CAPACITIVE SENSOR FOR CHEMICAL ANALYSIS AND MEASUREMENT

Abstract: An apparatus for detecting the presence and/or measuring the concentration of an analyte in a fluid by using a biochemical binding system having a substrate (12), a first conductor (10) and a second conductor (14) disposed on substrate (12). The conductor (10) and (14) are spaced apart to form a channel therebetween. A thin insulating layer (16) is coated on the surface of conductors (10, 14) and substrate (12) to form an ''open'' capacitor. A biospecific binding agent (20) is immobilized on the surface of the insulating layer (16) between the conductors (10, 14). The dielectric constant of the biospecific binding agent (20) is altered by binding of the analyte being detected/measured with the biospecific binding agent (20).

Description: Capacitive Sensor for Chemical Analysis and Measurement Corresponding to U.S. Patent Application Serial No. 799,761 Filed: November 19, 1986 Be it known that Arnold L. Newman, a citizen of the United States of America, and resident of Maryland, has invented a certain new and useful apparatus for detecting the concentration of an analyte in a fluid medium, of which the following is a specification: STATEMENT OF GOVERNMENTAL INTEREST The Government has rights in this invention pursuant to Contract No. N00024-85-C-5301, awarded by the Department of the Navy. BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an apparatus for determining the concentration of an analyte in a fluid medium. More particularly, the invention relates to a capacitive sensor which is uniquely designed to detect a change in the dielectric constant caused by biospecific binding of an analyte with a biochemical binding system. The biochemical binding system is selected to have specific affinity to the particular analyte or group of analytes under test. 2. Description of the Prior Art Various prior art techniques have attempted to measure the concentration of an analyte in a fluid medium using a binding substance having specific affinity for the analyte. Immunoassays are used to identify analytes, such as haptens, antigens and antibodies in a fluid medium. These immunoassays are based on biospecific binding between components of a reaction pair, such as the biospecific binding between an antigen and an antibody. Tagging one of the components of the binding pair enables more detailed quantification. For example, radioimmunoassay uses a radioisotope as a label for one of the components of the biospecific binding pair. Similarly, fluorescent labels have been used with fluorescent i munoassay. More recently, attempts have been made to develop an electrochemical sensor which can directly measure analyte concentration. Such sensors would greatly simplify and speed up immunoassay laboratory procedures and provide greater accuracy. These sensors generally detect a change in the physical, electrical or optical properties as one of the binding pairs (generally an antibody) biospecifically binds to its mated pair (generally an antigen). U.S. Patent 4,314,821, issued to Thomas K. Rice detects the change in resonance frequency of a piezoelectric oscillator as antibodies bind to the oscillator. The change in resonant frequency is proportional to the build-up of bound complexes on the oscillator surface (i.e., the build-up of the antibody-antigen complex physically changes the resonance of the oscillator). In U.S. Patent 4,238,757, issued to John F. Schenck, an antigen in a fluid medium is brought into contact with a protein surface layer and alters the charge of the surface layer through an antigen- antibody biospecific binding reaction. A field effect transistor is used to detect this change in charge. Similarly, U.S. Patents 4,444,892 and 4,334,880 detects a change in charge which occurs with certain biospecific binding reactions by using a polyacetylene semiconductive device. U.S. Patent 4,219,335, issued to Richard C. Ebersole, teaches the use of immune reagents labeled with reactance tags. These tags can be detected electrically since they alter the dielectric, conductive or magnetic properties of the test surface. The patent teaches binding a receptor agent to a test surface. The patient's body fluid containing a certain antibody is added to the test area and the antibody complexes with the receptor agents." In a second step, the test area is exposed to a second immune reagent that is bonded to a reactance tag. This immune tag complexes with the receptor agent-patient antibody complex, if present, on the test surface. The reactance tag containing a metal or metal-oxide is then detected by electrical means. U.S. Patent 4,054,646, issued to Ivan Giaever, teaches a method for determining, by electrical means, whether an antigen-antibody reaction produces a monomolecular layer or a biomolecular layer. An antigen is used to coat a metal substrate. The coated substrate is then brought into contact with the fluid suspected to contain a certain antibody. If the antibody is present it adheres to the antigen layer forming a biomolecular layer. If the antibody is not present, a monomolecular layer remains. The next step is to place a mercury drop on the upper layer and measure the capacitance between the mercury drop and the metal substrate. Since the distance between the mercury drop and the metal substrate changes for the biomolecular layer as compared to the monomolecular layer, the measured capacitance also changes. U.S. Patent 4,072,576, issued to Hans Arwin et al, teaches measuring the alternating voltage impedance between two platinum electrode plates immersed in a fluid medium. A biochemical substance, is adsorbed onto the metallic surface. If the fluid under test contains an analyte biospecific to the adsorbed substance binding will occur. For example, an antigen may be absorbed directly on the metal electrodes and a specific antibody in the test fluid may bind to it forming a complex which remains on the surface of the metal electrodes. The capacitance changes depending on whether the surface is coated with a mololayer of the antigen or whether a biomolecular layer, composed of antigen and antibody layers, are absorbed onto the surface. SUMMARY OF THE INVENTION The present invention represents a new type of electrochemical sensor for determining the concentration of ananalyte in a fluid medium. The invention has increased speed and accuracy compared to prior art methods. The invention utilizes an "open" capacitor which produces a higher electric field in a first volumetric region VI and a lower electric field in a second volumetric region V2. A change in the dielectric constant within the first region VI will have a greater effect on the measured capacitance than a change in the dielectric constant within the second region V2. Biospecific binding reactions are used to draw into or release large biochemical molecules from a surface located within the first region VI. Movement of these large molecules displaces molecules of the fluid medium which has a higher dielectric constant. The region VI is specifically designed so that the large molecules released from the binding surface can rapidly diffuse from region VI thereby allowing the sensor to respond relatively rapidly. The sensor has two general embodiments. In the first embodiment, referred to as the direct binding configuration, a surface in region VI is coated with-a layer of immobilized binding agent molecules. The binding agent molecules, may be antibodies immobilized on the substrate surface. The binding agent molecules are biospecific with a particular analyte, such as a virus, bacteria or large molecule. As fluid containing the analyte is introduced onto the sensor and approaches the surface, the analyte binds to the immobilized binding agent. As the analyte binds to the surface, fluid molecules are displaced from region VI changing the dielectric constant of the "open" capacitor. The second embodiment, referred to as the competitive binding embodiment, uses a more elaborate biochemical binding system. This method is preferred when the analyte molecules are relatively small. The biochemical binding system has a first layer of the analyte or analyte-analog immobilized on the substrate surface. A second layer of a binding agent, biospecific to the analyte, is bound onto the immobilized analyte layer. The binding agent molecules are larger molecules and have a lower dielectric constant than the fluid medium. When free analyte molecules in the fluid medium are introduced onto the sensor, they compete with the immobilized analyte molecules to bind with the binding agent molecules. This competitive binding results in a certain amount of the binding agent molecules forming a complex with the free analyte molecules. The free analyte-binding agent complex then diffuses from region VI allowing the higher dielectric fluid molecules to enter region VI, and increase the measured capacitance. The invention also teaches combining the invented analyte affinity capacitor with at least one reference capacitor to form a differential affinity sensor. The reference capacitor is used to compensate for non-analyte effects. These non-analyte effects include changes in the dielectric constant of the fluid medium caused by a change in temperature, ionic concentration, pH, composition and physical state of the fluid medium, as well as non-specific binding of other proteins contained within the fluid medium. The invented capacitive sensor can be used to measure the concentration of specific analytes in body fluids and can function as either an in vivo or in vitro sensor. The capacitor sensor can also be used to detect specific substances in the environment. The use of the reference capacitor allows the sensor to continuously measure analyte concentration even though the physical and chemical characteristics of the fluid medium containing the analyte may change. The capacitance affinity sensor can be used to detect a broad range of analytes including: bacteria, viruses, antibodies, large protein molecules, antigens, haptens, polysaccharides, glycoproteins, glycolipids, enzyme inhibitors, enzyme substrates, neurotransmitters and hormones. BRIEF DESCRIPTION OF THE DRAWINGS Figures la and b are schematic cross-sectional views of the direct binding configuration with Figure la showing the structure of the capacitive sensor, and Figure lb illustrating the operation of the capacitive sensor ' to detect the presence of an analyte in a fluid medium. Figures 2a and 2b are schematic cross-sectional views of the competitive binding configuration with Figure 2a showing the structure of the capacitive sensor and Figure 2b illustrating the operation-of the capacitive sensor to detect the presence of an analyte of in a fluid medium. Figure 3 is a perspective view of an "open" capacitor that uses a plurality of interdigited fingers. Figure 4 is a top view of an "open" capacitor which uses interleaved conductors. Figure 5 is a perspective view of an "open" capacitor that uses two parallel conductive wires positioned in an insulator. Figures 6a, b and c are schematic cross-sectional views showing various embodiments of the reference capacitor with Figure 6a showing a reference capacitor which does not contain the biochemical binding system. Figure 6b showing a reference capacitor that uses a "dummy" binding agent for the binding system, and Figure 6c showing a reference capacitor using a binding system composed of a "dummy" analyte and binding agent pair. Figures 7a and b are schematic cross-sectional views of the differential affinity sensor using a molecular sieve, with Figure 7a showing a single molecular sieve associated with both the affinity and reference capacitors and Figure 7b showing a first molecular sieve associated with the affinity capacitor and a second molecular sieve associated with the reference capacitor. Figure 8 is an embodiment of the differential affinity sensor having an affinity capacitor and a reference capacitor located side-by-side. Figure 9 is an embodiment of the differential affinity sensor having the affinity capacitor and the reference capacitor located back-to-back. Figure 10 is a schematic diagram of the circuit to detect the phase difference between the affinity capacitor and the reference capacitor. Figure 11 is a„schematic diagram of a microprocessor system for use with a differential affinity sensor that has an affinity capacitor and at least one reference capacitor. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The Capacitive Chemical Sensor can be made chemically sensitive to an analyte by any of a variety of biospecific chemical binding methods. These biospecific binding methods fallinto two general categories: (1) competitive binding configuration, and (2) direct binding configuration. As used herein, the term "analyte" means the species to be analyzed. Direct Binding Embodiment Figure la is a schematic cross-sectional view showing the first general configuration of the sensor, referred to as the direct binding configuration. A first conductor 10 is positioned on the surface of an insulating material or substrate 12; and, a second conductor 14 is also positioned on substrate 12 and disposed a distance from the first conductor 10 creating a channel between the two conductors. The two conductors 10, 14 are coated with a thin electrically insulating layer 16, and the resulting structure forms an "open" capacitor. When a direct alternating voltage is applied across the conductors, an electric field is generated having electric lines of flux 18. As seen generally in Figure la, the electric field has a higher field intensity within the volumetric region VI and a lower field intensity within volumetric region V2. Molecules of a binding agent 20 are immobilized on a surface in the volumetric region VI. In Figure la, the binding agent is immobilized within the channel formed between the two conductors; however, a layer of the immobilized binding agent may coat the entire surface covering the insulated conductors as well as the top surface of the substrate. The techniques for immobilizing the binding agent on the surface are known in the art and will be discussed later in this specification. The binding agent is an affinity ligand that will bind specifically to the analyte, such as an antibody binds specifically to a particular virus. Alternatively, the affinity ligand may bind to a specific group of analytes, such as nucleotide analogs and lectins bind to certain groups of biochemical analytes. In Figure lb, a fluid medium to be tested for a particular analyte is introduced onto the "open" capacitor. The sensor may be immersed into the fluid as in the case of an in vivo medical sensor or an environmental sensor; or, a small volume of the fluid medium may be poured onto the sensor. The fluid medium, shown in Figure lb, is composed of molecules of fluid 22 and molecules of analyte 24. The fluid medium fills the sensor volume VT which is composed of volumetric regions VI and V2. The fluid medium may be body fluids such as blood, urine, tears, saliva, semen or it may be other buffered solutions containing the analyte. The fluid molecules 22 will generally include water molecules and small amounts of protein molecules, ionic substances, etc. The dielectric constant of the analyte species must be lower than the dielectric constant of the dominant fluid molecule, generally the water molecule. In operation, when an analyte species in the fluid medium enters the "open" capacitor sensor and approaches the surface, it binds to the immobilized binding agent (i.e., the ligand layer). This binding will occur until equilibrium is reached between the binding agent, the analyte, and the binding agent-analyte complex (i.e., the ligand-analyte bound species). This equilibrium relationship can be related by the following equation: (A) + (B) =___: (A'B), where A = Analyte, B= Binding Agent and (A-C) is the Bound Complex. As the analyte species binds to the surface, fluid molecules from region VI are displaced and the resulting dielectric constant in a region VI will decrease. This change in the dielectric constant will be proportional to the analyte species concentration as related by the following equations : ( 1 ) [A- B] = K [A ] [B ] ( 2 ) T A = [A ] + [A- B ] ( 3 ) T B = [B ] + [A- B] where, [A] = free analyte concentration [B] = binding agent (ligand) concentration [A-B] = bound analyte-ligand complex T A = total analyte concentration Tβ = total binding agent (ligand) concentration It is to be understood that the above equilibrium equations are only approximations and are used only to illustrate the general functioning of the sensor. The quantity T Q , the number of immobilized binding agent molecules, is know; the quantity K is known or can be determined by experimentation; the concentration [A-B] is measured by the change in the dielectric constant of the "open" capacitor; and, the total concentration of the analyte in the test fluid (T A ) is what one wants to determine. For these equations to be generally representative, there should not be a large concentration gradient of the free analyte molecules in region VI. This concentration gradient can be reduced by thermal diffusion over a small volume. Therefore, the "open" face capacitor is specifically designed so that region VI, having the highest electric field flux, is small and there is a short diffusion distance for analyte molecules released from the binding surface 20 to migrate from region VI. It is also within the inventor's contemplation to measure the sensor response during non-equilibrium conditions. The use of kinetic rate equations or empirical data can relate non- equilibrium measurements to total analyte concentration. Usually, but not exclusively, the analyte species for the direct binding configuration will be large molecules (generally larger than 150,000 daltons) such as bacteria, viruses, other antibodies, or protein molecules. The larger the analyte molecule and the lower its dielectric properties, the greater will be the change in the bulk dielectric constant of region VI as the analyte binds to surface 20. Table I contains anon-limiting example of the type of binding agents (ligands) and analytes that can be used with the direct binding configuration of the sensor: TABLE I immobilized analyte binding agent bio-specific antibody bacteria bio-specific antibody viruses bio-specific antibody a second antibody bio-specific antibody large molecule analytes such as protein mole¬ cules Competitive Binding Embodiment The second general embodiment of the present invention is shown in the schematic cross-sectional view of Figure 2a. This embodiment is referred to as the competitive binding configuration of the sensor and is particularly useful in sensing analytes that are "small" molecules. In this case, small is defined as significantly smaller in molecular weight than 150,000 daltons (1 dalton = 1 atomic mass unit), the approximate atomic mass of antibodies. A first conductor 26 is positioned on the surface of an insulating material or substrate 27; and, a second conductor 28 also positioned on substrate 27 is disposed a distance from first conductor 26, creating a channel between the two conductors. The two conductors 26, 28 are coated with a thin electrically insulating layer 30, and the resulting structure forms an "open" capacitor, similar to that used in the first direct binding embodiment. As with the first embodiment, when a direct or alternating voltage is applied across the conductors, an electric field is generated having electric lines of flux 32. As seen generally in Figure 2a, the electric field has a higher field intensity within the region of VI, and a lower field intensity within region V2. The essential difference between the direct and competitive binding embodiments is that a two-layer biochemical binding system is used in the latter. A first layer 34 is made from molecules of the analyte or an analog of the analyte that is immobilized on a surface in the volumetric region VI. A second layer 36 is made from molecules of a binding agent that are biospecific with the analyte. The second layer 36 binds to the immobilized analyte layer 34. The molecules of the binding agent are generally large compared to the analyte molecules. Figure 2a shows the two-layer binding system positioned within the channel formed between the two conductors; however, the two-layer binding system may coat the entire surface covering the insulated conductors as well as the top surface of the substrate. In Figure 2b, the fluid medium to be tested for a particular analyte is introduced onto the "open" capacitor, as was done with the direct binding embodiment. The fluid medium that can comprise body fluids or a fluid buffer, is composed of fluid molecules 38 and analyte molecules 40. The fluid molecules 38 will generally include water molecules, as well as small amounts of protein molecules, ionic substances, etc. The binding agent is selected to have a dielectric constant lower than the dielectric constant of the dominant fluid molecule, generally the water molecule; and, the binding agent molecule is selected to be substantially larger than the dominant fluid molecule. In operation, when analyte species in the fluid medium enters the "open" capacitor sensor and approaches the two- layer biochemical binding system, it competes with the immobilized analyte 34 to bind with binding agent molecules 36. Since the binding agent molecules are in dynamic equilibrium, there is always a small fraction of these molecules not bound to the immobilized analyte. When free analyte enters into the system, some of these unbound binding agent molecules bind to the free analyte. This results in an overall loss of the binding agent molecules from the surface of the biochemical binding system as equilibrium is restored. The binding agent-free analyte complex diffuses from the binding system to region V2, allowing higher dielectric fluid molecules to enter the higher intensity electric field region VI. The result is an increase in the dielectric constant of the capacitor. This change in the dielectric constant will be proportional to the concentration of the analyte species as related by the following equations: (4) [A-C] = Ki [A] [C] (5) [A-B] = K 2 [A] [B] (6) T A = [A] + [A-C] + [A-B] (7) TB = [B] + [A-B] (8) Tc = [C] + [A-C] where [A] = binding agent concentration [B] = free analyte concentration [C] = immobilized analyte concentration [A-B] = free analyte-binding agent complex [A-C] = immobilized analyte-binding agent complex A = total binding agent concentration β = total free analyte concentration T c = total immobilized analyte concentration It is again to be understood that the above equilibrium equations are only approximations and used only to illustrate the general functioning of the sensor. For these equations, the quantity T A , the number of binding agent molecules, is known; the quantities K and K 2 are known or can be determined by expe imentation; the concentration [A-C] is measured by the change in the dielectric constant of the "open" capacitor; the quantity T c , the number of immobilized analyte molecules, is known; and, the total concentration of the analyte in the test fluid (T A ) is what one wants to determine. For these equations to be generally representative there (1) should not be a large concentration gradient of the free analyte molecules in region VI; and (2) the free analyte-binding agent complex (A:B) should diffuse rapidly from region VI. This concentration gradient can be reduced by thermal diffusion over a small volume. Therefore, the "open" capacitor is specifically designed so that region VI is small and there is a short diffusion distance allowing free analyte-binding agent complexes to move from the surface of the two-layer biochemical binding system and out of region VI, and the concentration gradient of free analyte in region VI is thereby reduced. Applicant envisions that the use of additional thermal energy or fluid agitation may increase the mobility of the free analyte molecules as well as the free analyte-binding agent complex molecules. It is also within the the Applicant's contemplation to measure the sensor response during nonequilibrium conditions. The use of kinetic rate equations or empirical testing can relate nonequilib ium measurements to total analyte concentration. The binding agent that forms the second layer of the biochemical binding system can be selected from general or specific affinity ligands and may include, but is not limited to, antibodies, lectins, enzymes and receptors. The immobilized analyte which forms the first layer of the biochemical binding system may be the same molecular substance as the analyte under test, or it may be an analog of the analyte that is biospecific to the binding agent. The immobilized analyte may, for example, be an antigen, a hapten, a polysaccharide, a glycoprotein, a glycolipid, an enzyme inhibitor, an enzyme substrate, a neurotransmitter, a hormone, etc. The immobilized analyte is covalantly bound to the substrate surface. Table II contains non- limiting examples of the biochemical binding system used in a competitive binding embodiment to test for particular analytes . TABLE II biochemical binding system analyte class of sensor immobilized binding agent analyte antigen antibody antigen hapten antibody hapten polysaccharides lectin polysaccharides B glycoproteins lectin glycoproteins B glycolipids lectin glycolipids enzyme enzyme enzyme inhibitor inhibitor enzyme enzyme enzyme substrate substrate enzyme enzyme enzyme inhibitor substrate 095 1 5 neurotrans¬ neural neurotrans¬ mitters receptor mitters hormones neural hormones receptor As can be seen from Table II, there are four classes of the competitive binding sensor. In class A the binding agent is an antibody specific to the analyte. The analyte may be an antigen or hapten. The biochemical binding system comprises a first immobilized layer of the antigen or hapten analyte with a second layer of the biospecific antibody biochemically bound to the immobilized analyte in the first layer. In class B, the binding agent is a lectin, which is a general ligand specific to a group of analytes. A lectin- based sensor can be made more specific by an appropriate molecular sieve membrane that excludes larger molecules in the general analyte group from reacting with the biochemical binding system. In this class, for example, the binding system could have a first immobilized layer of a polysaccharide or a membrane protein containing sugar residues of certain configurations and a second layer of the general lectin bound to the first layer. In class C, the binding agent is an enzyme reactive with an enzyme inhibitor or enzyme substrate. In this class, for example, the binding system could have an inhibitor for a particular enzyme immobilized on the sensor surface and a second layer containing the enzyme bound to the inhibitor in the first layer. With a particular enzyme substrate in the test fluid, the enzyme binding agent will be drawn from the surface of the binding system. In class D, the binding agents are neuroreceptors. The neuroreceptor has its function greatly altered by various neurotoxins and other agents. The binding system can have a layer of succinylcholine immobilized on the sensor surface with a second layer of acetylcholine receptor molecules bound to the first layer. If a neurotoxin, for example, is present in the test fluid, the receptor binding behavior will be altered and it will be released from the binding system surface, thereby altering the dielectric properties of the sensor. It is of course to be understood that these are merely examples of the biochemical binding systems that can be used with the competitive binding embodiment of the present invention. "Open" Capacitor Structures Figures 3, 4 and 5 show various embodiments of the "open" capacitor structure that can be used for either the direct or competitive binding embodiment of the sensor. Each of these alternative structures of the "open" capacitor contain similar features: (1) the electrical field intensity of the capacitor is higher in a first region VI than a second region V2; (2) the biochemical binding system is located on a surface area in the first region VI; and, (3) molecules released from the binding system have a short diffusion distance to migrate from the region VI into region V2. Figure 3 is a perspective view of an "open" capacitor that uses a plurality of interdigitated fingers. Metallic conductors 42 and 44 are positioned on an insulating substrate 46. Each conductor has a plurality of fingers that are disposed in an interdigitated manner relative to the fingers of the other conductors. The interdigitated fingers from both conductors form a plurality of channels that comprise a significant portion of the higher electric field region VI, as seen in Figures la and lb. Known photolithographic etching techniques are used to form the interdigitated fingers on the substrate. The substrate can be made from insulating materials such as Corning 7059 glass or alumina wafers. The interdigitated fingers can be made of copper and gold. Applicant selected 2 mil wide fingers that are approximately 1 mil high and separated by 3 mil spaces, although other dimensions may be used. The interdigitated fingers are covered with an insulating layer 48. Applicant made the insulating layer 48 with a 1-2.5 micron coating of parylene polymer deposited using known deposition processes and a 0.3 micron of SiO deposited using vapor vacuum evaporation deposition; however, alternative electrically insulating material can be used. In the direct binding configuration, a layer of the binding agent is immobilized onto the insulated layer 48. (see, generally Figure la). In the competitive binding configuration, the first layer of the two-layer biochemical binding system is immobilized onto the insulated layer 48 (see, generally Figure 2a). Fluid to be tested for a particular analyte is brought into contact with the "open" capacitor as discussed earlier. Figure 4 is a top view of an "open" capacitor that uses two interleaved conductors covered with an electrically insulated layer. Interleaved metallic conductors 50 and 52 are deposited on insulating substrate 54 using the same technique and materials discussed above. Each conductor is approximately 2 mil by 2 mil with a 2 mil spacing between the interleved conductors; although, other dimensions may be used. The binding agent, for the direct configuration, and the biochemical binding system, for the competitive embodiment, is immobilized on the surface of the insulated conductor and in the channels between the conductors. It is to be understood that the interdigitated and interleaved configurations of the two conductors are not limiting examples, and that other geometries can provide the desired features of the "open" capacitor. For example, in Figure 5 an embodiment of the "open" capacitor is shown that uses two parallel conductive wires 56, 58 embedded in a molded insulator 60. The molded insulator 60 is shaped to provide two channels positioned between and running parallel with the conductive wires. If a direct or alternating voltage were applied across conductors 56 and 58, electrical lines of flux 62 would be generated. The volume generally within the two channels will have a higher electric field intensity (similar to region VI in Figures la or 2a) than the region displaced further radially (similar to region V2 and Figures la and 2a). The binding agent, for the direct binding embodiment, and the biochemical binding system, for the competitive binding embodiment, are immobilized onto the surfaces 64 of the molded insulator. As with the interdigitated and interleaved embodiments, the following occurs: (1) the field intensity of the capacitor is higher within the two channels (region VI) than in the radially extended regions (region V2); (2) the biochemical binding system or binding agent is immobilized within the area (VI) having the higher electric field intensity; and (3) molecules removed from the binding system have a short diffusion distance to migrate from the region of the two channels (the region of higherns electrical field intensity) the radially extending regions having lower field intensity. This embodiment of the "open" capacitor can be placed in a 1 millimeter dialysis tube 66 which acts as a molecular sieve and the entire sensor can be inserted into a patient's vein or artery to measure the concentration of a particular analyte in the patient's blood. As an alternative to this embodiment, conductive wires 56, 58 are twisted around a center line. This embodiment may provide additional noise immunity. Further, in each of the embodiments in Figures 3, 4 or 5, the surface area of the binding agent or biochemical binding system can be increased by adding a plurality of ridges, corrugations, or protrusions in region VI. These ridges, corrugations or protrusions are positioned within the channels formed in region VI are be coated with the immobilized binding agent or biochemical binding system. Differential Capacitive Sensor The accuracy of both the direct binding and competitive binding embodiments of the present invention is increased if differential sensing is employed. The differential capacitive sensor uses an analyte affinity sensor (i.e.,the direct binding capacitive sensor or the competitive binding capacitive sensor discussed above) and at least one reference capacitor to compensate for non- analyte effects. The reference capacitor compensates for changes in dielectric constant of the fluid medium caused by changes in temperature, ionic concentration, pH, composition and physical and chemical state of the fluid medium, as well as non-specific binding of proteins that may be in the fluid medium. Figures 6a, b, and c, show various embodiments of the reference capacitor. Each reference capacitor has a first and second conductor 68, 70 positioned on a substrate to form the "open" capacitor as described above. In Figure 6a, a reference capacitor that can be used with both the direct and competitive binding embodiments is shown. This reference capacitor has no protein coat, i.e., it does not have the immobilized binding agent or binding system. In Figure 6b, a reference capacitor for use with the direct binding embodiment is shown. This reference capacitor contains an immobilized layer of a "dummy" binding agent 72. The "dummy" binding agent is selected from the same class as the analyte sensitive binding agent but it is made biospecific to a molecule not found in the test environment. Alternatively, if the reference capacitor uses the same binding agent as the affinity capacitor, a molecular sieve would be used to prevent the analyte from entering the reference capacitor. In Figure 6c, a reference capacitor for use with the competitive binding embodiment is shown. This reference capacitor contains a "dummy" biochemical binding system. The "dummy" binding system uses an immobilized "dummy" analyte 74 specifically reactive with a "dummy" binding agent 76. The "dummy" analyte and binding agent are chosen to have an affinity constant and other physical characteristics that closely match the real analyte and real binding agent. If an antigen-antibody pair are chosen for the binding system of the affinity capacitor, the "dummy" antibody would be selected from the same class of antibodies and from the same type of animal, but would not be biospecific with the analyte antigen. The reference capacitor may use only the immobilized "dummy" analyte layer, and not the "dummy" binding layer. Alternatively, the reference capacitor may use the same antigen-antibody pair as the affinity capacitor but a molecular sieve would be used to prevent the analyte from entering the reference capacitor. Each of the different types of reference capacitors outlined above compensates for non-analyte changes in the fluid medium. However, a multiplicity of reference capacitors could be used with one affinity capacitor. These reference capacitors would identify the end points and/or other specific points of the dose/response curve. The analyte concentration would be determined by the dielectric change in the analyte affinity capacitor as compared to the boundary values provided by the reference capacitors. The molecular sieves shown in Figures 7a 7 b enable the invented affinity sensor to be immersed in the test fluid. The molecular sieve provides two functions: (1) it retains the binding agent molecules in the sensor; and, (2) it selectively screens certain larger molecules from entering the "open" capacitor sensor. Figure 7a is a schematic drawing of a competitive binding differential sensor having an analyte affinity capacitor 78 and reference capacitor 80 (for simplicity the biochemical binding system is not shown in Figure 7a). Fluid molecules flowing into or from the analyte and reference capacitors must pass through molecular sieve 82. The molecular sieve is of a known construction having a pore size that can easily pass the fluid and analyte molecules but will not allow the larger binding agent molecules to escape from the sensor. The pore size for an antigen-antibody binding system would be less than 150,000 daltons to keep the antibody within the sensor. Molecular sieves are particularly useful when the sensor is an in vivo sensor implanted, for example, in a patient's blood stream. The molecular sieve prevents the binding agent molecules released by the binding system from being removed by the blood flow from the sensor. Figure 7b is a schematic drawing of a competitive binding differential sensor in which the analyte capacitor 78 and the reference capacitor 80 have separate molecular sieves 84 and 86. In this case, molecular sieve 84 prevents the binding agent molecules from leaving the affinity capacitor. A separate molecular sieve 86 is used with the reference capacitor if the reference capacitor does not use a "dummy" binding system but uses the same binding system as the affinity capacitor. In this case, the molecular sieve 86 provides the following two functions: (1) preventing the binding agent molecules from leaving the reference capacitor and, (2) preventing the analyte molecules from entering the reference capacitor. This form of reference capacitor would be particularly sensitive to changes in the affinity constant of the binding agent-immobilized analyte complex caused by temperature changes. It is to be further understood that a molecular sieve of this nature can be used to filter unwanted larger molecules from interacting with the biochemical binding system. In that case, the pore size of the molecular sieve would be such that fluid and analyte molecules could pass through whereas larger unwanted molecules would be blocked by the molecular sieve. The construction, fabrication and choice of materials for these types of molecular sieves are known in the art. Figures 8 and 9 show various embodiments for a differential sensor that includes an affinity capacitor and a reference capacitor. Figure 8 is a top view of an affinity capacitor 88 and a reference capacitor 90 located side by side on the same substrate. Figure 9 is a cross- sectional view of an affinity capacitor 92 and a reference capacitor 94 located back-to-back. A metal shield 96 located between the capacitors isolates the electrical field generated by each capacitor. For both the side-by- side and back-to-back embodiments, the fluid medium under test would be simultaneously introduced onto both the affinity and reference capacitors. It is also to be understood that a molecular sieve could be used to encompass either or both the reference capacitor and the affinity capacitor. The following non-limiting examples, describe several specific embodiments of the differential sensor: Example 1. Competitive binding embodiment. The analyte or analyte analog is immobilized on the dielectric surface forming the first layer of the biochemical binding system. An analyte specific antibody is conjugated to the immobilized analyte species and forms the second layer of the biochemical binding system. The sensor is enclosed by a molecular sieve membrane with pores large enough to be permeable to the analyte but small enough to confine antibodies on or close to the sensor. This example is appropriate for small and medium molecular weight analytes compared to antibodies, which have molecular weights of approximately 150,000 daltons. With this example, the most appropriate, but not exclusive, reference capacitor is made exactly the same way as the analyte sensitive side, except that a "dummy" analyte and its associated specific "dummy" antibody is used. The "dummy" analyte and its specific antibody are chosen to have an affinity constant and other physical characteristics that closely match the analyte and analyte specific antibody characteristics. The reference capacitor is also enclosed by a molecular sieve. A second reference capacitor configuration with no bound "dummy" antibody may also be used. Example 2. Direct Binding Embodiment. An antibody specific to particular cells, such as bacteria or to viruses, or to large molecules, is immobilized on the surface of the "open" capacitor, forming the binding agent molecules. A large molecule, bacterium, or virus, when bound to this antibody, will displace a significant amount of the fluid molecules, (predominantly water molecules) from the higher density electric field volume VI, and thus cause a detectable change in capacitance. In this case, a molecular sieve membrane would not be required. However, it would be useful to cover the surface with a mesh. The reference side of this sensor consists of a capacitor with a "dummy" antibody immobilized on the insulating substrate. This antibody is of the same class as the analyte sensitive antibody, but is made specific to a molecule not found in the test environment. Example 3. Competitive Binding Equipment. This sensor is analogous to Example 1, but uses a receptor in place of an antibody as the second layer of the biochemical binding system. A generic sensor for neurotoxins can be configured using acetylcholine receptors. A substrate, such as succinylcholine, for which the receptor has affinity, is immobilized on the dielectric substrate, forming the first layer of the biochemical binding system. Receptor molecules are then conjugated to the substrate forming the second layer of the biochemical binding system. The receptor molecules are confined within the sensor by the use of a molecular sieve. When a neurotoxin permeates, the receptor is pulled off the surface, and capacitance changes. A reference capacitor is made identical to the analyte sensitive side except that the molecule chosen for surface immobilization is one with an affinity so large that substances of interest will not pull the receptor off the immobilized layer. The above three examples show models that can be used for a large number of possible sensor configurations. It is to be understood that other binding agents and biochemical binding systems than those shown above are within the scope of this invention. Figures 10 and 11 are schematic diagrams which illustrate two possible circuits to be used with the differential sensor as taught by ' the present invention. Figure 10 is a schematic diagram of a circuit to detect the phase difference between the affinity and reference capacitors. A stable oscillator 98 supplies an alternating signal to the affinity capacitor 102 and the reference capacitor 104. These capacitors are placed in parallel with trimmer capacitors 104 and 106. Phase detector 108 detects the phase angle shift between the affinity capacitor 102 and the reference capacitor 104. The phase difference is functionally related to the analyte concentration in the fluid medium. Figure 11 is a schematic diagram of a microcomputer system for use with the differential sensor. The system contains an analyte affinity capacitor 110 and a plurality of reference capacitors 112 and 114 (although, a single reference capacitor may be used). The affinity and reference capacitors (110, 112, 114) are brought into contact the fluid under test. Each capacitor is connected to an oscillator (116, 118, 120) and a change in the capacitance will alter the frequency of oscillation of its associated oscillator. The output frequency of each - oscillator (116, 118, 120) is fed to an associated counter (122, 124, 126) which sends_ the frequency count in digital form via bus 128 to microcomputer 130. A look-up Table or Equations similar to Equations (1) through (8) are stored in the microcomputer and a determination of the concentration of the analyte in the fluid medium is made. This value is displayed on output display 132. It is to be understood, that other circuits can also be envisioned once one understands the differential change in capacitance between the analyte affinity capacitor and the reference capacitor as taught by the present invention. Binding Systems As described earlier, for the direct binding embodiment, molecules of a binding agent are immobilized on the substrate surface; and, for the competitive binding configuration, a layer of the analyte or analyte-analog is immobilized on the substrate surface to form the first layer of the biochemical binding system. As used herein, immobilized means attaching a molecule by one or more covalent bonds, or other biochemical bonds. Various immobilization techniques are known in the art. The attachment site on the molecule is chosen so that functional groups of the molecule have no interference. For example, in the direct binding embodiment, an antibody (the binding agent) is immobilized on the substrate so that its analyte recognizing and binding site or sites are free to function. For binding proteins, most reactions are nucleophilic with the nucleophitic group most often NH , OH or SH. Specific examples of biochemical binding systems are found in the art of affinity chromatography and are listed in Table II of Waters, R. , "Affinity Chromatography", Analytical Chemistry, Volume 57, No. 11, pp. 1099A-1114A and listed in the figures on pages 19, 21 and 22 of Parikh, I., and P. Cuatrecasas, "Affinity Chromatography", Chemical and Engineering News, August 26, 1985, pp. 17-32 (these articles being incorporated here and by reference). Attachment reactions include the use of Cyanogen Bromide, Active Esters, Epoxide, Tresyl Chloride, Carbonyldiimidazole, Thiol and Diazonium reagents. By way of illustration, the following experimental example performed by the Applicant shows covalent attachment of the biochemical binding system to the "open" affinity capacitor. The example is a sensor to detect the Trichothecene mycotoxin T-2, which is found in the environment and is produced by the fungal species Fuarium. Trichothecene mycotoxin is an agricultural toxin causing the loss of grain yield on various food crops. It has been implicated in human and animal mucotoxicoses. Experimental Example 1. The "open" capacitor is coated with a 0.3 micron thick layer of SiO. Without care to prevent hydration of the surface (dry vacuum), the surface becomes composed of silanol groups: OH OH i t Si Si The surface will have approximately 10 silanols per m^. 2. Amino groups are attached to the SiO surface for later attachment of proteins, using the following steps: a. - soak substrate in 10% Y -aminopropyl- triethoxysilane [(EtO)3-Si-(CH2.3-NH2I and dry toluene overnight at room temperature. b. wash with dry toluene; and, c. dry at 60 degrees C for two hours. The aminosilanized surface will be: 3. The surface is now ready for introduction of the Trichothecene (T-2) groups. a. The T-2 molecule is converted to a hemisuccinate derivative by heating it in the presence of Pyridine and Succinicynhydride. This derivization was necessary in this example, but some hemisuccinates can be bought off the shelf. For example, in making a hydrocortisone sensor, hydrocortisone hemisuccinate can be purchased directly from Sigma Chemical Co., and others. b. The hemisuccinate derivative of the analyte is then conjugated to the γ - amino function of the silanized surface, using a water soluble carbodiimide as a catalyst. The T-2 analyte is now immobilized on the surface of the "open" capacitor and the surface appears as follows: 4. The second layer of the biochemical, binding system is produced by adding the anti T-2 toxin antibody to fluid bathing the surface of the open face capacitor. The antibodies will bind with an affinity similar to that in the standard immunoassay (5.28 x 10? liters/mol) . The resulting biochemical binding system has a first layer of the T-2 analyte immobilized on the surface and a second layer of the anti T-2 toxin antibody specifically bound to the immobilized layer. Since the anti T-2 antibodies and the immobilized T-2 toxin are in dynamic equilibrium, an influx of free T-2 toxin molecules would perturb the equilibrium and draw the antibodies from the immobilized surface forming free analyte-antibody complexes. Removal of the free analyte- antibody complexes from the region of the capacitor sensor having higher field intensity, region VI, causes a change in the capacitance that is a direct indication of the concentration of free T-2 molecules in the fluid medium. Obviously many modifications and variations of the present invention are possible in light of the above teachings. It is therefore to be understood that within the scope of the appended claims the invention may be practiced otherwise than as specifically described.

Claims: WHAT IS CLAIMED IS: 1. A device for detecting the presence of an analyte in a fluid, said device comprising: a capacitive means for generating a time-varying electric field within said device, said device having a first volumetric region of higher average electric field intensity and a second volumetric region of lower average electric field intensity; a biochemical binding means, localized on a surface within said first volumetric region of higher average electric field intensity, for concentrating analyte onto said biochemical binding means and into said first volumetric region thereby resulting in fluid displacement from said first volumetric region to said second volumetric region, said analyte having a different bulk dielectric constant than the fluid; and, a means, associated with said capacitive means, responsive to the average dielectric constant in said first volumetric region, wherein relative analyte and fluid movement between said first volumetric region and said second volumetric region causes a change in said average dielectric constant. 2. The device of claim 1, wherein said capacitive means comprises a first conductor and a second conductor disposed a distance from said first conductor, surfaces of said first and second conductor adapted to be exposed to fluid under test are coated with electrically insulating material, and wherein said surf-ace, on which said biochemical binding means is localized, is positioned between and remote from said first and second insulated conductor. 3. The device of claim 1, wherein said capacitive means comprises a first conductor and a second conductor disposed a distance from said first conductor, surfaces of said first and second conductor adapted to be exposed to fluid under test are coated with electrically insulating material, and wherein said electrically insulating layer forms said surface on which said biochemical binding means is localized. 4. The device of claim 1, wherein said surface, on which said biochemical binding means is localized, is a surface of an electrically insulating material adapted to be exposed to fluid under test. 5. The device of claim 1, wherein said biochemical binding means reversibly binds with said analyte in accordance with analyte concentration in said fluid, wherein a reduction of analyte concentration in said fluid results in fluid returning to said first volumetric region from said second volumetric region. 6. The device of claim 1, wherein said biochemical binding means comprises a layer of a binding agent specifically reactive with said analyte and adapted to form an analyte/binding agent bond. 7. The device of claim 6, wherein said biochemical binding means further comprises linking molecules for immobilizing said binding agent to said surface and extending said binding agent a distance removed from the fluid/surface interface. 8. The device of claim 6, wherein said binding agent is an affinity ligand selected ' to bind specifically to said analyte. 9. The device of claim 8, wherein said binding agent is a biospecific antibody. 10. The device of claim 9, wherein said analyte is selected from the group consisting of bacteria, viruses and antibodies. 11. The device of claim 1, wherein said responsive means further comprises a differential means for comparing capacitance changes detected by said responsive means with the average dielectric constant in said second volumetric region. 12. The device of claim 11, wherein said differential means includes: a reference capacitor means responsive to the average dielectric constant in said second volumetric region. 13. The device of claim 1, wherein said capacitive means comprises: a first conductor having an electrically insulating layer; a second conductor having an electrically insulating layer and disposed a distance from said first conductor; a means for generating said electric field between said first and second conductor; and, wherein said responsive means comprises a circuit means responsive to changes in capacitance between said first and said second insulated conductor. 14. The device of claim 13, wherein said first and second insulated conductors are positioned on a substrate to form an "open" face capacitor. 15. The device of claim 14, wherein said biochemical binding means is disposed on the surface of said "open" face capacitor. 16. The device of claim 13, wherein said first conductor comprises a plurality of fingers disposed on a substrate and extending a distance above said substrate, and wherein said second conductor comprises a plurality of fingers disposed on said substrate and extending a distance above said substrate, fingers of said second conductor are interdigitated with fingers of said first conductor, whereby channels are formed between said first and said second conductor. 17. The device of claim 16, wherein said a plurality of fingers are coated with an electrically insulating layer. 18. The device of claim 17, wherein said biochemical binding means is immobilized on said electrically insulating layer. 19. The device of claim 17, wherein said biochemical binding means is immobilized within said channels formed between said fingers of said first and second conductor. 20. The device of claim 17, wherein said biochemical binding means is immobilized on structures that are positioned within said channels formed between said fingers of said first and second conductors. 21. The device of claim 16, wherein said fingers of said first and second conductor are interdigitated. 22. The device of claim 11, wherein said first and second conductors are parallel conductive wires imbedded in a molded insulator, wherein said molded insulator is shaped to provide at least one channel positioned between and running parallel with said conductive wires, and wherein said biochemical binding means is immobilized within said at least one said channel. 23. The device of claim 13, further comprising a reference means responsive to the average dielectric constant of fluid in said second volumetric region. 24. The device of claim 23, wherein said reference means comprises a reference capacitor means responsive to changes in the dielectric constant of said fluid. 25. The device of claim 24, wherein said reference capacitor means comprises: a first reference conductor having an electrically insulating layer; - a second reference conductor having an electrically insulating layer and disposed a distance from said first conductor; a means for generating a reference electric field between said first and said electrical conductors, wherein said reference electric field has a higher average intensity in a first reference volumetric region in a lower average intensity in a second reference volumetric region; and, a reference circuit means responsive to changes in capacitance in said first reference volumetric region. 26. The device of claim 25, further comprising a "dummy" biochemical binding means, positioned in said first reference volumetric region, said "dummy" biochemical binding means is not biospecific to said analyte under test. 27. The device of claim 25, wherein a portion of said biochemical binding means is positioned within said first reference volumetric region of said reference capacitor means, and wherein a molecular sieve means encompasses said first and second reference volumetric regions of said reference capacitor means, said membrane means having a porous size selected to permit the passage of fluid molecules but to inhibit passage of analyte molecules into said first and second reference' volumetric region. 28. The device of claim 24, further comprising a differential means for comparing the capacitance detected by said responsive means with the capacitance detected by said reference capacitor means. 29. A device for detecting the presence of an analyte in a fluid, said device comprising a sensing capacitor adapted to be exposed to said fluid including: a first conductor coated with an electrically insulated layer; a second conductor coated with an electrically insulated layer and disposed a distance from said first conductor so that application of time-varying voltage across said first and second conductor will generate a time-varying electric field having a higher average field intensity in a first volumetric region localized near a surface and a lower average field intensity in a second volumetric region, fluid displaced from said first volumetric region will move into said second volumetric region; a biochemical binding means localized on said surface for concentrating analyte into said first volumetric region whereby fluid is displaced from said first volumetric region into said second volumetric region, said analyte having a different bulk dielectric constant from said fluid. 30. The device of claim 29, wherein said biochemical binding means comprises a layer of a binding agent specifically reactive with said analyte and adapted to form an analyte/binding agent bond. 31. The device of claim 30, wherein said biochemical binding means further comprises a linking molecule for immobilizing said binding agent onto said surface. 32. The device of claim 30, wherein said binding agen is an affinity binding agent selected to bind specifically to the analyte. 33. The device of claim 30, wherein said binding agen is a biospecific antibody. 34. The device of claim 30, wherein said first conductor comprises a plurality of fingers deposited on a substrate and extending a distance above said substrate, and wherein said second conductor comprises a plurality of fingers deposited on said substrate and extending a distance above said substrate, fingers of said second conductor are interdigitated with fingers of said first conductor, where channels are formed between said first and second conductor, and wherein said plurality of fingers are coated with an electrically insulating layer. 35. The device of claim 29, further comprising: a reference capacitor adapted to be exposed to said fluid including: a first reference conductor coated with an electrically insulating layer, and a second reference conductor coated with an electrically insulating layer and disposed a distance from said first conductor, wherein said first and second electrically insulating conductors are adapted to be exposed to said fluid and wherein application of a voltage across said first and second reference conductor will generate an electric field having higher field intensity in a first reference volumetric region and a lower field intensity in a second reference volumetric region. 36. The device of claim 35, further comprising a "dummy" biochemical binding means, positioned in said first reference volumetric region, said "dummy" biochemical binding means is not biospecific to said analyte under test. 37. The device of claim 35, wherein a portion of said biochemical binding means is positioned within said first reference volumetric region of said reference capacitor , and wherein a molecular sieve means encompasses said first and second reference volumetric regions of said reference capacitor, said membrane means having a pore size selected to permit the passage of fluid molecules but to inhibit passage of analyte molecules into said first and second reference volumetric region. 38. The device of claim 35, wherein said sensing capacitor and said reference capacitor are positioned on a substrate that is adapted to be exposed to said fluid under test. 39. The device of claim 35, wherein a mesh is operably associated with said substrate so that a small volume above said substrate containing said sensing and reference capacitors is isolated from large particles in the environment. 40. The device of claim 35, wherein said first reference conductor comprises a plurality of fingers disposed on a substrate and extending a distance above said substrate and wherein said second reference conductor comprises a plurality of fingers disposed on said substrate and extending a distance above said substrate, fingers of said first conductor are interdigitated with fingers of said second conductor, whereby channels are formed between said first and second conductor, and wherein said plurality of fingers are coated with an electrically insulating layer. 41. A method for detecting the presence of an analyte in a fluid, comprising the steps of: concentrating analyte onto a biochemical binding means, whereby said analyte displaces fluid from a volume adjacent to said biochemical binding means; and, detecting the average dielectric constant in said volume adjacent to said biochemical binding means. 42. The method of claim 41, wherein said detecting step further involves the steps of: generating a time-varying electric field having a higher average electrical field intensity in said volume adjacent to said biochemical binding means and a lower average field intensity in a second volumetric region, wherein fluid displaced by said analyte from said adjacent volume moves into said second volumetric region; and, sensing a change in capacitance as fluid moves from said adjacent volumetric region into said second volumetric region. 43. The method of claim 42, wherein said detecting step involves the further steps of: determining the average dielectric constant of said fluid; and, comparing said sensed capacitance with said average dielectric constant of said fluid. 44. A method for detecting the presence of an analyte in a fluid, comprising the steps of: generating a time-varying electric field within a volume of fluid under test by using a capacitor that produces a first volumetric region of higher electric field intensity localized near a surface and a second volumetric region of lower average electric field intensity; concentrating analyte from said fluid under test into said first volumetric region by localizing a biochemical binding means on said surface; providing a path for movement of fluid between said first volumetric region and said second volumetric region, wherein said fluid is displaced along said path as analyte is concentrated into said first volumetric region; and, sensing the capacitance of said capacitor, wherein relative analyte and fluid movement between said first volumetric region and said second volumetric region causes a change in said capacitance. 45. The method of claim 44, wherein said concentrating step comprises the step of reversibly binding said analyte onto said biochemical binding means in response to analyte concentration in fluid under test, wherein a reduction of analyte concentration in said fluid under test reduces the analyte concentrated by ■ said " biochemical binding means in said first volumetric region. 46. The method of claim 44, wherein said concentrating step comprises the step of binding said analyte onto a biochemical binding means biospecifically reactive with the analyte to form an analyte/biochemical binding means bond. 47. The method of claim 44, further comprises the step of determining the average dielectric constant of the fluid. 48. The method of claim 47, further comprising the step of comparing the sensed capacitance with the determined average dielectric constant of the fluid. 49. A device for detecting the presence of molecules of analyte in a fluid medium, said device comprising: a biochemical binding system positioned in a first volumetric region and comprising: first layer molecules immobilized on a surface within said first volumetric region, second layer binding agent molecules conjugated onto said immobilized first layer molecules, said binding agent molecules having the following properties: a.a dielectric constant different from said fluid, b.biospecifically reactive with both said immobilized first layer molecules and molecules of said analyte in said fluid, wherein exposure of said biochemical binding system to a fluid medium containing analyte molecules reduces the percentage of said binding agent molecules bound to said first layer molecules through the formation of binding agent/analyte complexes; and, a means responsive to the average dielectric constant i said first volumetric region. 50. The device of claim 49, wherein said responsive means comprises: a capacitor means for generating an electric field having a higher field intensity in said first volumetric region and a lower field intensity in a second volumetric region, wherein said first and second volumetric regions comprise a total volumetric area. 51. The device of claim 50, wherein said responsive means detects a change in the dielectric constant in said first volumetric region as said fluid moves into said first volumetric region as said binding agent/analyte pairs migrate from said first volumetric region into said second volumetric region. 52. The device of claim 51, wherein said first volumetric region is small relative to said second volumetric region, and wherein said surface within said first volumetric region is a short diffusion distance from said second volumetric region. 53. The device of claim 50, wherein said capacitor means comprises: a first conductor having an.elect ically insulating layer, and second conductor having an electrically insulating layer and disposed a distance from said first conductor; a means for generating said electric field between said first and second conductor; and, a circuit means responsive to changes in capacitance between said first and second insulating conductor. 54. The device of claim 53, wherein said first conductor comprises a plurality of fingers disposed on a substrate and extending a distance above said substrate, and wherein said second conductor comprises a plurality of fingers disposed on said substrate and extending a distance above said substrate, fingers of said second conductor are interdigitated with fingers of said first conductor, whereby channels are formed between said first and second conductor, and wherein said plurality of fingers are coated with an electrically insulating layer. 55. The device of claim 53, wherein said biochemical binding system is immobilized on said electrically insulating layer. 56. The device of claim 53, wherein said biochemical binding system is immobilized within said channels formed between said fingers of said "first and second conductor. 57. The device of claim 53, wherein said biochemical binding system is immobilized on ridges that are positioned within said channels formed between sail fingers of said first and second conductors. 58. The device of claim 53, wherein said fingers of said first and second conductors are interdigitated. 59. The device of claim 50, wherein said first and second conductors are parallel conductive wires embedded in a molded insulator, wherein said molded insulator is shaped to provide at least one channel position between and running parallel with said conductive wires, wherein said biochemical binding system is immobilized within said at least one channel. 60. The device of claim 50, further comprising. a reference means responsive to the average dielectric constant of a fluid in said second volumetric region. 61. The device of claim 60, wherein said reference means comprises a reference capacitor means responsive to changes of the dielectric constant in said fluid. 62. The device of claim 60, wherein said reference capacitor means comprises: a first reference conductor having an electrically insulating layer, a second reference conductor having electrically insulated layer and disposed a distance from said first conductor; a means for generating a reference electrical field between said first and second conductor, wherein said electrical field has a higher field intensity in a first reference volumetric region and a lower field intensity in a second volumetric region; and, a reference circuit means responsive to changes in capacitance between said first and second insulated reference conductors. 63. The device of claim 62, further comprising a "dummy" biochemical system, positioned in said first reference volumetric region, said "dummy" biochemical binding system comprising first layer molecules immobilized on a surface within said first reference volumetric region and second layer binding agent molecules conjugated onto said first layer molecules, wherein said second layer binding agent molecules are not biospecific to said analyte molecules. 64. The device of claim 62, further comprising a "dummy" biochemical system, positioned in said first reference volumetric region, said "dummy" biochemical binding system comprising first layer molecules immobilized on a surface within said first reference volumetric region, • said first layer molecules are not biospecific to said analyte molecules. 65. The device of claim 62, wherein a portion of said biochemical binding system is positioned within said first reference volumetric region of said reference capacitor means, and wherein a molecular sieve means encompasses said first and second reference volumetric regions of said reference capacitor means, said membrane means having a pore size selected to permit the passage of fluid molecules but to inhibit passage of analyte molecules into said first and second volumetric region. 66. The device of claim 62, further comprising a differential means for comparing the capacitance detected by said capacitive means with the capacitance detected by said reference capacitive means. 67. The device of claim 49, wherein said first layer molecules are selected from the group consisting of the analyte molecule under test, and analog molecules of said analyte molecules that are biospecific to said second layer binding agent molecules. 68. The device of claim 49, wherein said biochemical binding system further comprises linking molecule for immobilizing said first layer molecules onto said surface within said first volumetric region. 69. The device of claim 68, wherein said first layer molecules are covalently bound to said surface within said first volumetric region. 70. The device of claim 49, wherein said second layer binding agent molecules are biological molecules having an affinity to the analyte. 71. The device of claim 49, wherein said second layer binding agent molecules are selected from the group consisting of antibodies, lectins, enzymes and receptors. 72. The device of claim 49, wherein said first layer immobilized molecules are selected from the group consisting of antigens, haptens, polysaccharides, polyglycoproteins, glycolipids, enzyme inhibitors, enzyme substrates, neurotransmitters and hormones. 73. The device of claim 49, wherein said analyte is an antigen, and said second layer binding agent is an antibody biospecific to said antigen analyte, and wherein said first layer immobilized molecules are selected from the group consisting of said antigen analyte and analogs to said antigen analyte that are biospecific to said second layer binding agent molecules. 74. The device of claim 49, wherein said analyte is a hapten, and said second layer binding agent is an antibody biospecific to said hapten analyte, and wherein said first layer immobilized molecules are selected from the group consisting of said hapten analyte and analogs to said hapten analyte that are biospecific to said second layer binding agent molecules. 75. The device of claim 49, wherein said second layer binding agent molecules are a lectin that is specific to a group of analytes. 76. The device of claim 75, wherein said first layer immobilized molecules are selected from the group consisting of polysaccharides, glycoproteins and glycolipids. 77. The device of claim 49, wherein said second layer binding layer agent is an enzyme. 78. The device of claim 77, wherein said first layer immobilized molecules are selected from the group consisting of enzyme inhibitors and enzyme substrates. 79. The device of claim 49, wherein said second layer binding agent is a neuroreceptor. •80. The device of claim 79, wherein said first layer immobilized molecules are selected from the group consisting of neurotransmitters and hormones. 81. The device of claim 50, further comprising a membrane surrounding said total volumetric area, wherein said membrane has a plurality of pores adapted to pass analyte and fluid molecules. 82. The device of claim 81, wherein said pore size is selected to pass analyte and fluid molecules but to prevent second layer binding agent molecules from escaping from said total volumetric area. 83. The device of claim 82, wherein said pore size is chosen to selectively pass molecules below a certain size, wherein said membranes can selectively screen certain molecules from entering said total volumetric area. 84. A device for detecting the presence of an analyte in a fluid, said device comprising: a sensing capacitor adapted to be exposed to said fluid including: a first conductor coated with an electrically insulated layer; a second conductor coated with an electrically insulated layer and disposed a distance from said first conductor so that application of a time-varying voltage across said first and second conductor will generate a time-varying electric field having a higher field intensity in a first volumetric region and a lower field intensity in a second volumetric region, said first and second volumetric regions comprising a total volumetric region, a biochemical binding system positioned in said first volumetric region and comprising: first layer molecules immobilized on a surface within said first volumetric region, second layer binding agent molecules conjugated onto said immobilized first layer molecules, said binding agent molecules having the following properties: (a) larger in size than dominant fluid molecules and molecules of said analyte; (b) a dielectric constant different from said fluid, and (c) biospecifically reactive with both said immobilized first layer molecules and said molecules of said analyte in said fluid, wherein exposure of said biochemical binding system to a fluid medium containing analyte molecules displaces a percentage of said binding agent molecules from said biochemical binding system through competitive binding to form binding agent/analyte pairs, migration of said binding agent/analyte pairs from said first volumetric region to said second volumetric region changes the average dielectric constant in said first volumetric region. 85. The device of claim 84, wherein said first volumetric region is small relative to said second volumetric region, and wherein said surface within said first volumetric region is a short diffusion distance from said second volumetric region. 86. The device of claiπr 85, wherein fluid diffuses into said first volumetric region as said binding agent/analyte pairs migrate from said first volumetric region to said second volumetric region causing a change in the average dielectric constant in said first volumetric region. 87. The device of claim 84, wherein said first conductor comprises a plurality of fingers disposed on a substrate and extending a distance above said substrate, and wherein said second conductor comprises a plurality of fingers disposed on said substrate and extending a distance above said substrate, fingers of said second conductors are interdigitated with fingers of said first conductor, whereby channels are formed between said first and second conductor, and wherein said plurality of fingers are coated with an electrically insulating layer. 88. The device of claim 87, wherein said biochemical binding system is immobilized on said electrically insulating layer and within said channels. 89. The device of claim 84, wherein said first layer molecules are selected from the group consisting of analyte molecules under test, and analog molecules of said analyte molecules that are biospecific to said second layer binding agent molecules. 90. The device of claim 84, wherein said second layer binding agent molecules are biological molecules having an affinity to the analyte under test. 91. The device of claim 84, wherein said second layer binding agent molecules are selected from the group consisting of antibodies, lectins, enzymes and receptors. 92. The device of claim 84, further comprising a membrane means for isolating said total volumetric area from fluid outside said total volumetric area, wherein said membrane has a plurality of pores adapted to pass analyte and fluid molecules but to prevent second layer binding agent molecules from escaping from said total volumetric area. 93. The device of claim 84, further comprising: a reference capacitor adapted to be exposed to said fluid including: a first reference conductor coated with an electrically insulating layer, and a second reference conductor coated with an electrically insulating layer and disposed a distance from said first conductor, wherein said first and second electrically insulating conductors are adapted to be exposed to said fluid, application of a time- varying voltage across said first and second reference conductor will generate a time-varying electric field having a higher field intensity in a first reference volumetric region and a lower field intensity in a second reference volumetric region. 94. The device of claim 93, further comprising a "dummy" biochemical system, positioned in said first reference volumetric region, said "dummy" biochemical binding system comprising first layer molecules immobilized on a surface within said first reference volumetric region and second layer binding agent molecules conjugated onto said first layer molecules, wherein said second layer binding agent molecules are not biospecific to said analyte molecules. 95. The device of claim 93, further comprising a "dummy" biospecific system, positioned in said first reference volumetric region, said "dummy" biochemical binding system comprising first layer molecules immobilized on a surface within said first reference volumetric region, said first layer molecules are not biospecific to said analyte molecules. 96. The device of claim 93, wherein a portion of said biochemical binding system is positioned within said first reference volumetric region of said reference capacitor, and wherein a molecular sieve means encompasses said first 5 and second reference volumetric regions of said reference capacitor, said membrane mean's having a pore size selected to allow the passage of fluid molecules but to inhibit passage of analyte molecules into said first and second volumetric region. 97. The device of claim 93, wherein said first reference conductor comprises a plurality of fingers disposed on a substrate and extending a distance above said substrate and wherein said second reference conductor 5 comprises a plurality of fingers disposed on said substrate and extending a distance above said substrate, fingers of said first conductors are interdigitated with fingers of said second conductor, whereby channels are formed between said first and second conductor, and wherein said plurality ° of fingers are coated with an electrically insulating layer. 98. The device of claim 93, where said first and second conductor and said first and second reference conductor are positioned on a single substrate.

Inventors: NEWMAN ARNOLD L, NEWMAN, ARNOLD, L.
Applicants: UNIV JOHNS HOPKINS, THE JOHNS HOPKINS UNIVERSITY/APPLIED PHYSICS LABOR
Application year: 1986
Main classification: G01N33
IPC codes: G01N27, G01N33