|Número de publicación||USRE40198 E1|
|Tipo de publicación||Concesión|
|Número de solicitud||US 10/671,436|
|Fecha de publicación||1 Abr 2008|
|Fecha de presentación||25 Sep 2003|
|Fecha de prioridad||1 Jun 1998|
|También publicado como||CA2333686A1, CA2333686C, CA2333732A1, CA2333732C, CA2333875A1, CA2333875C, DE69902265D1, DE69902265T2, DE69902662D1, DE69902662T2, DE69917258D1, DE69917258T2, EP1084132A1, EP1084132B1, EP1084133A1, EP1084133B1, EP1084409A1, EP1084409B1, US6262264, US6294062, US6352824, US7045310, US20020090632, WO1999062918A1, WO1999062919A1, WO1999063346A1|
|Número de publicación||10671436, 671436, US RE40198 E1, US RE40198E1, US-E1-RE40198, USRE40198 E1, USRE40198E1|
|Inventores||Harvey B. Buck, Jr., Zhi David Deng, Eric R. Diebold|
|Cesionario original||Roche Diagnostics Operations, Inc.|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (54), Otras citas (23), Citada por (83), Clasificaciones (41), Eventos legales (4)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
This application claims benefit of provisional application 60/087,576 Jun. 1, 1998.
This invention relates to a method and device for detection and quantification of biologically significant analytes in a liquid sample. More particularly the invention is directed to a biosensor and method of using same for electrochemical immunoassays of multiple analyte species in a single liquid sample.
Therapeutic protocols used today by medical practitioners in treatment of their patient population requires accurate and convenient methods of monitoring patient disease states. Much effort has been directed to research and development of methods for measuring the presence and/or concentration of biologically significant substances indicative of a clinical condition or disease state, particularly in body fluids such as blood, urine or saliva. Such methods have been developed to detect the existence or severity of a wide variety of disease states such as diabetes, metabolic disorders, hormonal disorders, and for monitoring the presence and/or concentration of ethical or illegal drugs. More recently there have been significant advancements in the use of affinity-based electrochemical detection/measurement techniques which rely, at least in part, on the formation of a complex between the chemical species being assayed (the “analyte”) and another species to which it will bind specifically (a “specific binding partner”). Such methods typically employ a labeled ligand analog of the target analyte, the ligand analog selected so that it binds competitively with the analyte to the specific binding partner. The ligand analog is labeled so that the extent of binding of the labeled ligand analog with the specific binding partner can be measured and correlated with the presence and/or concentration of the target analyte in the biological sample.
Numerous labels have been employed in such affinity based sample analysis techniques, including enzyme labeling, radioisotopic labeling, fluorescent labeling, and labeling with chemical species subject to electrochemical oxidation and/or reduction. The use of redox reversible species, sometimes referred to as electron transfer agents or electron mediators as labels for ligand analogs, have proven to provide a practical and dependable results in affinity-based electrochemical assays. However, the use of electrochemical techniques in detecting and quantifying concentrations of such redox reversible species (correlating with analyte concentrations) is not without problem. Electrochemical measurements are subject to many influences that affect the accuracy of the measurements, including those relating to variations in the electrode structure itself and/or matrix effects deriving from variability in liquid samples.
The present invention relates to immunosensors based on direct electrochemical measurement of detectable species with microarray electrodes under bipotentiostatic control. An electrochemical label, for example as Oe mediator, is covalently attached to a peptide which has amino acid sequence of the binding epitope for the antibody. When indicator/peptide conjugate is bound to antibody, the indicator does not function electrochemically or it is said to be “inhibited”. The analyte present in sample will compete with indicator/peptide conjugate for the limited number of binding sites on the antibody. When more analyte is present, more free indicator/peptide conjugate will be left producing higher current at a sensor electrode, i.e., one of the working electrodes where measured events (oxidation or reduction) are taking place. In the opposite case, when less analyte is present, more indicator/peptide conjugate will be bound to antibody resulting less free conjugates and producing lower current levels at the working electrodes. Therefore the current detected at either one of the working electrodes will be a function of analyte concentration.
It is frequently desired to measure more than one analyte species in a liquid sample. Measurement of multiple species in a mixture has been achieved with photometry and fluoroescence, via selection of the appropriate wavelengths. Electrochemical measurements of a single species in a complex mixture are routinely made by selecting a potential at which only the desire species is oxidized or reduced (amperometry) or by stepping or varying the potential over a range in which only the desired species changes its electrochemical properties (AC and pulse methods). These methods suffer from disadvantages including lack of sensitivity and lack of specificity, interference by charging and matrix polarization currents (pulse methods) and electrode fouling due to the inability to apply an adequate overpotential. Moreover, electrochemical measurements are complicated by interference between the multiplicity of electroactive species commonly extant in biological samples.
Electrode structures which generate steady state current via diffusional feedback, including interdigitated array electrodes (IDAs) (
One embodiment of the present invention provides a method for measuring multiple analyte species in the same sample, and optimally on the same electrode structure, thus improving the accuracy of the relative measurements. This invention also provides an electrochemical biosensor with capacity to provide improved accuracy through the use of self-compensation. Analyte concentration can be measured/calculated from electrometric data obtained on the same liquid sample with the same electrode structure (the working electrodes), thereby minimizing perturbations due to variability in sample or electrode structure.
The various embodiments of this invention utilize the principle of diffusional recycling, where a diffusible redox reversible species is alternately oxidized and reduced at nearby electrodes, thereby generating a measurable current. As alternate oxidation and reduction is required for measurement, only electroactive species which are electrochemically reversible are measured thereby eliminating, or at least reducing, the impact or interference from non-reversible electroactive species in the sample. Redox reversible species having different oxidation potentials can be independently measured in a mixture by selecting and bipotentiostatically controlling the oxidizing and reducing potentials for neighboring electrode pairs so that only the species of interest is oxidized at the anode (the electrode with the more positive potential) and reduced at the cathode (the electrode with the less positive or negative potential). When the working electrodes (the anode/cathode arrays) are dimensioned to allow diffusional recycling of the redox-reversible-species at the selected oxidizing and reducing potentials appropriate for that species, a steady state current at the working electrodes where the measurable oxidative and reductive events are taking place, is quickly established through the sample and the electrode structure. The magnitude of the current is proportional to the concentration of the diffusible redox reversible species in the sample. When two or more redox reversible species are utilized, they are selected to have redox potentials differing by at least 50 millivolts, most preferably at least 200 millivolts, to minimize interference between one species and the other in measurements of the respective steady state currents.
Any electrode structure which allows for diffusional recycling to achieve steady state current in response to application of pre-selected species-specific anodic and cathodic potentials can be utilized in carrying out the invention. Suitable electrode structures include interdigitated array microelectrodes and parallel plate electrodes separated by distances within the diffusion distance of the respective redox reversible species. The electrode structures typically include a reference electrode (e.g., Ag/AgCl), at least two working electrodes (one at positive potential and another at a less positive or negative potential relative to the reference electrode), and optionally an auxiliary electrode for current control. In use, a programmable bipotentiostat is placed in electrical communication with the electrode structure for applying the respective anoidic and cathodic potentials specific for each of the respective redox reversible species utilized in the method/biosensor. Several novel osmium complexes have been developed for use as labels for preparing ligand analog conjugates having potential differences sufficient to allow the use of two osmium complexes (as opposed to an osmium complex and a ferrocene or other redox reversible label) in this invention.
Accordingly, one embodiment of the invention provides a device for detecting or quantifying one or more analytes in a liquid sample. The device comprises at least two redox reversible species having respective redox potentials differing by at least 50 millivolts, and an electrode structure for contact with the liquid sample. In one embodiment the device further comprises a chamber for containing the liquid sample, optionally dimensioned for capillary fill. The electrode structure includes a reference electrode and an anode and a cathode (working electrodes) dimensioned to allow diffusional recycling of the redox reversible species in the sample when a redox-reversible-species-dependent cathodic potential is applied to one working electrode and a redox-reversible-species-dependent anodic potential is applied to a second electrode to enable and sustain a measurable current through the sample. The device also includes conductors communicating with the respective electrodes for applying potentials and for carrying current conducted between the sample and the respective electrodes.
The device in accordance with this invention is typically utilized in combination with a meter which includes a power source, for example a battery, a microprocessor, a register for storing measured current values, and a display for reporting calculated analyte concentrations based on measured current values. The construction and configuration of such meters are well known in the art. Meters for use in accordance with the present device further comprise a bipotentiostat under control of the microprocessor or separately programmable to apply predetermined potentials to the device component microelectrode arrays during liquid sample analysis. Improvements in meter construction and design for biosensor systems are described in U.S. Pat. Nos. 4,999,632; 5,243,516; 5,366,609; 5,352,351; 5,405,511; and 5,48,271, the disclosures of which are hereby incorporated by reference.
In another embodiment of the invention there is provided a method for measuring the concentration of one or more analytes in a liquid sample. The method includes contacting a portion of the sample with pre-determined amounts of at least a first and second redox reversible species having a redox potential differing by at least 50 millivolts from that of each other species. Each respective species comprises a liquid sample diffusible conjugate of a ligand analog of an analyte in the liquid sample and a redox reversible label. The liquid sample is also contacted with a predetermined amount of at least one specific binding partner for each analyte to be measured. The diffusible conjugate is selected so that it is capable of competitive binding with the specific binding partner for said analyte.
The concentration of diffusible redox-reversible-species in the liquid sample is then determined electrochemically. The sample is contacted with an electrode structure, including a reference electrode and at least first and second working electrodes dimensioned to allow diffusional recycling of at least one of the diffusible redox-reversible-species in the sample, when a predetermined redox-reversible-species-dependent cathodic potential is applied to one working electrode and a predetermined redox-reversible-species-dependent anodic potential is applied to the second working electrode. Typically, a first cathodic potential is applied to the first working electrode and a first anodic potential is applied to the second working electrode to establish current flow through the sample due to diffusional recycling of the first redox-reversible-species without significant interference from the second redox-reversible-species. Current flow through one or more of the electrodes at the first anodic and cathodic potentials is measured. Similarly current flow responsive to application of second cathodic and anodic potentials to electrodes in contact with the sample is measured and correlated with measured current flows for known concentrations of the respective redox-reversible-species, said concentrations being proportionate to the respective analyte concentrations at a predetermined redox-reversible species-dependent potential (anoidic or cathodic). Alternatively, the potential of one of the working electrodes can be held constant and current flow is monitored as the potential of the other working electrode is varied and swept through the other redox-reversible species-dependent potential.
The reagent components for the invention, including the redox reversible species and the specific binding partners, can be provided in the form of a test kit for measuring the targeted analyte(s) in a liquid sample, either as separate reagents or, more preferably, combined as a multi-reagent composition, e.g. combined redox reversible species, combined specific binding partners, or combined redox reversible species and specific binding partners. The kit optionally, but preferably, includes an electrode structure dimensioned to allow diffusional redox recycling of diffusable redox reversible species in the liquid sample. The electrode structure includes conductors for connecting the structure bipotentiostat programmed to apply redox-reversible-species-dependent-anodic and cathodic potentials to the electrode structure and to sense and measure current flow, typically at one or both of the working electrodes, responsive to such applied potentials.
Also described herein is the preparation and use of electrochemically detectable osmium complexes and covalent conjugates of said complexes having oxidation potentials differing sufficiently to enable their use together in the respective method and device embodiments of the invention. Osmium labeled ligand analogs capable of binding to a specific binding partner of a biologically significant analyte are prepared. One group of electrochemically detectable conjugates comprise a bis(bipyridyl) imidazolyl chloroosmonium complex characterized by fast mediation kinetics and low redox potential (+15 mV vs. Ag/AgCl). Another group of osmium complex labeled, electrochemically detectable conjugates include tris(biphenyl) osmium complexes, which, like the bis(bipyridyl) imidazolyl chloroosmium complexes are characterized by fast mediation kinetics, but the tris(bipyridyl) complexes have a redox potential sufficiently different from the bis(pyridyl) imidazolyl chloroosmium complexes to allow their use together in the various embodiments of this invention to enable use of microelectrode arrays for measuring more than one analyte in a single liquid sample by concentration dependent currents amplified by diffusional redox recycling.
In one preferred embodiment of the invention at least one osmium complex conjugates is used in combination with another conjugated redox-reversible-species for the measurement of both glycosylated hemoglobin and hemoglobin in a lysed blood sample. One redox-reversible-species preferably comprises an osmium complex covalently linked to a ligand analog of either hemoglobin or glycosylated hemoglobin, and the second redox-reversible-species comprises a second redox reversible label covalently bound to a ligand analog of the other of the two target analytes. The method enables measurement of the concentration of both the glycosylated hemoglobin (HbAlc) and the concentration of either total hemoglobin or that of unglycosylated hemoglobin (HbA0) thereby enabling calculation of the results as a ratio of the two measurements (% HbAlc). It is advantageous to assay both HbAlc and total hemoglobin (or HbA0) using the same principle in a single sample.
One aspect of the invention is a method for measuring the concentration of one or more analytes in a liquid sample. The method enables two or more independent amperometric measurements of the sample on a single electrode structure.
The method of the invention has very broad applicability but in particular may be used to assay: drugs, hormones, including peptide hormones (e.g., thyroid stimulating hormone (TSH), luteinizing hormone (LH), follicle stimulating hormone (FSH), insulin and prolactin) or non-peptide hormones (e.g., steroid hormones such as cortisol, estradiol, progesterone and testosterone, or thyroid hormones such as thyroxine (T4) and triiodothyronine), proteins (e.g., human chorionic gonadotropin (hCG), carcino-embryonic antigen (CEA) and alphafetoprotein (AFP)), drugs (e.g., digoxin), sugars, toxins or vitamins.
The method can be performed on liquid samples comprising biological fluids such as saliva, urine, or blood, or the liquid sample can be derived from environmental sources. The liquid samples can be analyzed “as is,” or they can be diluted, buffered or otherwise processed to optimize detection of the targeted analyte(s). Thus, for example, blood samples can be lysed and/or otherwise denatured to solubilize cellular components.
The method can be performed using widely variant sampling handling techniques. Thus, the sample can be premixed with either or both of the specific binding partner for the targeted analytes and the redox reversible species prior to contacting the sample with the electrode structure, or the liquid sample, either neat or pre-processed, can be delivered to a vessel containing predetermined amounts of the redox reversible species and the specific binding partner for subsequent or simultaneous contact with the electrode structure. The order of introduction of the components into the sample is not critical; however, in one embodiment of the invention the predetermined amounts of the specific binding partners are first added to the sample, and thereafter, there is added the predetermined amounts of the redox reversible species. It is also possible to combine the predetermined amounts of the specific binding partners with the redox reversible species to form the respective complexes prior to combining those components with the liquid sample. In that latter case the redox reversible species will be displayed from its respective specific binding partner by the corresponding analyte to provide a concentration of the redox reversible species proportionate to the concentration of analyte in the liquid sample. The reagents, that is, the predetermined amounts of the specific binding partner of each analyte and the predetermined amounts of the corresponding redox reversible species can, for example, be deposited in a vessel for receiving a predetermined volume of the liquid sample. The liquid sample is added to the vessel, and thereafter, or simultaneously, the liquid sample is contacted with the electrode structure.
The electrode structure includes a reference electrode and at least first and second working electrodes dimensioned to allow diffusional recycling of the diffusible redox reversible species in the sample when predetermined redox-reversible-species-dependent-cathodic and anodic potential is applied to the working electrodes. The term “working electrode” as used herein refers to an electrode where measured events (i.e. oxidation and/or reduction) take place and resultant current flow can be measured as an indicator of analyte concentration. “Anodic potential” refers to the more positive potential (applied to the anode) and “cathodic potential” refers to the less positive or negative potential applied to the cathode (vs. a reference electrode). Electrodes dimensioned to allow diffusional recycling are well known in the art and are typically in the form of arrays of microdiscs, microholes, or microbands. In one embodiment the electrodes are in the form of an interdigitated arrangement of microband electrodes with micron or submicron spacing. Short average diffusional length and a large number of electrodes are desirable for effective current amplification by recycling of reversible redox species. The microelectrode arrays can be fabricated, for example, as pairs of interdigitated thin film metal electrodes in micron and submicron geometry arranged on an insulator substrate, for example, oxidized silicon. Each of the electrode fingers (
The electrode structure can be formed on an inner surface of a chamber for receiving the liquid sample, e.g., a cuvette, a capillary fill chamber, or other sample receiving vessel wherein the electrode structure can be contacted with the liquid sample. Alternatively, the electrode structure can form part of a probe for dipping into the liquid sample after the sample has been contacted with the predetermined amounts of the redox reversible species and the specific binding partners. The electrode structure is in contact with conductors that enable application of the respective cathodic and anodic potentials for carrying out the present method. The anodic and cathodic potentials are applied relative to a reference electrode component of the electrode structure using a bipotentiostat. The electrode structure can optionally include an auxiliary electrode for current control. The bipotentiostat is utilized to apply a first cathodic potential to a first working electrode and a first anodic potential to a second working electrode, the first cathodic and anodic potentials corresponding to those respective potentials necessary to establish current flow through the sample due to diffusional recycling of the first redox reversible species. Optionally the potential on one working electrode can be set at a first diffusible species dependent, anodic potential and current flow is measured as the potential of the other working electrode is swept through a potential corresponding to the predetermined diffusible species dependent cathodic potential (or vice versa).
The cathodic and anodic potentials appropriate for each reversible redox species can be readily determined by empirical measurement. The multiple redox reversible species used in performance of the method of this invention are selected to have redox potentials differing by at least 50 millivolts, more preferably at least 100 millivolts, more preferably at least 200 millivolts, from that of each other redox reversible species utilized in the method. The difference in redox potentials of the redox reversible species being used allow each species to be detected without significant interference from the second or any other redox reversible species in the liquid sample. A steady state current flow is rapidly established at each of the working electrodes following application of the anodic and cathodic potentials. Current flow can be measured at either or both working electrodes, and it is proportionate to the concentration of the recycling redox reversible species.
Second cathodic and anodic potentials are applied to the working electrodes wherein said second potentials correspond to those respective potentials necessary to establish current flow through the sample due to diffusional recycling of the second redox reversible species without significant interference from the first redox reversible species, and the resulting steady state current flow is measured. This step is repeated for each redox reversible species utilized in the method. The measured current flows are then correlated to known concentrations of the respective diffusible redox reversible species. Those concentrations are proportionate to the respective analyte concentrations.
The method steps can be conducted using a programed bipotentiostat to control potentials on the electrode structure in contact with the sample. The bipotentiostat can be included either in a desktop or hand-held meter further including means for reading values for steady state current, storing said values, and calculating analyte concentrations using a microprocessor programmed for making such calculations.
The redox reversible species utilized in the method comprise a liquid-sample-diffusible conjugate of a ligand analog of an analyte in the liquid sample and a redox reversible label. The term “ligand analog” as used in defining the present invention refers to a chemical species capable of complexing with the same specific binding partner as the analyte being measured and can include the analyte itself, provided that the molecular weight of the conjugate is less than about 50,000, more preferably less than about 10,000 Daltons. Most preferably the molecular weight of the conjugate of the ligand analog and the redox reversible label is between about 500 and about 5,000 Daltons. Low molecular weight redox reversible species are most desirable in view of the diffusion-based electrochemical detection technique utilized in carrying out the present method.
The term “redox reversible label” as used herein refers to a chemical species capable of reversible oxidation and reduction in a liquid sample. It can be in the form of an organic moiety, for example, a chemical group comprising a nitrosoaniline, a catechol, hydroquinone, or an aminophenol group. Alternatively, the redox reversible label can be an inorganic or organometallic species capable of undergoing reversible oxidation and reduction in a liquid sample. Such species may be, for example, complete molecules, portions of molecules, atoms, ions, or more particularly, ion complexes. Redox reversible labels are well-known in the art and include ligand complexes of transition metal ions, for example iron (ferrocene and ferrocene derivatives), ruthenium and osmium.
The relative amounts of the first and second redox reversible species and the respective specific binding partners for the targeted analytes to be measured in the method can be determined empirically. They are dependent on the concentration ranges of the targeted analyte, and the binding stoichiometry of the specific binding partner, the binding constant, the analyte and the corresponding redox reversible species. The amounts of each reagent appropriate for each analyte being measured can be determined by empirical methods.
The redox reversible species typically comprises a conjugate of a ligand analog of an analyte in a liquid sample and a redox reversible label. The conjugate is prepared by linking the ligand analog to the label either covalently through bifunctional linking agents or by combination of covalent linkages and art-recognized specific binding entities (for example, biotin-avidin).
In one embodiment of the invention the specific binding partner for each analyte is an antibody and the ligand analog is selected so that it binds competitively with the analyte to the antibody. There are, however, other examples of ligand-specific binding partner interactions that can be utilized in developing applications of the present method. Examples of ligands and specific binding partners for said ligands are listed below.
Specific Binding Partner
Antigen (e.g., a drug substance)
Complementary polynucleotide strand
Enzyme cofactor (substrate)
Enzyme cofactor (substrate)
The term “antibody” refers to (a) any of the various classes or subclasses of immunoglobulin, e.g., IgG, IgM, derived from any of the animals conventionally used, e.g., sheep, rabbits, goats or mice; (b) monoclonal antibodies; (c)intact molecules or “fragments” of antibodies, monoclonal or polyclonal, the fragments being those which contain the binding region of the antibody, i.e., fragments devoid of the Fc portion (e.g., Fab, Fab1, F(ab′)2) or the so-called “half molecule” fragments obtained by reductive cleavage of the disulfide bonds connecting the heavy chain components in the intact antibody. The preparation of such antibodies are well-known in the art.
The term “antigen” used in describing and defining the present invention includes both permanently antigenic species (for example, proteins, peptides, bacteria, bacteria fragments, cells, cell fragments, drug substances, and viruses) and haptans which may be rendered antigenic under suitable conditions.
In one embodiment of the invention there is provided a method for measuring two proteinaceous analytes in a liquid sample wherein the ligand analog component of the first redox reversible species is a peptide comprising an epitope of a first analyte and the ligand analog component of a second redox reversible species is a peptide comprising an epitope of a second analyte. One specific binding partner utilized in the method is an antibody recognizing the epitope of the first analyte, and the other specific binding partner is an antibody recognizing the epitope of the second analyte. In another application of the present method two independent measurements are performed on a single analyte in a liquid sample. In that embodiment the respective ligand analog component of the first and second redox reversible species are different ligand analogs of the targeted analyte. Where the targeted analyte is a proteinaceous compound, the ligand analog component of the first redox reversible species is a peptide comprising a first epitope of the analyte, and the ligand analog of the second redox reversible species is a peptide comprising a second epitope of the analyte, and the specific binding partners are first and second antibodies, each recognizing respective first and second analyte epitopes.
In one preferred embodiment of the invention, at least one of the redox reversible labels is an osmium complex. In another embodiment, both redox reversible labels are osmium complexes, each having an oxidizing potential difference of at least 50, most preferably at least 200 millivolts. Illustrative of the redox reversible osmium complexes for use in this invention are complexes of the formula
R and R1 are the same or different and are 2,2′-bipyridyl, 4,4′-disubstituted-2,2′-bipyridyl, 5-5′-disubstituted,-2,2′-bipyridyl, 1,10-phenanthrolinyl, 4,7-disubstituted-1,10-phenanthrolinyl, or 5,6-disubstituted-1,1 0-phenanthrolinyl, wherein each substituent is a methyl, ethyl, or phenyl group,
R and R1 are coordinated to Os through their nitrogen atoms;
q is 1 or 0;
R7 is B-(L)k—Q(CH2)i—;
R2 is hydrogen, methyl, or ethyl when q is 1, and R2 is B—(L)k—Q(CH2)i—when q is 0;
wherein in the group B—(L)k—Q(CH2)i—Q is O,S, or NR4 wherein R4 is hydrogen, methyl or ethyl;
—L—is a divalent linker;
k is 1 or 0;
i is 1, 2, 3, 4, 5 or 6; and
B is hydrogen or a group comprising a ligand capable of binding to a specific binding partner;
Z is chloro or bromo;
m is+1 or+2;
X is a mono- or divalent anion, e.g., chloride, bromide, iodide, fluoride, tetrafluoroborate, perchlorate, nitrate, sulfate, carbonate, or sulfite;
Y is monovalent anion, e.g., chloride, bromide, iodide, fluoride, tetrafluoroborate, perchlorate or nitrate; and
n is 1 or zero,
provided that when X is a divalent anion, n is zero,
and when m is 1, n is zero and X is not a divalent anion.
Another redox reversible osmium complex for use in the present method is a compound of the formula
R and R1 are the same or different and are 2,2′-bipyridyl, 4,4′-disubstituted-2,2′-bipyridyl, 5-5′disubstituted,-2,2′-bipyridyl, 1,10-phenanthrolinyl, 4,7-disubstituted-1,10-phenanthrolinyl, or 5,6-disubstituted-1,10-phenanthrolinyl, wherein each substituent is a methyl, ethyl, or phenyl group,
R5 is 4-substituted-2,2′-bipyridyl or 4,4′-disubstituted-2,2′-bipyridyl wherein the substituent is the group B—(L)k—Q(CH2)i—and the 4′-substituent is a methyl, ethyl or phenyl group;
R, R1 and R5 are coordinated to Os through their nitrogen atoms;
Q is O, S, or NR4 wherein R4 is hydrogen, methyl or ethyl;
—L—is a divalent linker;
k is 1 or 0;
i is 1, 2, 3, 4, 5 or 6;
B is hydrogen or a group comprising a ligand capable of binding to a specific binding partner;
X and Y are anions selected from monovalent anions, e.g., chloride, bromide, iodide, fluoride, tetrafluoroborate, perchlorate, and nitrate and divalent anions, e.g., sulfate, carbonate or sulfite wherein x and y are independently 0, 1, 2, or 3 so that the net charge of XxYyis−2 or−3.
Redox reversible conjugate species of each of those formulas are prepared from the corresponding compounds wherein K is O and B is hydrogen by reacting such compounds with either a hetero functional crosslinker of the formula S—L′—T wherein L′ is a divalent linker and S and T are different electrophilic groups capable of reacting with a nucleophilic group to form a covalent bond, or with a homofunctional crosslinker of the formula S—L′—T wherein L′ is a divalent linker and S and T are the same electrophilic groups capable of reacting with a nucleophilic group to form a covalent bond. The resulting products are then reacted with ligand analogs using classical coupling reacting conditions to product the conjugate species. The oxidizing potentials of the respective bis(pyridyl) and tris(bipyridyl)osmium complexes defined above is such that the respective complexes can be used as reversible redox labels for the respective redox reversible species in performance of the method.
In another embodiment of the invention there is provided a device for detecting or quantifying one or more analytes in a liquid sample. The device comprises
The device can be constructed using procedures and techniques that have been previously described in the art for construction of biosensors employing electrometric detection techniques. Thus, for example, the device can include a chamber that has a receiving port, and the chamber is dimensioned so that it fills by capillary flow when the liquid sample is contacted with the sample receiving port. The electrode structure can be formed on a plate that defines a wall of the chamber so that the electrode structure will contact a liquid sample in the chamber. Thus, for example, the device can be constructed using the general procedures and designs described in U.S. Pat. No. 5,141.868, the disclosure of which is expressly incorporated herein by reference. The features of the present invention can also be incorporated into other electrochemical biosensors or test strips, such as those disclosed in U.S. Pat. Nos. 5,120,420; 5,437,999; 5,192,415; 5,264,103; and 5,575,895, the disclosures of which U.S. Pat. are expressly incorporated herein by reference. The device can be constructed to include the predetermined amounts of the redox reversible species and the specific binding partners. For example, a mixture of such reagents can be coated onto a wall of the sample chamber in said device during device construction, so that the liquid sample is contacted with the reagent mixture as it is delivered into the chamber for containing the sample. In one embodiment the device is constructed for quantifying a first analyte and a second analyte in liquid sample. The device comprises two redox reversible species, a first redox reversible species comprising a conjugate of a ligand analog of the first analyte and a second redox reversible species comprising a conjugate of a ligand analog of the second analyte, and a specific binding partner for each analyte so that each of said analyte analog conjugates are capable of binding competitively with its respective analyte to a specific binding partner.
In one device embodiment of this invention the device further comprises a bipotentiostat in electrical communication with the conductors for applying a redox-reversible-species-dependent-cathodic potential to one working electrode and a redox-reversible-species-dependent-anodic potential to a second working electrode. The biopotentiostat can be programmed to apply a sequence of potentials to the respective working electrodes. More particularly, the bipotentiostat can be programmed to apply first cathodic potential to a first working electrode and a first anodic potential to a second working electrode, said first anodic and cathodic potentials corresponding to those potentials necessary to establish current flow to the sample due to diffusional recycling of the first redox reversible species. The bipotentiostat is also programmed to apply a second cathodic potential to said first working electrode and a second potential to the second anodic electrode, said second cathodic and anodic potentials corresponding to those potentials necessary to establish current flow through the sample due to diffusional recycling of the second redox reversible species. In an alternate embodiment the device includes first and second redox reversible species, and at least first and second electrode structures for contact with the liquid sample in the chamber, each of said electrode structures comprising a microarray of working electrodes, and means for switching the bipotentiostat between the first and second electrode structures. In preferred device embodiments there is provided means for measuring current flow through the sample at each of the first and second potentials and preferably storing values for said current flows in a register coupled to a microprocessor programmed to calculate analyte concentrations based on said values.
In still another embodiment of the present invention there is provided a kit for measuring the concentration of one or more analytes in liquid sample. The kit comprises
In one embodiment, the redox reversible species are mixed as a novel composition for contact with the liquid sample. In another embodiment each of the redox reversible species and the specific binding partner for each analyte is mixed as a novel composition for contact with the liquid sample. Preferably, the redox reversible label of at least one of the redox reversible species comprises an osmium complex.
The Os mediator bis(bipyridyl) imidazolyl chloroosmium has been shown to be an excellent electron mediator for many oxido-reductase enzymes (U.S. Pat. No. 5,589,326). It has fast mediation kinetics (about 500 times faster than ferricyanide with glucose oxidase) and a relatively low redox potential (+150 mV vs. Ag/AgCl). It has also very fast electron transfer rate at electrode surface. More importantly, the organic ligands on Os mediator can be functionalized so that it can be covalently linked to other molecules without detrimental effects on redox properties of the Os center. These unique properties of Os mediator make it an ideal electrochemical indicator for sensors based on immunoaffinity.
Os mediators with these new ligands were synthesized using the same procedure used for Os free mediator. Their synthesis consists of two major process steps as outlined below. Details of these processing steps are described below.
The first process step involves the synthesis of Os intermediate, cis-bis(2,2′-bipyridyl) dichloroosmium(II), from commercially available osmium salt using the following scheme. The intermediate product is isolated through recrystallization in an ice bath.
K2OsIVCl6+2bpy DMF [OsIII(bpy)2Cl2]Cl+2KCl
2[OsIII(bpy)2Cl2]+Na2S2O4+2H2O 0° C
The second process step involves the reaction between Os intermediate and histamine or 4-imidazoleacetic acid (or a substituted bipyridine for preparation of the tris(bipyridyl) complexes) to produce Os mediators with the appropriate “handle”. The desired product is then precipitated out from solution by addition of ammonium tetrafluoroborate.
These Os mediators can also be easily converted to oxidized form, i.e. Os(III) using nitrosonium tetrafluoroborate. However, this is unnecessary since the Os revert back to reduced form anyway at alkaline conditions during conjugation reactions. And it does not require oxidized form of Os(III) for the detection on the biosensor.
1. Interdigitated array microelectrodes (IDA) are produced through photolithographic means by art-recognized methods, (See W 97/34140; EP 0299,780; D. G. Sanderson and L. B. Anderson, Analytical Chemistry, 57 (1985), 2388; Koichi Aoki et al., J. Electroanalytical Chemistry, 256 91988) 269; and D. Niwa et la., J. Electroanalytical Chemistry, 167 (1989) 291. Other means which are standard in lithographic processing may also be used to produce the desired patterns of a conductor on insulator substrate.
2. Reversible mediators are selected from those described herein and those described references (U.S. Pat. Nos.4,945,045 and 5,589,325, the disclosures of which are incorporated herein by reference). Preferably two different mediators are selected with potentials which differ by at least 100 mV, more preferably at least 200 mV. Examples of suitable mediators include the Os(bipy)ImCl described herein and in U.S. Pat. No. 5,589,326, the disclosure of which is incorporated herein by reference, and ferrocene, described in U.S. Pat. No. 4,945,045 and EP 0142301, the disclosures of which are incorporated herein by reference. Mixtures of these mediators are made in aqueous solution, for example phosphate-buffered saline (PBS). Concentrations between about 1 uM and 1000 uM may conveniently be measured.
3. The IDA is connected to a bipotentiostat, an instrument capable of controlling the potential of two separate electrodes. Also provided is a reference electrode. This nonpolarizable electrode serves as the reference for the two applied potentials and may also serve as the counter electrode. Any non-polarizable electrode may be used, for example Ag/AgCl, such as may be obtained from ABI/Abtech. An auxiliary electrode can also be used for controlling current flow through the working electrodes. The mixtures are placed on the IDA electrode and the reference electrode also contacted with the mixture, or the IDA along with the reference electrode may be dipped into the mixture.
4. To measure Mediator 1 (Os(bipy)21mCl) A cathodic potential is applied to one set of fingers of the IDA which is capable of reducing mediator 1 (ca−50 mV vs. Ag/AgCl.) An anodic potential is applied to the other set of finger of the IDA which is capable of oxidizing mediator 1 but not mediator 2 (or any other mediators) (ca 250 mV vs Ag/AgCl). After a short time (msec to sec), a steady state current will be measurable which is dependent only on the concentration of mediator 1.
5. To measure Mediator 2 (Ferrocene) A cathodic potential is applied to one set of fingers of the IDA which is capable of reducing mediator 2 but not mediator 1 (ca 250 mV vs. Ag/AgCl.) An anodic potential is applied to the other set of fingers of the IDA which is capable of oxidizing mediator 2 (ca 550 mV vs Ag/AgCl). After a short time (msec to sec), a steady state current will be measurable which is dependent only on the concentration of mediator 2.
1. IDA electrodes are provided as in Paragraph A above.
2. Conjugates of mediators 1 and 2 and haptens or specific binding members are provided using art-recognized procedures for covalent coupling using either a homo-functional or hetero-functional linker. Specifically, a synthetic peptide corresponding to the N-terminal sequence of the β-chain of HbAlc is conjugated to the osmium complex. Similarly, a synthetic peptide corresponding to the N-terminal sequence of HbA0 is conjugated to a second mediator, for example ferrocene.
3. Antibodies for the analytes (HbAlc and HbAO) which react specifically with the N-terminal peptides which have been incorporated into the conjugate are provided by standard methods for producing polyclonal antibodies. In this case, sheep were immunized with carrier proteins to which were conjugated the synthetic peptide sequences for HbAlc and HbA0. Following the appropriate immunization schedule, the sheep were bled, and the antibody isolated from the blood via ion exchange chromatography, followed by immunosorbent purification on a column of the same N-terminal peptide with a different linker.
4. Appropriate stoichiometry of the reaction was determined for the two reactions independently by methods standard for immunoassay development. A solution containing a fixed amount of labeled conjugate was mixed with a solution with varying amounts of antibody, and, following an appropriate incubation period, the amount of free conjugate remaining was measured on the IDA electrode using the procedure described above. The amount of antibody just sufficient to achieve maximum inhibition of the conjugate (ca>80%) was selected.
5. Reagent solution 1 was made containing a mixture of the two conjugates in the appropriate concentrations. Reagent solution 2 was made containing a mixture of the two antibodies in the amounts determined above. A blood sample was diluted ca 20-fold in a solution of 25mM citric acid/0.5% Brij-35. Following a 30 second incubation to allow for lysis and denaturation of the hemoglobin, to 66 uL of this diluted sample was added 33 uL of 1 M phosphate buffer, to adjust the pH back to neutral. 30 uL of antibody solution 2 was added, and the mixture allowed to incubate 30 sec. Then 30 uL of conjugate solution 1 was added, and the mixture measured on the IDA electrode. The concentration of HbAlc in the sample is related to the current measured from Mediator 1, and the concentration of HbA0 is related to the current from Mediator 2. The %HbAlc in the sample is related to the ratio of the measured amounts of Mediator 1 and Mediator 2.
Hemoglobin Alc is a specific glycohemoglobin in which the glycosylation takes place at the N-terminal of hemoglobin β-chain. The antibody binds specifically to HbAlc has an epitope sequence of Gluc-Val-His-Leu-Thr. To facilitate conjugation to other molecules, a nonnative amino acid has been added to the sequence e.g., Cys, Lys, or Lys-MH, to produce Alc peptides including: 1) Gluc-Val-His-Leu-Thr-Lys-MH; 2) Gluc-Val-His-Leu-Thr-Lys; 2) Gluc-Val-His-Leu-Thr-Cys.
HbAlc assay requires measuring both Al c concentration and total hemoglobin concentration and reports the results as a ratio of these two measurements (% HbAlc). It is advantageous to assay both Alc and total hemoglobin using same principle because ratioing would minimize biases due to environmental effects. Thus antibody has been raised to bind specifically to hemoglobins with unglycosylated N-terminus, i. e. with an epitope sequence of Val-His-Leu-Thr. Similarly, nonnative amino acid is added to the sequence to facilitate conjugation. The peptides used for total hemoglobin measurement is termed as AO peptide. AO peptides that have been used in the preparation of Os mediator-peptide conjugates include Val-His-Leu-Thr-Cys and Val-His-Leu-Thr-Lys.
There are many types of conjugation chemistry that can be employed to link Os mediator to a peptide. The following two conjugation chemistries employed for the preparation of Os mediator-peptide conjugates have also been commonly used for preparing protein conjugates: 1) formation of amide bond by reactive ester with primary amine; 2) formation of thioether bond by maleimide with sulfhydryl group. Amide bond is preferred over thioether bond because amide bond is generally more stable. Based the preferred conjugation chemistry, the ligand on Os mediator can be functionalized with either a primary amine group or a carboxylic acid group. The best location for these functional groups is believed to be the C-4 or C-5 positions on the imidazole ligand of Os mediator, however, functionalization through the non-Os-complexed imidazole ring nitrogen atom can also be carried out. Two different functionalized Os mediators were synthesized as described above.
Os mediator (a) was formed with histamine while Os mediator (b) was formed with imidazolacetic acid. However, it was found that the imino nitrogen of the imidazole ring interferes with the activation of carboxylic acid group to reactive ester (i.e., N-hydroxysuccinimide ester) using carbodiimide. Thus, use of carboxylic acid functionalized Os mediator in the synthesis of Os mediator-peptide conjugates gave much less favorable results.
The amine group on histamine ligand of Os mediator readily reacts with N-hydroxysuccinimide (NHS) ester to form amide bond. Two types of crosslinkers have been employed to link Os mediator to peptides, (a) heterofunctional crosslinker, having a NHS ester at one end and the other end has a maleimide or a sulthydryl group; and (b) homofunctional crosslinker, e.g. both ends have NHS esters.
In the case of heterofunctional crosslinker, the crosslinker is first reacted with Os mediator with histamine ligand (Os histamine) at 1:1 molar ratio. One particular point needs to be noted here. Os mediator in oxidized form, i.e. Os(III), can instantly oxidize sulfhydryl group to form disulfide bond. It is importnat to keep Os center in the reduced form by addition of a small amount of reductant such as sodium dithionite during the conjugation processes. The reaction progress can be monitored by analytical reverse-phase HPLC on a C 18 column. Then the Os mediator-crosslinker adduct is isolated via preparative HPLC and the collected fraction is subsequently freeze-dried. Finally, the Os mediator-crosslinker adduct is reacted with the appropriate peptide to form Os mediator-peptide conjugate. Again, the product is isolated by collecting appropriate fraction in preparative HPLC and the collected fraction is then freeze-dried.
Two different heterofunctional crosslinkers have been used for the synthesis of Os mediator-peptide conjugates. SMCC (succinimidyl 4-[N-maleimidomethyl]cyclohexane-1-carboxylate) is used for cystein-containing peptide, while SATA (N-succinimidyl S-acetylthioacetate) is used for maleimide-containing peptide. Three Os mediator-peptide conjugates (two with Alc peptide and one with A0 peptide) have been made using heterofunctional crosslinkers and their structure are shown below: (a) Os-SMMC-A1c; (b) Os-SATA-A1c, and (c) Os-SATA-AO.
However, it has been found that these conjugates were not stable when they were stored as solutions. Analytical HPLC results indicated that these conjugates degrade. Mass spectroscopy confirmed that the instability is due to splitting of thioether bond present in these conjugates.
In order to avoid thioether bond in the conjugate, homofunctional crosslinker containing two NHS esters was used instead to prepare the conjugates. The crosslinker used was DSG (disuccinimidyl glutarate). In order to prevent the formation of crosslinked Os mediator, i.e. Os-crosslinker-Os, a large excess of homofunctional crosslinker was used in the reaction with Os histamine at 4:1 molar ratio. Under this condition, only the desired product, i.e. Os-crosslinker, was formed. The Os-DSG-Alc conjugate was similarly prepared using the procedure described earlier.
The preparation of analogous Os-DSG-Ao conjugate requires and extra step since the unglycated N-terminal amine of HbAAo peptide is also reactive toward NHS ester. In this case, the N-terminal amine of HbAo peptide is first protected by either a base-labile Fmoc1 or an acid-labile Boc2 group. After reacting with Os-DSG adduct to form Os-DSG-Ao conjugate, the protecting group is then cleaved using appropriate deprotection method (adding base for Fmoc or acid for Boc). The peptides prepared by solid-phase peptide synthesis already have N-terminal Fmoc protecting groups. The protecting groups are usually removed prior to cleavage of peptide from the resin beads, but they can also be left on if so desired. The HbAo peptide from Zymed has an intact Fmoc protecting group at N-terminus. Using this strategy the Os-DSG-Ao conjugate was successfully synthesized.
Many analytes cannot be assayed using enzyme-based sensors. They require the development of affinity biosensors or immunosensors which are based on the selective binding of antigens to antibodies. The key to the detection of this binding event on electrochemical sensors is the inclusion of antigens labeled with redox labels.
Bis(2,2′-bipyridyl) imidazolyl chloroosmium, a.k.a. Os mediator, possesses many properties that make it an excellent redox label for this purpose. In addition, a “handle” for linking it covalently to antigens can be added on without affecting its redox properties.
Several assay schemes can be used in affinity biosensors including, i) competitive binding assay (labeled antigen is competing for a limited number of binding sites); ii) sequential binding assays (labeled antigen is bound to excess binding sites); iii) heterogeneous assay (uses a separation step to separate bound and free labeled antigens); and iv) homogeneous assay (no separation step). The steps involved in a homogeneous sequential binding assay include binding the analyte to an antibody. The labeled antigen (analyte analog) binds to the remaining binding sites on the antibody. Finally the leftover free labeled antigen is detected at electrode surface. The resulting current will be a function of the amount of analyte present.
The detection of free labeled antigens can be achieved using either direct detection or amplified detection methods. Direct detection requires the use of advanced electrochemical techniques such as ac voltammetry, differential pulse voltammetry, square wave voltammetry or ac impedance in order to reach a sensitivity of 5 μM or less. Amplified detection methods use dc amperometry with amplification through reaction with enzyme or chemical reductants or by using interdigital array (IDA) microelectrodes. The preferred detection method is amplified amperometry through cycling of free Os mediator label by using IDA microelectrodes in accordance with this invention.
All HPLC analysis were performed using a Beckman System Gold HPLC system consists of a 126 pump module and a 168 diode array detector module.
Stationary phase is a Vydac analytical reverse-phase C18 analytical column. Other parameters are listed below.
Peak λ (nm)
Peak λ (nm)
Elution time = 32.1 min
m+/e = 434.2
Elution time = 27.5 min
m+/e = 382.8
Elution time = 27.1 min
m+/e = 429.2 and 859.6
elution time = 27.6 min
m+/e = 559.1 and 838.5
elution time = 27.6 min
m+/e = 480.5 and 534.4
elution time = 27.9 min
m+/e = 360.7 and 720.5
elution time = 23.5 min
m+/e = 501.8 and 752.8
elution time = 23.2 min
m+/e = 447.4 and 670.3
Potassium hexachloroosmium was reacted with 4,4′-dimethyl-2,2′-dipyridyl at 1:2 molar ratio by refluxing in DMF. The potassium chloride preparative was filtered and the dimethyl-bipyridyl dichloroosmium complex was reduced from+3 oxidation state to+2 oxidation state using excess sodium dithionite. The product was recrystallized in DMF/water mixture at 0° C. and recovered by filtration.
4,4′-Dimethyl-2,2′-bipyridyl dichloroosmium was reacted with 4-methyl-4′-carboxylpropyl-2,2′-dipyridyl by refluxing in ethylene glycol. The solvent was removed by rotary evaporation. The product was dissolved in DMF and precipitate in ethyl ether. The product was dried in a vacuum oven overnight.
Analyticals: Product and intermediate product were analyzed by HPLC and mass spectroscopy for purity and identity of the compound.
Os(dm-bpy)2Cl2: Theoretical MW=629.6, MS showed 8 isotope peaks with most abundant peak at 630. HLPC elution time at 29.94 min with a purity of 90%+
Os(dm-bpy)2(mcp-bpy): MS confirmed the MW at 814.5 and HPLC showed a purity greater than 85%.
The carbonyl group was activated by reacting the above Os complex with dicyclohexylcarbodiimide in the presence of N-hydroxysuccinimide. The active ester Os complex was isolated using preparative HPLC method and then reacted with amine-containing biotin to form the final conjugate.
Os(bipy)HisCl-DSG-HbAlc was prepared as described above.
Ferrocene-AMCHA-DADOO-biotin was prepared from ferrocene monocarboxylic acid, the crosslinker aminomethylcyclohexylic acid, the chain extender 1,8-diamino-3,6-DiOxoOctane and biotin as described elsewhere.
Mixtures of the two conjugates were prepared to evaluate the ability of the method of the invention to independently measure the concentration of the conjugates, and make corrections for variations in reagent amounts, electrode response, and environmental conditions.
The following matrix of solutions was prepared in 10 mM phosphate buffer with 150 mM NaCl and 0.5 % Brij-35, a non-ionic surfactant.
An Interdigitated array (IDA) microelectrode was fabricated according to the procedures described. In addition to the IDA, the chip had a silver/silver chloride electrode on the surface to function as the reference electrode and counter electrode. This electrode was produced with the same lithographic process, and then electroplated with silver and silver chloride according to standard techniques. The IDA was connected to a bipotentiostat capable of controlling the potential relative to the reference and measuring the current at each of the electrodes of the IDA. Aliquots of the solutions were placed onto the surface of the chip, such that the IDA and the reference electrodes were covered.
Measurements were made by first applying−100 mV (vs. Ag/AgCl) to one electrode of the IDA, and 200 mV to the other electrode for a period of 30 seconds. At this time, current was measured at each electrode. Then 200 mV was applied to one electrode, and 550 mV to the other. After 30 seconds, current was again measured. See
In this experiment, it was demonstrated that by making a mixture of known concentrations of two different mediators, and measuring different dilutions of that mixture by the method of the invention, the ratio of the concentrations of the mediators remains constant. (Internal standard application).
The same two mediator conjugates wee used as in Part 1. ( Os-DSG-Alc and Fc-Bi).
From a solution containing 40 uM of each conjugate, solutions containing 27 uM, 32 uM, and 36 uM of each conjugate were prepared in the same buffer ( PBS/Brij).
The solutions were measured as in the previous example. Each solution was measured on 5 different IDA electrodes. The results are presented as the means, standard deviations, and coefficient of variation for each solution separately, and for all solutions pooled over all electrodes.
This example clearly demonstrates that the internal standard effect of measuring two conjugates or mediators and calculating the ratio gives significantly improved precision of measurement, not only within each solution (compensation for variation between electrodes) but over all solutions (compensation for variation in sample dilution or amount).
It was desired to show the effectiveness of the method in compensating for environmental influences such as Temperature variation on the accuracy or the measurement.
The same two conjugates were prepared in solution at 40 uM as before. They were measured as before on IDA electrodes, either at room temperature or warmed to 35-40° C. on a heated metal plate prior to the measurement. The solutions were also warmed to 37° C. prior to application to the electrodes.
Ratio of response
As demonstrated by the results, the measured values increase by almost 50 % in the case of the warmed samples, which would lead to a large measurement error. However the use of the internal standard and ratio calculation effectively eliminates the temperature dependent of the result.
The goal of all diabetic therapy is to maintain a near normal level of glucose in the blood. Home blood glucose kits are available to monitor the current glucose values and are valuable for diabetics to adjust day to day insulin doses and eating habits. Unfortunately, since the tests only measures a point in time result, it does not tell them the overall effectiveness of their actions in maintaining glycemic control. Measurement of glycosylated hemoglobin is now becoming widely accepted as an index of mean blood glucose concentrations over the preceding 6-8 weeks and thus provides a measure of the effectiveness of a diabetic's total therapy during periods of stable control. Since monitoring a diabetic's glycated hemoglobin can lead to improved glycemic control, the ADA recommends routine measurements of four times a year up to once a month for less stable type I diabetics.
Several technologies are available for the measurement of glycated hemoglobin. They include immunoassays for HbAlc (TinaQuant, BMC; DCA2000, Ames; and Unimate, Roche), icon exchange (Variant, BioRad; Eagle Diagnostics), and affinity chromatography (ColumrMate, Helena; GlyHb, Pierce).
One objective of this project is to develop a simple to use disposable strip for electrochemical detection of HbAlc for use in both physician offices and the home.
The most significant parameter for assessing patient condition is ratio of HbAlc to HbAo, and thus the measurement of both glycated (HbAlc) and nonglycated (HbA0) values is required to calculate the ratio. This requires two separate measurements. It is preferable to use the same technology to measure both the glycated and nonglycated fractions, thus removing some sample and environmental interferences. Measurement of HbAlc via electrochemical immunoassay is described below. Electrochemical HbA0 immunoassay measurements are carried out using the same methods as that for HbAlc. The concentrations of HbA0 are significantly higher. One alternative to A0 measurements using immunoaffinity would be to measure total hemoglobin directly using biamperometry or differential pulse voltammetry. This can be easily accomplished since hemoglobin is readily oxidized by [Os(bpy)2(im)Cl]2+Cl 2.
The N-terminal valine of the β-chain of hemoglobin A is the site of glycosylation in HbAlc, and serves as a recognition site for the antibody. In whole blood the N-terminal valine is not accessible for the antibody to bind. Access is gained by lysing the red cells to release the hemoglobin followed by a conformation change (denaturing or unraveling) to adequately expose the HbAlc epitope. Dilution of the sample may occur as part of the lysing/denaturing process or may be required post denaturing to prepare the sample for the antibody (adjust pH, other) or bring the sample into a range suitable for electrochemical immunoassay. In one embodiment, a fixed amount of antibody is incubated with the prepared sample and it binds to the HbAlc epitopes of the sample. The free antibody and the antibody bound sample is then combined with the osmium peptide conjugate (Alc or A0) to allow the remaining unbound antibody to bind to the mediator label. When the mediators is bound to the antibody (a macromolecule), it can not freely diffuse to interact with the electrode and thus currents generated are significantly reduced. The remaining unbound mediator label is therefore proportional to the concentration of the HbAlc in the sample. The unbound mediator can be measured electrochemically preferably using an interdigitated array electrode with bipotentiostatic control.
Blood lysis is necessary to release the hemoglobin followed by denaturing to expose the HbAlc epitope. Lysis can easily be accomplished via surfactants, osmotic effects of dilution with water, and directly by many denaturants. Blood lysed through a freeze/thaw cycle was shown not to significantly interfere with the biamperometric measurement (“open rate” with and without lysed blood was almost identical). Conversely, denaturing the lysed blood with a variety of known denaturants to expose the HbAlc epitope has shown significant suppression of the electrochemical response, inhibiting measurement of an HbAlc dose response. Only LiSCN and citric acid from the list of evaluated denaturants shown in Table 1 was able to expose the Alc epitope and minimize protein fouling enough to measure an HbAlc dose response.
Denaturing the sample for antibody recognition without severely fouling the electrode surface is important for successful development of an HbAlc immunoassay. Although LiSCN has been used almost exclusively to show feasibility, it has many limitations that would hinder its use in the disposable. Citric acid, a solid at RT may offer benefits as a denaturant if it could be dried onto a strip followed by a diluent to adjust the pH to neutral. Acid or base blood denaturing followed by a final pH adjustment with a buffered diluent is an area worth further evaluation. One problem that was initially encountered was precipitation in adjusting the pH back to neutral, which can be overcome by using a different buffer or with the addition of surfactants.
Initial work did not show a dose response with KSCN
denatured blood. KSCN has a larger negative effect on the
electrochemical response than LiSCN.
Literature shows that LiSCN is more effective than KSCN
(concentrated efforts on LiSCN).
Denaturing of blood not evident with the higher blood
concentrations required for this assay. Higher concen-
trations of LiSCN are shown below.
Method used by Ames DCA2000 HbAlc immunoassay.
Blood HbAlc dose response (high/low) was seen with
citric acid and was comparable to the response
Evidence of blood denaturing was seen by
all: “solution turned brown.” Citric acid is preferred.
Adjustment of pH to neutral after denaturing also saw
problems of precipitation. Enzyme mediated responses
with Gluc-Dot at pH 5.7 reduces response 50%
compared to pH 7-8.
Citric acid blood denaturing method is shown in
Roche HbAlc immunoassay uses pepsin/citric acid to
hemolyze and proteolytically degrade hemoglobin
in glycoproteins accessible by the antibody.
Denaturation was apparent by the color change to a brown-
ish red solution.
Hemoglobin Alc dose response (high/low) was obtained
comparable to LiSCN and citric acid denaturants. The
procedure was identical to that of citric acid used above
with the exception of pepsin added to the acid. Results were
identical to that of citric acid.
Method of denaturing used in the TinaQuant HbAlc
Evidence of denaturing: “solution turned green”
TTAB concentrations 0.0125-0.2% severely suppressed
enzyme mediated (Glucdor/PQQ/Glucose) biamperometric
measurements. Open rates were 16-50 nA compared to
140 nA without TTAB.
Evidence of denaturing: “solution turned brown.”
NaOH does not adversely effect the enzyme mediated
electochemistry. Even at high pH the open rates do
not change, although pH adjustment will probably
be required to bring it within an optimal range
for the antibody.
NaOH denatured blood suppresses the open rates probably
due to protein fouling.
Lowering the pH to neutral tends to cause some
Effective Blood Denaturing Procedure for 2% Blood
LiSCN (One Step)
LiSCN (Two Step)
Citric Acid (2 Step)
40 μL 6 M LiSCN
960 μL 1.5 M LiSCN
200 μL 0.2 M Citric
20 μL 5% Tween in
20 μL 5% Tween in PBS
20 μL 5% Tween in
20 μL Blood
20 μL Blood
20 μL Blood
Mix (vortex) and
Mix (vortex) and allow
Mix (vortex) and
allow to denature
to denature for 10
allow to denature
for 10 minutes.
for 10 minutes.
Dilute with 920 μL
Dilute with 760 μL
8X PBS (0.1%
Denaturing time was not
was not optimized.
Limited data supports
Data indicates shorter
longer times for better
times may be adequate.
precision using this
PBS = 10 mM Phosphate Buffer, 2.7 mM KCl, 137 mM NaCl pH = 7.4
Increased level of surfactant (5% Tween) reduces or eliminates precipitate.
Electrode fouling caused by denatured blood proteins adsorbing to the electrode surface can impede electron transfer and thus decrease electrode sensitivity.
Electrode fouling or passivation occurs more or less immediately following sample contact with the surface thus minimizing the severity of denaturing in the sample should be the first approach. Surface conditions that are hydrophobic will favor adhesion of the proteins and thus fouling may be minimized with electrode surfaces of higher surface energies. This explains why gold electrodes shows less fouling with denatured blood than palladium. Reduction of protein fouling may be achieved by changing or protecting the electrode surface. Modifications that make the surface more hydrophilic should reduce the amount of fouling and can be accomplished by argon or oxygen plasma treatment or corona treatment. Selective coatings that could block the proteins from reaching the electrode surface can usually partially circumvent the problem have been used in the field to reduce fouling. Unfortunately, dramatic decreases in responses greater than seen with the denatured blood proteins are normally noted with their use. Hydrophilic coatings such as PEO were also evaluated and showed some improvement, but have similar problems of decreased magnitude and precision caused by forcing reagents to diffuse through the polymers. Reagents dispensed and dried over the electrodes may help reduce the magnitude of protein fouling with less negative effects.
Mediator concentration dose response, inhibition with antibody and reversal with a BSA-Alc polyhaptan were evaluated and summarized in Table 3. The Os-DSG-Alc is stable in a lyophilized form and when frozen in solution at−20° C. (40 and 80 μM).
Osotium Mediator Labels
PAB IS (≦92%)
Yes with BSA-Alc
% = Inhibition values ranged
PAB DE (≦97%)
from 16% to 97% depending on
age of Os-SMCC stock solution.
Degrades in solution.
PAB IS (≦44%)
Yes with BSA-Alc
Stability similar to SMCC.
PAB IS (≦91%)
Yes with BSA-Alc
More stable than conjugate
PAB DE (<87%)
made with SATA and SMCC
crosslinker but still degrades in
Yes with Sheep
No with AoHB-
Ao conjugate was found to be
unstable in solution. Conjugate
was not lyophilized.
Polyclonal DE (ion-exchange) purified sheep antibody is used in the TinaQuant HbAlc assay. IS (immunosorbent) antibody is prepared using standard IS purification methodology. Samples of a monoclonal antibody were also obtained for evaluation. Inhibition curves were performed in solution with all mixing occurring in microcentrifuge tubes. Assays were measured by applying 20 μL onto 6 mm2 palladium electrodes with the conditions shown in Table 3. Inhibition curves with the three hemoglobin Alc antibodies (PAB IS, PAB DE, and MAB) were generated by fixing OS-DSG-Alc at 5μM and varying the antibody concentration. Both PAB IS and MAB showed the expected stoichiometric relationship for inhibition with the osmium peptide conjugate indicating efficient and fast binding of the antibody to the Alc peptide. The polyclonal IS and monoclonal bother showed steep inhibition curves with maximum change being reached close to 5 μM. Additional antibody above 5 μM showed little effect on increasing the inhibition. The less purified PAB DE antibody had a much smaller slope and as expected required more than 3 times the amount to get close to maximum inhibition.
Inhibition curves were also performed for the Os-SMCC-Alc (Max=97%) and OS-SATA-Als (Max=44%) mediator labels. Stability of the mediator labels were also evaluated by monitoring % inhibition values over time. All of the mediator labels showed some degradation when stored in dilute solutions (40 μM) at RT. Samplers frozen at−20° C. appear to be stable.
For demonstrating inhibition reversal, antibody concentrations of 4 μM for both PAB IS and MAB and 15 μM for PAB DE were chosen from the inhibition curves shown above. Reversal curves were then generated using a series of dilutions ofBAS-Alc-polyhaptan with a−1:1 Alc:BAS. The BAS-Alc acts as our sample and binds to the antibody.
While these feasibility studies for a HbAlc immunoassay used an enzyme mediated amplification method (Glucdor/PQQ/glucose was used to regenerate reduced mediator after oxidation at the electrode surface providing a higher diffusion controlled current is given by the cottrell equation), they are considered to be indicative of results attainable with the use of IDA electrodes with bipotentiostatic control is most preferred for measuring mediator labeled conjugates in accordance with this invention.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US4293310||14 Mar 1980||6 Oct 1981||University Of Pittsburgh||Photoelectrochemical immunoassay|
|US4323536||6 Feb 1980||6 Abr 1982||Eastman Kodak Company||Multi-analyte test device|
|US4381978||14 Ago 1981||3 May 1983||Engelhard Corporation||Photoelectrochemical system and a method of using the same|
|US4526661||31 May 1983||2 Jul 1985||Basf Aktiengesellschaft||Electrochemical hydrogenation of nicotinamide adenine dinucleotide|
|US4545382||22 Oct 1982||8 Oct 1985||Genetics International, Inc.||Sensor for components of a liquid mixture|
|US4711245||7 May 1984||8 Dic 1987||Genetics International, Inc.||Sensor for components of a liquid mixture|
|US4830959||10 Nov 1986||16 May 1989||Medisense, Inc.||Electrochemical enzymic assay procedures|
|US4832814||28 Dic 1987||23 May 1989||E. I. Du Pont De Nemours And Company||Electrofusion cell and method of making the same|
|US4945045||23 Jun 1988||31 Jul 1990||Serono Diagnostics Ltd.||Electrochemical methods of assay|
|US4954414||8 Nov 1988||4 Sep 1990||The Mead Corporation||Photosensitive composition containing a transition metal coordination complex cation and a borate anion and photosensitive materials employing the same|
|US4963245||9 Mar 1990||16 Oct 1990||Ciba Corning Diagnostics Corp.||Unitary multiple electrode sensor|
|US4999632||15 Dic 1989||12 Mar 1991||Boehringer Mannheim Corporation||Analog to digital conversion with noise reduction|
|US5120420||31 Mar 1989||9 Jun 1992||Matsushita Electric Industrial Co., Ltd.||Biosensor and a process for preparation thereof|
|US5141868||27 Nov 1989||25 Ago 1992||Internationale Octrooi Maatschappij "Octropa" Bv||Device for use in chemical test procedures|
|US5192415||2 Mar 1992||9 Mar 1993||Matsushita Electric Industrial Co., Ltd.||Biosensor utilizing enzyme and a method for producing the same|
|US5229282||26 Nov 1990||20 Jul 1993||Matsushita Electric Industrial Co., Ltd.||Preparation of biosensor having a layer containing an enzyme, electron acceptor and hydrophilic polymer on an electrode system|
|US5243516||15 Dic 1989||7 Sep 1993||Boehringer Mannheim Corporation||Biosensing instrument and method|
|US5264103||15 Oct 1992||23 Nov 1993||Matsushita Electric Industrial Co., Ltd.||Biosensor and a method for measuring a concentration of a substrate in a sample|
|US5288636||14 Dic 1990||22 Feb 1994||Boehringer Mannheim Corporation||Enzyme electrode system|
|US5312762||13 Sep 1991||17 May 1994||Guiseppi Elie Anthony||Method of measuring an analyte by measuring electrical resistance of a polymer film reacting with the analyte|
|US5352351||8 Jun 1993||4 Oct 1994||Boehringer Mannheim Corporation||Biosensing meter with fail/safe procedures to prevent erroneous indications|
|US5366609||8 Jun 1993||22 Nov 1994||Boehringer Mannheim Corporation||Biosensing meter with pluggable memory key|
|US5405511||8 Jun 1993||11 Abr 1995||Boehringer Mannheim Corporation||Biosensing meter with ambient temperature estimation method and system|
|US5427912||27 Ago 1993||27 Jun 1995||Boehringer Mannheim Corporation||Electrochemical enzymatic complementation immunoassay|
|US5437772||1 Nov 1993||1 Ago 1995||The Electrosynthesis Co., Inc.||Portable lead detector|
|US5437999||22 Feb 1994||1 Ago 1995||Boehringer Mannheim Corporation||Electrochemical sensor|
|US5438271||22 Nov 1994||1 Ago 1995||Boehringer Mannheim Corporation||Biosensing meter which detects proper electrode engagement and distinguishes sample and check strips|
|US5491097||28 Feb 1994||13 Feb 1996||Biocircuits Corporation||Analyte detection with multilayered bioelectronic conductivity sensors|
|US5575895||30 May 1995||19 Nov 1996||Matsushita Electric Industrial Co., Ltd.||Biosensor and method for producing the same|
|US5589326||30 Dic 1993||31 Dic 1996||Boehringer Mannheim Corporation||Osmium-containing redox mediator|
|US5643721 *||9 Feb 1994||1 Jul 1997||Abbott Laboratories||Bioreagent immobilization medium|
|US5670031||21 May 1994||23 Sep 1997||Fraunhofer-Gesellschaft Zur Angewandten Forschung E.V.||Electrochemical sensor|
|US5958791 *||27 Sep 1996||28 Sep 1999||Innovative Biotechnologies, Inc.||Interdigitated electrode arrays for liposome-enhanced immunoassay and test device|
|DE4344646A1||24 Dic 1993||29 Jun 1995||Frieder Prof Dr Scheller||Device for a competitive immuno-assay for the detection of hapten(s)|
|EP0096288B1||24 May 1983||21 Ago 1985||BASF Aktiengesellschaft||Process for the electrochemical hydrogenation of nicotin-amide-adenine dinucleotide|
|EP0125139A2||8 May 1984||14 Nov 1984||MediSense, Inc.||Assay techniques utilising specific binding agents|
|EP0127958B1||8 May 1984||11 Mar 1992||MediSense, Inc.||Sensor electrode systems|
|EP0142301B1||24 Oct 1984||27 Nov 1991||Serono Diagnostics Limited||Methods of assay|
|EP0150999A2||25 Ene 1985||7 Ago 1985||Serono Diagnostics Limited||Methods of Assay|
|EP0167248A2||13 May 1985||8 Ene 1986||Serono Diagnostics Limited||Methods of assay|
|EP0299780A2||15 Jul 1988||18 Ene 1989||Sri International||Surface type microelectronic gas and vapor sensor|
|EP0328380A2||9 Feb 1989||16 Ago 1989||Nec Corporation||Electrochemical sensors in immunological measurement|
|EP0402126B1||7 Jun 1990||3 Abr 1996||Ciba Corning Diagnostics Corp.||Homogeneous amperometric immunoassay|
|WO1986002734A1||30 Oct 1985||9 May 1986||Hyperion Catalysis Int||Luminescent metal chelate labels and means for detection|
|WO1986003837A1||18 Dic 1985||3 Jul 1986||Iq Bio Ltd||Method and apparatus for biochemical assay|
|WO1986004926A1||21 Feb 1986||28 Ago 1986||Genetics Int Inc||Assay for degradable substrates by electrochemical detection of redox species|
|WO1991016630A1||11 Abr 1991||31 Oct 1991||Optical Systems Dev Partners||Device and method for electroimmunoassay|
|WO1992014741A1||19 Feb 1992||3 Sep 1992||Asulab Sa||Mono, bis or tris (2,2'-substituted bipyridine) complexes of a metal selected amongst iron, ruthenium, osmium or vanadium and preparation methods thereof|
|WO1992014836A1||19 Feb 1992||3 Sep 1992||Asulab Sa||Sensor for measuring the quantity of a dissolved component|
|WO1993025907A1||11 Jun 1993||23 Dic 1993||Centre Nat Rech Scient||Redox system marked antigen, electrochemical detection immunoassay and assay kit|
|WO1994014066A1||3 Dic 1993||23 Jun 1994||Univ Manchester||Immunoassay|
|WO1997001097A1||19 Jun 1996||9 Ene 1997||Serex Inc||Receptor:release ligand (reland) complexes and assays and kits based thereon|
|WO1997032866A1||5 Mar 1997||12 Sep 1997||Basf Ag||Catalyst composition free from noble metals|
|WO1997034140A1||12 Mar 1997||18 Sep 1997||Fraunhofer Ges Forschung||Detection of molecules and molecule complexes|
|1||Aoki et al., "Quantitative Analysis of Reversible, diffusion-Controlled Currents of Redox Soluble Species at Interdigitated Array Electrodes Under Steady-State Conditions," J. Electroanal. Chem., 256, 269-82, 1988.|
|2||Aoki et al., "Time-Dependence of Diffusion-Controlled Currents of a Soluble Redox Couple at Interdigitated Microarray Electrodes," J. Electroanal. Chem., 266, 11-20, 1989.|
|3||Chidsey et al., "Micrometer-Spaced Platinum Interdigitated Array Electrode: Fabrication, Theory, and Initial Use," Anal. Chem., 58 601-677, 1986.|
|4||Collin et al., "Anodic Electropolymerization of Films of Polypyrrole Functionalized with Metal Terpyridyl Redox Centres," J. Electroanal. Chem., 286, 75-87, 1990.|
|5||Foster et al., "Synthesis, Characterization, and Properties of a Series of Osmium- and Ruthenium-Containing Metallopolymers," Macromolecules, 23, 4372-4377, 1990.|
|6||Garguilo et al., "Amperometric Sensors for Peroxide, Choline, and Acetylcholine Based on Electron Transfer Between Horseradish Peroxidase and a Redox Polymer," Anal. Chem., 65, 523-528, 1993.|
|7||Geraty et al., "Polymer Modified Electrodes, Part III. Characterisation, Electrochemical and Photochemical Properties of Ruthenium Containing Poly-N-Vinylimidazole Coatings," J. Electroanal Chem., 176, 389-393, 1984.|
|8||Heineman et al., "Strategies For Electrochemical Immunoassay," Anal. Chem. 57 (12), 1321-1331, 1985.|
|9||International Search Report for PCT Application No. PCT/US99/11855, Sep. 22, 1999, 4 pages.|
|10||Matsue, "Electrochemical Sensors Using Microarray Electrodes," Trends Anal. Chem., 12 (3), 100-108, 1993.|
|11||Nielson et al., "Reactions of Osmium Tetraoxide with Protein Side Chains and Unsaturated Lipids," J. Chem. Soc., Delton Transactions, 1084-1088, 1979.|
|12||*||Niwa et al. ("Voltammetric Measurements of Reversible and Quasi-Reversible Redox Species Using Carbon Film Based Interdigitated Array Microelectrodes," Anal. Chem. 1994, 66, 285-289).|
|13||Niwa et al., "Fabrication and Characteristics of Vertically Separated Interdigitated Array Electrodes," J. Electroanal. Chem., 267, 291-297, 1989.|
|14||Ohara et al., "Glucose Electrodes Based on Cross-Linked [OS(bpy)<SUB>2 </SUB>C1]<SUP>+72+ </SUP>Complexed Poly(1-Vinylimidazole) Films," Anal. Chem., 65, 3512-3517, 1993.|
|15||Paeschke et al., "Voltammetric Multichannel Measurements Using Silicon Fabricated Microelectrode Arrays," Electroanalysis, 8, (10), 891-898, 1996.|
|16||Pishko et al., "Direct Electrical Communication Between Graphite Electrodes and Surface Adsorbed Glucose Oxidase/Redox Polymer Complex," Angew. Chem. Int. Ed. Engl., 29, (1), 82-84, 1990.|
|17||Sanderson et al., "Filar Electrodes: Steady-State Currents and Spectroelectrochemistry at Twin Interdigitated Electrodes," Anal. Chem. 57, 2388-2393, 1985.|
|18||Surridge et al., "Electron and Counterion Diffusion Constants in Mixed-Valent Polymeric Osmium Bipyridine Films" J. Phys. Chem., 98, 917-923, 1994.|
|19||Thompson et al., "Comparison of Methods for Following Alkaline Phosphatase Catalysis: Spectrophotometric versus Amperometric Detection," Anal. Biochem., 192, 90-95, 1991.|
|20||Wollenberger et al., "Interdigitated Array Microelectrodes for the Determination of Enzyme Activities," Analyst, 119, 1245-1249, Jun. 1994.|
|21||Wollenberger, "Electrochemical Biosensors-Ways to Improve Sensor Performance," Biotechnology and Genetic Engineering Reviews, 13, 27-266, Dec. 1995.|
|22||Xu et al., "Heterogeneous Enzyme Immunoassay of Alpha-Fetoprotein in Maternal Serum by Flow-Injection Amperometric Detection of 4-Aminophenol," Clin. Chem., 36 (11), 1941-1944, 1990.|
|23||Zakeeruddin et al., "Towards Mediator Design: Characterization of Tris-(4-4'-Substituted-2,2'-Bipyridine) Complexes of Iron (II), Ruthenium (II) and Osmium (II) as Mediators for Glucose Oxidase of Aspergillus niger and other Redox Proteins," J. Electroanal. Chem., 337, 253-283, 1992.|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US7875047||25 Ene 2007||25 Ene 2011||Pelikan Technologies, Inc.||Method and apparatus for a multi-use body fluid sampling device with sterility barrier release|
|US7892183||3 Jul 2003||22 Feb 2011||Pelikan Technologies, Inc.||Method and apparatus for body fluid sampling and analyte sensing|
|US7901365||21 Mar 2007||8 Mar 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US7909774||13 Feb 2007||22 Mar 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US7909775||26 Jun 2007||22 Mar 2011||Pelikan Technologies, Inc.||Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge|
|US7909777||29 Sep 2006||22 Mar 2011||Pelikan Technologies, Inc||Method and apparatus for penetrating tissue|
|US7909778||20 Abr 2007||22 Mar 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US7914465||8 Feb 2007||29 Mar 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US7938787||29 Sep 2006||10 May 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US7959582||21 Mar 2007||14 Jun 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US7976476||16 Mar 2007||12 Jul 2011||Pelikan Technologies, Inc.||Device and method for variable speed lancet|
|US7981055||22 Dic 2005||19 Jul 2011||Pelikan Technologies, Inc.||Tissue penetration device|
|US7981056||18 Jun 2007||19 Jul 2011||Pelikan Technologies, Inc.||Methods and apparatus for lancet actuation|
|US7988644||2 Ago 2011||Pelikan Technologies, Inc.||Method and apparatus for a multi-use body fluid sampling device with sterility barrier release|
|US7988645||3 May 2007||2 Ago 2011||Pelikan Technologies, Inc.||Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties|
|US8007446||19 Oct 2006||30 Ago 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US8016774||22 Dic 2005||13 Sep 2011||Pelikan Technologies, Inc.||Tissue penetration device|
|US8062231||11 Oct 2006||22 Nov 2011||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US8079960||10 Oct 2006||20 Dic 2011||Pelikan Technologies, Inc.||Methods and apparatus for lancet actuation|
|US8123700||26 Jun 2007||28 Feb 2012||Pelikan Technologies, Inc.||Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge|
|US8157748||10 Ene 2008||17 Abr 2012||Pelikan Technologies, Inc.||Methods and apparatus for lancet actuation|
|US8162853||22 Dic 2005||24 Abr 2012||Pelikan Technologies, Inc.||Tissue penetration device|
|US8197421||16 Jul 2007||12 Jun 2012||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US8197423||14 Dic 2010||12 Jun 2012||Pelikan Technologies, Inc.||Method and apparatus for penetrating tissue|
|US8202231||23 Abr 2007||19 Jun 2012||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8206317||22 Dic 2005||26 Jun 2012||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8206319||26 Ago 2010||26 Jun 2012||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8211037||22 Dic 2005||3 Jul 2012||Pelikan Technologies, Inc.||Tissue penetration device|
|US8216154||23 Dic 2005||10 Jul 2012||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8221334||22 Dic 2010||17 Jul 2012||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8235915||18 Dic 2008||7 Ago 2012||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8251921||10 Jun 2010||28 Ago 2012||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for body fluid sampling and analyte sensing|
|US8262614||1 Jun 2004||11 Sep 2012||Pelikan Technologies, Inc.||Method and apparatus for fluid injection|
|US8267870||30 May 2003||18 Sep 2012||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for body fluid sampling with hybrid actuation|
|US8282576||29 Sep 2004||9 Oct 2012||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for an improved sample capture device|
|US8282577||15 Jun 2007||9 Oct 2012||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge|
|US8296918||23 Ago 2010||30 Oct 2012||Sanofi-Aventis Deutschland Gmbh||Method of manufacturing a fluid sampling device with improved analyte detecting member configuration|
|US8333710||5 Oct 2005||18 Dic 2012||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8337419||4 Oct 2005||25 Dic 2012||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8337420||24 Mar 2006||25 Dic 2012||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8337421||16 Dic 2008||25 Dic 2012||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8343075||23 Dic 2005||1 Ene 2013||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8360991||23 Dic 2005||29 Ene 2013||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8360992||25 Nov 2008||29 Ene 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8366637||5 Feb 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8372016||30 Sep 2008||12 Feb 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for body fluid sampling and analyte sensing|
|US8382682||6 Feb 2007||26 Feb 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8382683||7 Mar 2012||26 Feb 2013||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8388551||27 May 2008||5 Mar 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for multi-use body fluid sampling device with sterility barrier release|
|US8403864||1 May 2006||26 Mar 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8414503||16 Mar 2007||9 Abr 2013||Sanofi-Aventis Deutschland Gmbh||Methods and apparatus for lancet actuation|
|US8430828||26 Ene 2007||30 Abr 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for a multi-use body fluid sampling device with sterility barrier release|
|US8435190||19 Ene 2007||7 May 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8439872||26 Abr 2010||14 May 2013||Sanofi-Aventis Deutschland Gmbh||Apparatus and method for penetration with shaft having a sensor for sensing penetration depth|
|US8491500||16 Abr 2007||23 Jul 2013||Sanofi-Aventis Deutschland Gmbh||Methods and apparatus for lancet actuation|
|US8496601||16 Abr 2007||30 Jul 2013||Sanofi-Aventis Deutschland Gmbh||Methods and apparatus for lancet actuation|
|US8556829||27 Ene 2009||15 Oct 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8562545||16 Dic 2008||22 Oct 2013||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8574168||26 Mar 2007||5 Nov 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for a multi-use body fluid sampling device with analyte sensing|
|US8574895||30 Dic 2003||5 Nov 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus using optical techniques to measure analyte levels|
|US8579831||6 Oct 2006||12 Nov 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8622930||18 Jul 2011||7 Ene 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8636673||1 Dic 2008||28 Ene 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8641643||27 Abr 2006||4 Feb 2014||Sanofi-Aventis Deutschland Gmbh||Sampling module device and method|
|US8641644||23 Abr 2008||4 Feb 2014||Sanofi-Aventis Deutschland Gmbh||Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means|
|US8652831||26 Mar 2008||18 Feb 2014||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for analyte measurement test time|
|US8668656||31 Dic 2004||11 Mar 2014||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for improving fluidic flow and sample capture|
|US8679033||16 Jun 2011||25 Mar 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8690796||29 Sep 2006||8 Abr 2014||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8702624||29 Ene 2010||22 Abr 2014||Sanofi-Aventis Deutschland Gmbh||Analyte measurement device with a single shot actuator|
|US8721671||6 Jul 2005||13 May 2014||Sanofi-Aventis Deutschland Gmbh||Electric lancet actuator|
|US8784335||25 Jul 2008||22 Jul 2014||Sanofi-Aventis Deutschland Gmbh||Body fluid sampling device with a capacitive sensor|
|US8808201||15 Ene 2008||19 Ago 2014||Sanofi-Aventis Deutschland Gmbh||Methods and apparatus for penetrating tissue|
|US8828203||20 May 2005||9 Sep 2014||Sanofi-Aventis Deutschland Gmbh||Printable hydrogels for biosensors|
|US8845549||2 Dic 2008||30 Sep 2014||Sanofi-Aventis Deutschland Gmbh||Method for penetrating tissue|
|US8845550||3 Dic 2012||30 Sep 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8905945||29 Mar 2012||9 Dic 2014||Dominique M. Freeman||Method and apparatus for penetrating tissue|
|US8945910||19 Jun 2012||3 Feb 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for an improved sample capture device|
|US8965476||18 Abr 2011||24 Feb 2015||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US9034639||26 Jun 2012||19 May 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus using optical techniques to measure analyte levels|
|US9072842||31 Jul 2013||7 Jul 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US9089294||16 Ene 2014||28 Jul 2015||Sanofi-Aventis Deutschland Gmbh||Analyte measurement device with a single shot actuator|
|US9089678||21 May 2012||28 Jul 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|Clasificación de EE.UU.||205/777.5, 204/403.1|
|Clasificación internacional||C07F15/00, G01N33/72, C07K5/103, G01N33/536, C07K7/06, C07K7/02, G01N27/49, G01N33/532, C07K9/00, G01N27/327, G01N33/58, C07K14/805|
|Clasificación cooperativa||Y10T436/105831, Y10S436/806, Y10S436/805, G01N33/58, C07K7/02, C07K14/805, G01N2458/30, G01N2333/805, C07K9/001, C07K7/06, C07K5/101, G01N33/536, G01N33/532, G01N27/3277, C07F15/0026, G01N33/723|
|Clasificación europea||C07K7/06, C07F15/00N2B, C07K5/10A1B, G01N33/72B2, G01N33/58, G01N33/536, C07K14/805, C07K7/02, G01N33/532, C07K9/00D, G01N27/48|
|16 Ago 2004||AS||Assignment|
Owner name: ROCHE DIAGNOSTICS OPERATIONS, INC., INDIANA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:ROCHE DIAGNOSTICS CORPORATION;REEL/FRAME:015201/0368
Effective date: 20040101
Owner name: ROCHE DIAGNOSTICS OPERATIONS, INC.,INDIANA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:ROCHE DIAGNOSTICS CORPORATION;REEL/FRAME:015201/0368
Effective date: 20040101
|24 Feb 2009||FPAY||Fee payment|
Year of fee payment: 8
|25 Feb 2013||FPAY||Fee payment|
Year of fee payment: 12
|23 Jun 2015||AS||Assignment|
Owner name: ROCHE DIABETES CARE, INC., INDIANA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:ROCHE DIAGNOSTICS OPERATIONS, INC.;REEL/FRAME:036008/0670
Effective date: 20150302