolecules include antibodies, nucleic acid molecules, aptamers, peptides and receptors. In particularly disclosed embodiments, the capture biomolecules may change conformation when binding to the target, and this change in conformation can disrupt the continuity of the network of nanotubes to result in increased resistance. This increase in resistance indicates the presence of the analyte, and the increase in resistance can in some embodiments be proportional to the amount (such as concentration) of target analyte present in the sample.
  • Carbon nanotube As used herein, the terms “carbon nanotube” and the shorthand “nanotube” refer to carbon fullerene, a synthetic graphite, which typically has a molecular weight between about 840 and greater than 10 million grams/mole.
  • the carbon nanotubes can be single- walled carbon nanotubes (SWCNT or SWNT) or multi-walled carbon nanotubes (MWCNT or MWNT).
  • SWCNT or SWNT single- walled carbon nanotubes
  • MWCNT or MWNT multi-walled carbon nanotubes
  • the present disclosure is not limited to any one method by which to produce carbon nanotubes. Rather, any suitable method can be used to produce carbon nanotubes for use in conjunction with methods and apparatus of this disclosure. Additionally, any size of carbon nanotube can be used.
  • Carbon nanotubes suitable can have average diameters in the range of about 1 nanometer to about 25,000 nanometers (25 microns). Alternatively, the carbon nanotubes suitable can have average diameters in the range of about 1 nanometer to about 10,000 nanometers, or about 1 nanometer to about 5,000 nanometers, or about 3 nanometers to about 3,000 nanometers, or about 7 nanometers to about 1,000 nanometers, or even about 15 nanometers to about 200 nanometers. Alternatively, carbon nanotubes can have an average diameter of less than 25,000 nanometers, or less than 10,000 nanometers, or even less than 5,000 nanometers. Alternatively, carbon nanotubes suitable can have average diameters of less than 3,000 nanometers, or less than about 1,000 nanometers, or even less than about 500 nanometers.
  • the length of the carbon nanotubes is not critical and any length can be used.
  • carbon nanotubes can have lengths in the range of about 1 nanometer to about 25,000 nanometers (25 microns), or from about 1 nanometer to about 10,000 nanometers, or about 1 nanometer to about 5,000 nanometers, or about 3 nanometers to about 3,000 nanometers, or about 7 nanometers to about 1,000 nanometers, or even about 10 nanometers to about 500 nanometers.
  • the carbon nanotubes can have a length of at least about 5 nanometers, at least about 10 nanometers, at least about 25 nanometers, at least about 50 nanometers, at least about 100 nanometers, at least about 250 nanometers, at least about 1,000 nanometers, at least about 2,500 nanometers, at least about 5,000 nanometers, at least about 7,500 nanometers, at least about 10,000 nanometers, or even at least about 25,000 nanometers. Still further, the carbon nanotubes can have lengths that would not be considered to be nano-scale lengths.
  • Example nanowires include, but are not limited to metal nano wires, such as gold and silver or conductive polymers, such as polypyrolle, polythiophene, etc.
  • Detect or determine an analyte An analyte is "detected” when its presence is ascertained or discovered. "Determination" of an analyte refers to detecting an amount/concentration (either approximate or exact) of the analyte. Hence “detection” is a generic term that includes either ascertaining its presence or determining an amount/concentration (since determining an amount can also indicate the presence of the analyte).
  • Embodiments of the device and method disclosed herein are capable of detecting the presence or determining a quantity of the analyte in a sample.
  • Electrical conductors are capable of allowing electrical charges, such as electrons, to move relatively freely along the conductor.
  • Example electrical conductors include carbon nanotubes, graphene, and buckyballs.
  • Electrical Percolation Electrical percolation is used to characterize changes in the connectivity of elements within the network. Electrical percolation can be modeled as the flow of electricity through a randomly distributed network of conducting elements. In such a network, sites (vertices) or bonds (edges) are established by randomly placing resistors in a 3-D vector space with a statistically independent probability (p) of making contacts. At a critical threshold (pc), long- range connectivity within the vector space first appears (known as the "percolation threshold").
  • the conducting elements increase precipitously and there is an onset of a sharp and very significant increase in the electrical conductivity of the material. Therefore, it is characteristic of the minimal concentration of conductive filler required to form a randomly distributed network that spans the whole material system.
  • concentration of conductive filler correlating to the percolation threshold will be affected, not by the mobility of electrons within the filler, but rather by the characteristics that control the number of contacts and the contact resistance between filler elements.
  • the principles governing the percolation threshold are not “electrochemical”, but rather “electrophysical” (e.g., morphology, scale, and orientation of the filler).
  • FET Field-Effect Transistor
  • An FET is a type of transistor commonly used for weak-signal amplification (for example, for amplifying wireless signals).
  • current flows along a semiconductor path called the channel.
  • At one end of the channel there is an electrode called the source.
  • At the other end of the channel there is an electrode called the drain.
  • the physical diameter of the channel is fixed, but its effective electrical diameter can be varied by the application of a voltage to a control electrode called the gate.
  • the conductivity of the FET depends, at any given instant in time, on the electrical diameter of the channel. A small change in gate voltage can cause a large variation in the current from the source to the drain, which is how amplification of signals occurs.
  • the nanowires When nanowires are used to manufacture FETs, the nanowires must be positioned in a well-defined pattern and orientation, which requires specialized manufacturing techniques.
  • Immunogen a chemical or biochemical structure, determinant, antigen or portion thereof, that elicits an immune response, including, for example, polylysine, bovine serum albumin and keyhole limpet hemocyanin (KLH).
  • Matrix A three-dimensional region that contains the three-dimensional network of electrical conductors.
  • the matrix can have a three-dimensional shape and can have an irregular structure.
  • Capture biomolecules can be positioned throughout the matrix including on interior conductors and exterior conductors. In some embodiments, the capture biomolecules can be uniformly distributed throughout the width, length, and depth of the matrix.
  • Nucleic acid A polymer composed of nucleotide units (ribonucleotides, deoxyribonucleotides, related naturally occurring structural variants, and synthetic non-naturally occurring analogs thereof) linked via phosphodiester bonds, related naturally occurring structural variants, and synthetic non-naturally occurring analogs thereof.
  • Non-naturally occurring synthetic analogs include, for example and without limitation, phosphorothioates, phosphoramidates, methyl phosphonates, chiral- methyl phosphonates, 2-O-methyl ribonucleotides, peptide-nucleic acids (PNAs), and the like.
  • Such polynucleotides can be synthesized, for example, using an automated DNA synthesizer.
  • oligonucleotide typically refers to short polynucleotides, generally no greater than about 50 nucleotides. It will be understood that when a nucleotide sequence is represented by a DNA sequence (i.e., A, T, G, C), this also includes an RNA sequence (i.e., A, U, G, C) in which "U” replaces "T.” Conventional notation is used herein to describe nucleotide sequences: the left-hand end of a single-stranded nucleotide sequence is the 5'-end; the left-hand direction of a double-stranded nucleotide sequence is referred to as the 5'-direction.
  • RNA transcripts The direction of 5' to 3' addition of nucleotides to nascent RNA transcripts is referred to as the transcription direction.
  • the DNA strand having the same sequence as an mRNA is referred to as the "coding strand;” sequences on the DNA strand having the same sequence as an mRNA transcribed from that DNA and which are located 5' to the 5'-end of the RNA transcript are referred to as "upstream sequences;” sequences on the DNA strand having the same sequence as the RNA and which are 3' to the 3' end of the coding RNA transcript are referred to as "downstream sequences.”
  • cDNA refers to a DNA that is complementary or identical to an mRNA, in either single stranded or double stranded form.
  • a first sequence is an "antisense" with respect to a second sequence if a polynucleotide whose sequence is the first sequence specifically hybridizes with a polynucleotide whose sequence is the second sequence.
  • an antisense sequence can be used as a capture biomolecule to specifically bind a target nucleic acid molecule.
  • sequence relationships between two or more nucleotide sequences or amino acid sequences include “reference sequence,” “selected from,” “comparison window,” “identical,” “percentage of sequence identity,” “substantially identical,” “complementary,” and “substantially complementary.”
  • Polypeptide A polymer in which the monomers are amino acid residues that are joined together through amide bonds, for example ⁇ amide bonds (for example from the ⁇ position of a glutamic acid side chain) or ⁇ amide bonds.
  • the amino acids are alpha-amino acids
  • either the L-optical isomer or the D-optical isomer can be used, for example D-glutamic acid to form poly- ⁇ -D-glutamic acid ( ⁇ DPGA).
  • ⁇ DPGA poly- ⁇ -D-glutamic acid
  • polypeptide or "protein” as used herein is intended to encompass any amino acid sequence and include modified sequences such as glycoproteins.
  • polypeptide is specifically intended to cover naturally occurring proteins, as well as those that are recombinantly or synthetically produced.
  • polypeptide fragment refers to a portion of a polypeptide which exhibits at least one useful epitope.
  • functional fragments of a polypeptide refers to all fragments of a polypeptide that retain an activity of the polypeptide.
  • Biologically functional fragments for example, can vary in size from a polypeptide fragment as small as an epitope capable of binding an antibody molecule to a large polypeptide capable of participating in the characteristic induction or programming of phenotypic changes within a cell.
  • Sample or Specimen any cell, tissue, or fluid from a biological source (a "biological sample"), or any other medium, biological or non-biological, that can be evaluated in accordance with the invention, such as serum or water.
  • a sample includes, but is not limited to, a biological sample drawn from an organism (e.g. a human, a non-human mammal, an invertebrate, a plant, a fungus, an algae, a bacteria, a virus, etc.), a sample drawn from food designed for human consumption, a sample of blood destined for a blood supply, a sample from a water supply, or the like.
  • a sample is a sample drawn from a human or animal to determine the presence or absence of a specific nucleic acid sequence.
  • sample suspected of containing a particular component means a sample with respect to which the content of the component is unknown.
  • a fluid sample from a human suspected of having a disease such as an infectious disease or a non-infectious disease, but not known to have the disease, defines a sample suspected of containing an infectious pathogen.
  • the sample is one being analyzed for scientific research.
  • Sample in this context includes naturally- occurring samples, such as physiological samples from humans or other animals, samples from food, livestock feed, etc. However, the sample can also be a product made in a research laboratory.
  • Typical samples taken from humans or other animals include tissue biopsies, cells, whole blood, serum or other blood fractions, urine, ocular fluid, saliva, cerebro-spinal fluid, fluid or other samples from tonsils, lymph nodes, needle biopsies, etc.
  • the samples are liquid samples.
  • Specific binding partner a member of a pair of molecules that interact by means of specific, non-covalent interactions that depend on the three-dimensional structures of the molecules involved.
  • Exemplary pairs of specific binding partners include antigen/antibody, hapten/antibody, ligand/receptor, nucleic acid strand/complementary nucleic acid strand, substrate/enzyme, inhibitor/enzyme, carbohydrate/lectin, biotin/avidin (such as biotin/streptavidin). Examples include a hormone binding to receptors, and virus/cellular receptor. The methods and devices disclosed herein can be used for any analyte for which a specific binding partner exists.
  • analyte refers to a binding reaction which is determinative of the presence of the analyte in the presence of a heterogeneous population of molecules such as proteins and other biologic molecules.
  • a cellular receptor is, for example, capable of specifically binding to an analyte.
  • the specified antibodies bind to a particular analyte and do not bind in a significant amount to other analytes present in the sample.
  • a variety of immunoassay formats may be used to select antibodies specifically immunoreactive with a particular analyte.
  • solid-phase ELISA immunoassays are routinely used to select monoclonal antibodies specifically immunoreactive with a protein. See Harlow and Lane, Antibodies, A Laboratory Manual, CSHP, New York (1988), for a description of immunoassay formats and conditions that can be used to determine specific immunoreactivity.
  • Target analyte An analyte to be detected by the detector, and which binds to the specific binding partner on the nanotube.
  • Three-dimensional network A complex, interconnected group of electrical conductors allowing electrical charge to pass between two points using multiple and unique electrical paths.
  • the network is an unpatterned, random interconnection of electrical conductors. If any electrical paths in the network are disrupted, electrical charge can still pass between the two points using alternative electrical paths in the network.
  • the three-dimensional network can be any size (i.e., any length, depth, and width), depending on the application.
  • One example can use carbon nanotubes of at least 0.4nm in diameter.
  • the desired depth and width of the network can be greater than a single nanotube, such as 2, 3, 4, 5, etc. times the thickness of a single nanotube. Other thicknesses can be between 10 to 100 times the thickness of a single nanotube.
  • FIG. IA shows a biological semiconductor 10 having opposing electrodes
  • the gate region 16 includes a matrix 18 of electrical conductors 20 that create a plurality of electrical connections between the electrodes 12, 14.
  • the electrical conductors form a three-dimensional network of individual entangled or overlapping conductors.
  • a plurality of capture biomolecules 22 are shown as half-moon shapes and are positioned within the matrix 18.
  • the capture biomolecules 22 are shown connected to the exterior surface of the carbon nanotubes, but are contained substantially within the interior region of the matrix of entangled conductors.
  • the matrix 18 is a multi-layer, three- dimensional network that can be made of a variety of conductive materials, such as carbon nanotubes (e.g., single-walled carbon nanotubes), graphene, buckyballs, or other fullerene material. Other materials can also be used, such as metal nanowires, made of gold, silver, etc. or conductive polymers, such as polypyrolle, polythiophene, etc. By multi-layered, it is meant that multiple of the electrical conductors 20 are interconnected in the network in three-dimensional space.
  • the matrix 18 can be a solid or a solution, depending on the application.
  • the electrodes 12 are made of a conductive metal, such as silver, but other conductive metals can be used.
  • the capture biomolecules 22 are capable of binding/interacting with target molecules, such as antibodies, nucleic acid molecules, aptamers, peptides, etc.
  • the electrical conductors 20 are bound in a way as to not overly confine the conductors to allow movement in response to biomolecular binding between the capture biomolecules and targets, which are introduced into the gate region 16.
  • the gate region 16 can be protected or shielded from the outside environment using a polymer-based coating or layer, such as of polydiallyldimethylammonium chloride or other suitable covering material. Such a covering material limits any surface interaction occurring in the gate region 16, which could impact results.
  • the specimen can interact with the gate region by adding the specimen prior to placing a covering material or by placing the gate in a flow cell and injecting the specimen in the flow cell.
  • the opposing electrodes 12, 14 are electrically coupled to a resistance measuring device 24 for reading a resistance of the biological semiconductor across the gate region 16.
  • the resistance measuring device can be a commercially available ohm meter.
  • the concentration of conductive material in the matrix 18 is such that the material is at or near a percolation threshold.
  • the conductivity of the semiconductor 10 depends on the number of contacts in the network between the electrical conductors 20. This number of contacts can be varied through molecular interactions, which changes the spacing orientation, and continuity of the matrix 18.
  • the binding of target analyte to the receptors within the matrix disrupts the pre- binding architecture of the matrix to change the conductivity of the matrix.
  • the molecular interactions also change the resistance of the matrix 18, which can be used to indicate the presence and/or number of molecular interactions.
  • a quantitative change in resistance can be made to correlate with a particular quantity (such as a concentration of the target molecule).
  • FIG. IB shows target molecules 26 bound to the capture biomolecules 22.
  • the molecular interactions between the capture biomolecules and the target molecules disrupt the matrix continuity resulting in increased resistance.
  • the molecular interaction can include binding of antigens to antibodies, nucleic acid binding, hormone binding to a receptor, etc.
  • the conductors 20 are not overly confined to allow for movement, some electrical paths between the electrodes 12, 14 break, which forces current to pass through other conductors, increasing overall resistance.
  • FIG. IA represents a low-resistance mode of operation.
  • single-walled nanotubes were used (shown in black lines) with no antigens bound to antibodies (shown as half-moon shapes).
  • IB represents a high-resistance mode wherein binding of antigens (ovals) results in disruption of the three-dimensional matrix (non-contact SWNTs are shown in grey) thus increasing electrical resistance. Disruption of the three-dimensional matrix means that some of the conductive paths between electrodes have been severed, while other conductive paths remain intact.
  • FIG. IA and IB therefore, show that the semiconductor is based on electrical percolation, rather than FETs where channel width changes as a result of gate activity.
  • Semiconductors based on electrical percolation are easier to manufacture than FETs, as there is no need for direct chemical vapor deposition or specialized expertise needed for FET manufacture.
  • FETs require specific patterned, structured placement of nanowires.
  • semiconductors formed using the techniques described herein use an unoriented, unstructured, pattern less, mesh-like network of interconnected conductors.
  • the binding molecules are therefore distributed throughout the interior of the gate region, instead of being confined to an outer surface.
  • various binding partners can be used to functionalize pre-made SWNT gates in bulk. The gates can then be simply printed or deposited onto non-conductive materials.
  • FIG. 2 shows a tray 40 that can be used to assemble a plurality of biological semiconductors in parallel.
  • the tray acts as a base substrate and can be made of plastic or other non-conductive material.
  • An upper portion 42 of the tray is blank and has a plurality of blank forms 44 for making biological semiconductors.
  • the forms can be any shape and dimensions.
  • a lower portion 46 has sixteen biological semiconductors coupled in parallel, such as a biological semiconductor shown at 47. Although sixteen are shown, the number of biological semiconductors can be any desired number simply by modifying the size of the tray 40.
  • the biological semiconductor can be manufactured as a stand-alone device, such as a more traditional transistor package or chip.
  • Positive electrodes 12 are floating and are used to connect a positive lead of an ohm meter or other resistance measuring device.
  • Negative electrodes 14 are coupled together through an electrical common 56 that extends the width of the tray. Any number of the electrodes 50 can be coupled to one or more resistance measuring devices. Between the positive and negative electrodes 12, 14 are the gate regions 16 having a three-dimensional network into which one or more different specimens may be injected. Upon injection, molecules of the specimen can bind with capture biomolecules in the network resulting in increased resistance across a gate region of the biological semiconductor. Some of the biological semiconductors in the tray 40 can act as control elements, which are used as a baseline to show the resistance of the biological semiconductors without any molecular reactions.
  • Such a baseline is needed in order to determine a difference between a measurement of resistivity of a biological semiconductor that had a detectable target molecule and a biological semiconductor that had no specimen introduced or that had limited or no molecular binding.
  • a biological semiconductor can have a different antibody associated with it.
  • a user's sample can be injected into all sixteen gate regions and sixteen different readings can be taken to determine different antigens in the sample.
  • the gate regions 16 are circular in cross section (i.e., cylindrical in three-dimensions), but other shapes can be used, such as rectangular, square, etc.
  • FIG. 3 shows a system 70 for implementing continuous monitoring.
  • One or more biological semiconductors 72 include networks with capture biomolecules to which targets are bound.
  • An electrical resistance detector 76 continuously monitors one or more of the biological semiconductors in order to detect molecular interactions.
  • the resistance detector can be an ohm meter or other devices for measuring current, voltage, resistance capacitance or impedance.
  • the detector 76 is coupled to a computer 78 that monitors and stores readings from the detector. Periodic readings can be taken and compared to control readings where no biomolecular activity occurred.
  • the computer 78 can be coupled to a digital-to- analog converter 80, which allows the computer 78 to communicate with a pump 82 and a plurality of valves 84.
  • the valves 84 can be coupled to one or more specimens 86, which are samples to be injected into the biosemiconductors in order to detect biomolecules therein. If two-way communication is desired between the computer 78 and the pump and valves, an analog-to-digital converter can be housed together with the digital-to-analog converter, as is shown at 80. Such two-way communication may be desirable to monitor that state of the valves and the pumping mechanism. In general operation, the computer releases one or more of the specimens 86 by controlling the valves 84. The pump 82 then pumps the specimen released by the valves and injects it into the gate region 16 of the semiconductor for analysis. Using the system 70, biomolecular sampling and detection can be fully automated.
  • FIG. 4 is a flowchart of a method for detecting and measuring biomolecules in a specimen.
  • a circuit is provided including a biosemiconductor with a gate region of electrically conductive material whose resistance changes with biomolecular binding.
  • An example semiconductor is shown in FIG. 1 and example circuits are shown in FIGs. 1, 2 and 3.
  • a specimen is applied to the circuit including target biomolecules to be detected by the circuit.
  • automatic application can occur using the system of FIG. 3.
  • manual application can be used.
  • automatic measurement of resistivity can be performed, such as using resistance detector 76 of FIG. 3. Using the measured resistance, a change is resistivity as compared to a previous measurement can be performed.
  • FIG. 1 a circuit is provided including a biosemiconductor with a gate region of electrically conductive material whose resistance changes with biomolecular binding.
  • An example semiconductor is shown in FIG. 1 and example circuits are shown in FIGs. 1, 2 and 3.
  • a specimen is applied to
  • process block 110 the specimen can be automatically injected into the gate region 16 of the semiconductor.
  • Such automatic injection can occur through using a pump 82 (FIG. 3), which is responsive to a computer 78, for pumping the specimen released by control valves 84 and delivering the specimen to the gate region 16 of a semiconductor.
  • a pump 82 FIG. 3
  • control valves 84 for pumping the specimen released by control valves 84 and delivering the specimen to the gate region 16 of a semiconductor.
  • process block 112 an automatic comparison is made between the measured resistance and a
  • Such automatic comparison can occur using the computer 78.
  • the computer 78 can measure a control resistance obtained through measuring the resistance of a biological semiconductor that does not have molecular binding pairs as described above.
  • process block 114 using a difference calculation between the measured resistance and a control resistance, a quantity of biomolecules in the specimen can be determined.
  • FIG. 6 is a method of manufacturing a semiconductor for measuring biological interactions.
  • a multi-layered material is provided that is capable of forming a network of electrical conductors.
  • the multi-layered material can be formed from a bio-nanocarbon material, such as carbon nanotubes (e.g., single-walled carbon nanotubes), graphene, buckyballs, etc.
  • capture biomolecules are immobilized onto surfaces of electrical conductors in the bio-nanocarbon material through electrostatic absorption, using techniques well known in the art.
  • the gate region 16 is formed that is a three-dimensional network of electrical conductors.
  • electrode material e.g., silver, gold, etc.
  • a semiconductor such as a transistor.
  • no specific electrodes are needed and the leads of the measuring device can be connected directly to opposing ends of the gates (See FIG. 11).
  • a specific example of manufacture for the gate region is provided below. Additional techniques are well known in the art. Suitable densities of nanotube material can be derived from percolation curves associated with the material used. For example, in FIG. 8A, the density determined can be based on where the percolation curve levels off, such as between .5 and 1.5. Some examples densities have been shown in the art and are described in U.S. Patent No. 6,918,284, at column 2, lines 54-64, which is hereby incorporated by reference.
  • FIG. 7 includes graphs A, B, and C showing an experiment with the system in continuous monitoring mode.
  • Staphylococcal enterotoxin B SEB
  • the trace labeled “a” shows 100 ng/mL of SEB. As can be seen, all traces react nearly simultaneously to injection of target biomolecules.
  • the trace labeled “b” shows 1 g/mL BSA.
  • the trace labeled “c” shows 1 g/mL of lysozyme.
  • the trace labeled shows 1 g/mL IgG applied to a sensor.
  • Graph B demonstrates the rapid response of the biological semiconductor.
  • Graph C demonstrates SEB is bound to the biological semiconductor by having a first injection of SEB, shown at I, and a second injection shown at II. The signal is detected as shown by trace "e", but it is not detected in control trace "f.”
  • Example 1 Using Single-walled Carbon Nanotubes.
  • a detector was fabricated with the bio-nanocomposite material by depositing pre-functionalized single-walled nanotubess (SWNTs) with biological ligands to form a biological semiconductor (BSC) layer.
  • SWNTs single-walled nanotubess
  • BSC biological semiconductor
  • FIG. 2 A simplified prototype of the BSC sensor is shown in FIG. 2.
  • the BSC is a unipolar device, with two electrodes painted with silver contact paste on both sides of the printed SWNT-antibody bio-nanocomposite.
  • Several BSCs can be easily fabricated in a row on the same surface.
  • each BSC contains a connection well, shown at 130 for the silver electrode, a channel, shown at 132 for the bio-nanocomposite and a channel 134 for the silver electrode that functions as a common ground point for all BSCs.
  • the resultant plurality of semiconductors are shown in the lower portion 46 of FIG. 2.
  • the SWNTs were functionalized with rabbit anti-SEB IgG.
  • a previously developed CNT functionalization scheme is employed for binding the SWNTs with antibodies.
  • the fabrication and preparation of the carbon nanotubes is described in more detail in Example 2.
  • the bio-nanocomposite is then immobilized by drying it directly on the surface of either Poly(methyl methacrylate) (PMMA) or polycarbonate wells fabricated by laser micromachining.
  • the BSC is operated simply by measuring the electrical resistance between the silver paste electrodes. Binding of the specific antigen to the antibody disrupts the network and increases the resistance. The amount of binding of the specific antigen to the antibody controls the overall resistance of the electrical percolation BSC network, which is measured by an ohmmeter via each BSC electrode 50 and the common electrode 56.
  • FIG. 8 includes two graphs showing concentration levels for single- walled carbon nanotubes. Varying concentration levels can be used based on the application, but for single-walled carbon nanotubes it is believed that a concentration of about between 1 and 1.5 mg/ml is suitable.
  • the concentration levels can be chosen to that the network is maintained at around the percolation threshold so that any molecular interactions can have a measurable impact on resistance.
  • percolation principles it is possible to characterize changes in the connectivity of elements within the network by modeling electrical percolation as the flow of electricity through a randomly distributed network of conducting elements.
  • sites verices
  • bonds edges
  • p statistically independent probability
  • the conducting elements increase precipitously and there is an onset of a sharp and very significant increase in the electrical conductivity of the material. Therefore, it is characteristic of the minimal concentration of conductive filler required to form a randomly distributed network that spans the whole material system.
  • concentration of conductive filler correlating to the percolation threshold will be affected, not by the mobility of electrons within the filler, but rather by the characteristics that control the number of contacts and the contact resistance between filler elements.
  • the principles governing the percolation threshold are not “electrochemical”, but rather “electrophysical” (e.g., morphology, scale, and orientation of the filler).
  • FIG. 8 shows an establishment of a percolation threshold of the SWNT- antibody network using various concentrations of SWNT immobilized onto a PMMA surface without (FIG. 8A, labeled (a)) and with anti-SEB antibody (FIG. 8 A, labeled (b)).
  • Their resistance was measured to determine the percolation threshold, vp, using a conventional power law equation from percolation theory with a baseline resistance. Using a power law fit, it was possible to determine that the percolation threshold for the SWNT-antibody network is between 0.2 to 0.3 mg/mL, and does not change significantly after antibody immobilization.
  • the rate of change in resistance is directly related to the power-law exponent, n, which was 8 and the power-law coefficient, a, which was 5.xl0-6, in this particular example.
  • n the power-law exponent
  • a the power-law coefficient
  • SWNT concentration There are three characteristic regimes in SWNT concentration associated with these values: (1) between -0.2 to 0.5 mg/mL the percolation threshold is characterized by a steep change (approximately four orders of magnitude) in resistance due to the onset of percolation, (2) between -0.5 to 1 mg/mL the change levels off and the increase is approximately one order of magnitude, (3) over -1 mg/ml the resistance levels off and does not change significantly with higher concentrations of SWNT resulting in complete percolation. Over the entire range, the total change in resistance is approximately five orders of magnitude.
  • the percolation threshold of the SWNT- antibody bio-nanocomposite network also indicates that its typical resistance (FIG. 8A, labeled (b)) will be higher than the resistance that is attributed to the SWNT only (FIG. 8A, labeled (a)), presumably due to the contacts between the antibody and the functionalized SWNT.
  • the S/B ratio from eight replicas of various concentrations of SEB was compared to buffer.
  • a T-test demonstrated that at 1 ng/ml, the S/B ratio is significantly different (P ⁇ 0.00017) from the value using buffer only.
  • the current configuration has a LOD of 1 ng/mL for SEB.
  • an independent measurement of bound SEB to the SWNTs bio-nanocomposite was carried out using a sandwich immunoassay detected by Enhanced Chemiluminescence (ECL). As shown in FIG.
  • the intensity of the signal from the captured SEB on the BSC chip is proportional to the amount of SEB.
  • the linear regression is also highly significant (p ⁇ 0.0056), suggesting that the anti-SEB antibody on the BSC chip did indeed capture SEB, and that the direct electrical measurements are in agreement with the indirect sandwich immunoassay detected by ECL.
  • the percolated SWNT-antibody network can therefore be considered the "conduction band", and the number of electrons in the conduction band (i.e., the band gap) is physically determined by the number of SWNT-antibody complexes in the conduction band, rather than by the conventional electronic band gap at the surface of the SWNT that is responsible for electrochemical detection principles.
  • the response of the electrical percolation BSC can be attributed to the number of contacts of carbon nanotubes within the network. Since the number of contacts can be varied by molecular interactions (i.e., by antibody-antigen binding), changes in the resistance of the network can be used to determine the number of interactions and hence the concentration of the target molecule.
  • FETs field-effect transistors
  • BSC Bio Central Processing Units
  • SEB affinity purified IgG, and peroxidase (HRP) conjugated anti-SEB IgG were purchased from Toxin Technology (Sarasota, FL).
  • Single-walled Carbon Nanotubes (CNTs) were obtained from Carbon Solutions Inc (Riverside, CA).
  • Poly(diallyldimethylammonium chloride) polymer (PDDA) was purchased from Sigma- Aldrich (St. Louis, MO).
  • Silver contact "Silver Liquid” was purchased from Electron Microscopy Sciences (Hatfield, PA).
  • Immun-Star HRP Chemiluminescence Kit was obtained from Bio-Rad (Hercutes, CA). All other reagents were of analytical grade and de-ionized water was used throughout.
  • the BSC sensor was designed in CorelDrawl 1 (Corel Corp. Ontario, Canada) and micro-machined in 1.5 mm acrylic using a computer controlled laser cutter Epilog Legend CO2 65 W cutter (Epilog, Golden, CO).
  • Epilog Legend CO2 65 W cutter Epilog, Golden, CO.
  • the lower side of the PMMA sheet was coated with 3M 9770 adhesive transfer doublesided tape (Piedmont Plastics, Beltsville, MD) and the polycarbonate film was immobilized directly on the PMMA.
  • the bio-nanocomposite was bonded to the polycarbonate film and the electrodes were filled with silver conducting paste.
  • Carbon nanotube preparation The CNTs (30 mg) were first shortened and oxidized by mixing with concentrated sulfuric acid and nitric acid mixture (3: 1 v/v) and sonicating with a Fisher (FS-14) sonicator for 6 h followed by extensive washing in water (100 ml) until neutralized (pH 7.0). Then the CNT were dispersed in 100 ml IM NaOH solution for 5 min to achieve net negative charged carboxylic acid groups and washed with water (100 ml).
  • CNT functionalization a linker molecule to the carbon nanotube was used to attach the capture biomolecule.
  • Poly(diallyldimethylammonium chloride (PDDA) is positively charged and SEB antibody was negatively charged, so antibodies electrostatically adsorbed onto carbon nanotube.
  • the positively charged polycation was adsorbed by dispersing the CNT in 50 ml of 1 mg/mL PDDA containing 0.5 M NaCl for 30 min followed by centrifugation (10,000 RPM in Beckman centrifuge for 15 minutes) and washed with 100 ml of water.
  • CNT-antibody complex preparation The CNT were functionalized by dispersing in a rabbit anti-SEB IgG phosphate buffer solution (20 mM, pH 8.0) at a concentration of 0.01 mg/mL for 1 h at room temperature, so that the antibody was adsorbed onto the CNT surface. After centrifugation (15 minutes) and washing extensively with water (10 ml), the modified CNT was stored at 4 0 C in pH 8.0 phosphate buffer at a concentration of approximately lmg/mL for no more than two weeks before use.
  • BSC detection of SEB The CNT-antibody complex described above is immobilized directly on polycarbonate. Before applying SEB samples, the resistance of the BSC is first measured (R 0 ). Different concentrations of SEB samples in phosphate buffer are added to sample wells and incubated for 60 min at room temperature (25 0 C). After washing, the BSC was dried at room temperature for 2 hours and the resistance measured again (Ri). The difference between the two readings (R] - Ro) is used as signal corresponding to different concentration of SEB.
  • ECL detection using ECL For the control experiment, after SEB binding, the BSC was then blocked with 1% BSA in 15 ⁇ l buffer for 30 min. A HRP conjugated anti-rabbit IgG was added to the captured SEB and after 60 minutes incubation and washing, ECL was achieved by adding 7mL of ECL buffer (formed by mixing the two solutions from the chemiluminescent kit in a 1:1 volume ratio) into each well and the ECL intensity was measured immediately with a custom-built point-of-care CCD detector.
  • the CCD-based detector consists of an SXVF- M7.cooled CCD camera (Adirondack Video Astronomy, Hudson Falls, NY) equipped with a 5mm extension tube and a 12mmPentax fl.2 lens (Spytown, Utopia, NY). The luminescence was measured after 2 and 10 minutes of exposure. The CCD image intensities were analyzed using ImageJ software, developed and distributed freely by the NIH, and the data generated was then imported into Microsoft Excel for further manipulation.
  • CM Cation exchanger carboxymethylcellulose
  • loading buffer 5 mM NaP03, pH 5.7
  • Sample preparation The tubes containing the spiked food samples were vortexed briefly, centrifuged at 14,000 rpm for 2 min, and the resulting supernatant transferred into a fresh tube. Loading buffer was added into the supernatant to reach a sample volume of I mL. The sample (400 J.1L) was mixed with 200 J.1L of equilibrated eM, and vortexed for 30 min which was following by centrifugation at 14,000 rpm for 2 min and the soluble material was removed. The material left at the tube was then washed 3 times by repeatedly adding loading buffer and centrifuging. Finally, 100 J.1L elution buffer (50 mM aP03, pH 6.5; 50 mM NaCI) was added to the matrix, the tubes centrifuged and eluted material collected for immunoassay.
  • elution buffer 50 mM aP03, pH 6.5; 50 mM NaCI
  • the semiconductor sensor used (See FIG. 11) is a unipolar device, with two electrodes on both side of the SWNT-antibody resistor printed on a PMMA surface. Several BSCs can be printed on the same PMMA surface. At the circuit level, semiconductor operation is simple: the current flow through the BSC gate via the source and drain electrodes and the application of the specific antigen into the gate controls the resistance of the semiconductor, which is measured by an ohm meter via the electrodes.
  • the biological nanocomposite sensor acts as a semiconductor with a variable gate with an ON mode and with a constant current flow between the source and drain. Upon actuation by binding of antigen to the antibody on the gate (FIG. 1 IB), the current flow changes with the change of resistance of the semiconductor. Such change in conductivity (the variable OFF mode) depends on the amount of antigens bound.
  • FIG. HC A simplified prototype of the semiconductor sensor is shown in FIG. HC.
  • the rabbit anti-SEB IgG -functionalized SWNT gate was immobilized into the PMMA circuit board fabricated with laser micromachining.
  • a previously developed CNT functionalization scheme was used in which shortened (by sonication) and oxidized CNT (reacted with concentrated sulfuric acid and nitric acid mixture) were dispersed in NaOH solution to achieve net negative charged carboxylic acid groups which then absorb a linker molecule Poly(diallyldimethylamrnonium chloride (PDDA) which is positively charged.
  • PDDA diallyldimethylamrnonium chloride
  • the activated CNT was then reacted with rabbit anti-SEB IgG which are negatively charged, so antibodies electro statically adsorbed onto carbon nanotube.
  • the circuit board with eight such semiconductors was then used for conventional immunodetection assay including binding of SEB to the gate and washing unbound material.
  • a second layer of PMMA with holes for the source and the drain electrodes (FIG. HC, middle portion) was used to seal the eight BSC sensor chip.
  • the assembled chip is shown in FIG. 11C, bottom.
  • the source and the drain electrodes were inserted into the holes to measure change in resistance upon actuation by SEB.
  • the measurement value was calculated as the difference between the initial reading recorded (Rn) with no SEB and the reading with SEB (Rr). The difference between the two reading was used as signal corresponding to different concentration of SEB.
  • SWNT-antibody percolation curve For establishing SWNT-antibody percolation curve, various concentrations of SWNT (FIG. 12A, labeled as (a)) and SWNT film immobilized with primary antibody (FIG. 12A, labeled as (b)) were immobilized on PMMA at various SWNT concentrations, v, and their resistance, Q, was measured to determine the percolation threshold, vP' using a conventional power law equation.
  • the percolation threshold for SWNT is between 0.2 to 0.3 mg/mL (FIG.
  • the threshold shifted to between 0.3 and 0.4 mg/mL, reducing the base conductivity, ⁇ , by l/3rd and increasing the exponent, n, from 8 to 9 while shifting the percolation threshold from 0.2 to 0.22.
  • the percolation threshold of the SWNT -antibody indicates that the typical resistance of the will be higher than the resistance is attributed to the SWNT, presumably due to the contacts between the antibody and the SWNT in the functionalized SWNT.
  • the change in resistance as the SWNTs percolate is approximately 5 orders of magnitude.
  • the SWNT film was prepared with 1 mg/mL of SWNT, which has a resistance of around 1 k ⁇ , and corresponds to the point at which the change in resistance begins to level off, consistent with the complete percolation of the SWNTs.
  • the resistance increased to about 5 k ⁇ .
  • this 1 mg/mL of SWNT should provide the greatest sensitivity to the increase in resistance due to SEB.
  • the resistance increased proportionally to the amount of SEB.
  • a quadratic logarithmic fit was applied and was found to be the best for the log of SEB concentration.
  • the log fit indicates a LOD that is -0.01 ng/mL, which is similar to typical levels of detection for commercial colorimetric ELISA systems which is from 0.5 to 2 ng/gr of food (16, 18-20,25,27).
  • eight samples of 1 ng/ml, SEB were analyzed and the RSD was 10.5%.
  • ECL buffer mix the two solutions from Chemiluminescent Kit in a 1 : 1 volume ratio
  • ECL intensity was measured immediately with a custom-built Point-of-Care CCO detector described in previous work. The luminescence was measured over the full optical spectrum after 20 minutes of exposure.
  • the CCO Image intensities were analyzed using ImageJ software, and the data generated is then analyzed using a concentration of 0 ng/mL SEB as background. The ratio of the signal to background (S/B) ratio was further used to quantify the SEB concentration.
  • S/B signal to background
  • the intensity of the signal from the captured SEB on the BSC chip is proportional to the amount of SEB. Quantitative analysis of the data (FIG.

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Abstract

La présente invention concerne un appareil et un procédé permettant de détecter électriquement et directement une liaison biomoléculaire dans un semi-conducteur. Ce semi-conducteur peut être basé sur la percolation électrique d'un nanomatériau formé dans la région de grille. Dans un mode de réalisation de l'appareil, le semi-conducteur comprend une première et une deuxième électrode, séparées par une région de grille. La région de grille comprend une matrice multicouche de matériau électriquement conducteur avec des molécules de capture pour fixer des molécules cibles telles que des anticorps, des récepteurs, de l'ADN, de l'ARN, des peptides et des aptamères. Les interactions moléculaires entre les molécules de capture et les molécules cibles interrompent la continuité de la matrice, ce qui modifie la résistance, la capacité ou l’impédance électrique. L'augmentation de résistance, de capacité ou d’impédance peut être directement mesurée électroniquement, sans recourir à des capteurs optiques ou des marqueurs. La matrice multicouche peut être formée à partir d'une pluralité de nanotubes monoparois, de graphène, de buckminsterfullerènes ou de tout autre type de nanofil conducteur, tel que des nanofils métalliques ou des nanofils fabriqués à partir de polymères conducteurs.
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CN102208545A (zh) * 2011-04-18 2011-10-05 电子科技大学 一种柔性光电子器件用基板及其制备方法
CN102208543A (zh) * 2011-04-18 2011-10-05 电子科技大学 一种柔性光电子器件用基板及其制备方法
TWI688768B (zh) * 2013-03-14 2020-03-21 美商拜耳保健公司 分析物濃度測定的正規化校正
WO2014162148A3 (fr) * 2013-04-04 2014-11-27 Isis Innovation Limited Capteur
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WO2015001286A1 (fr) * 2013-07-01 2015-01-08 Swansea University Biocapteur
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CN104777318A (zh) * 2015-04-30 2015-07-15 云南师范大学 一种c-反应蛋白免疫传感器及其使用方法
WO2018216017A1 (fr) * 2017-05-24 2018-11-29 Technion Research And Development Foundation Ltd. Capteurs de dioxyde de carbone comprenant un polymère liquide ionique
WO2021146710A1 (fr) * 2020-01-17 2021-07-22 Graphene-Dx, Inc. Capteur de toxicologie à base de graphène de point de collecte

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US20110217763A1 (en) 2011-09-08
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EP2350644A2 (fr) 2011-08-03
EP2350644A4 (fr) 2012-04-04

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