Continuous monitoring of analyte concentrations.

We have investigated the application of a modified, heterogeneous, competitive enzyme immunoassay for the continuous measurement of small analytes in a medium stream. The analytical system contains two antibodies that are immobilized on spatially separated areas, one binding the analyte (Ab1) and the other binding the enzyme (Ab2). An analyte-enzyme conjugate serves as signal generator. The analyte-enzyme conjugate functions as a heterobifunctional shuttle that can bind to either antibody. A semipermeable membrane retains the enzyme shuttle in the internal volume of the sensor but permits the passage of small analytes from the medium stream. The amount of enzyme bound to Ab1 is inversely proportional and the amount of enzyme bound to Ab2 is directly proportional to the analyte concentration. We have demonstrated that this analytical system (1) can provide a larger total signal; (2) has a sensitivity comparable with conventional competitive immunoassays; (3) does not require the separation of bound from free antigens; and (4) is therefore suitable for the continuous measurement of analytes in a medium stream. With a model system, an increase from 0 ng ml-1 to 20 ng ml-1 of the steroid hormone progesterone and the subsequent fall to 0 ng ml-1 could be monitored.     

Performance characteristics of a reversible immunosensor with a heterobifunctional enzyme conjugate as signal generator

Factors that control the performance of a reversible immunosensor with an analyte (progesterone)-enzyme (horseradish peroxidase) conjugate as signal generator have been investigated. The conjugate is used in conjunction with two antibodies, which are specific to progesterone and to horseradish peroxidase, immobilized on two spatially separated polypropylene mesh discs. The conjugate and two antibodies are confined to an internal compartment of a microdialyzer by a semipermeable membrane. The small analyte from an external medium permeates across the membrane into the internal compartment where the analyte concentration determines the relative amounts of the bound conjugate on the two solid surfaces. By measuring two signals from the conjugate bound at two separate sites, we experimentally obtained time-response curves to a concentration pulse of the external analyte. A mathematical (kinetic) model describing the sensor system was developed and used for the determination of rate-limiting factors. In semicontinuous monitoring of the analyte concentrations, operation of the immunosensor with the enzyme conjugate as signal generator required special attention to (a) enzyme stability, (b) analyte permeation (dependence on medium components), and (c) kinetics related to the different accessibility to the same antibody of the small analyte (to be measured) vs. the larger counterpart on the enzyme conjugate (for signal generation). (c) 1997 John Wiley & Sons, Inc. Biotechnol Bioeng 56: 221-231, 1997.     

Enzyme-amplified rate conductimetric immunoassay

A new immunoassay technique based on measurement of conductance changes in solutions is described. The assay employs an immobilized monoclonal antibody to capture a protein analyte along with a second antibody to the same analyte, conjugated to an enzyme capable of producing ions which are measured conductimetrically. Urease was selected as the enzyme, because it produces, from urea, four ions for each catalytic event. The analyte studied was human chorionic gonadotropin in serum. Higher concentrations of analyte during incubation with immobilized antibody and antibody-urease conjugate led to increased binding of the latter. After removal of unbound conjugate, urea solution was added and the rate of conductance change measured in the bulk substrate solution. Experiments, performed in polystyrene microtiter wells using a specially designed electrode, demonstrated the ability to measure 30 picomolar concentrations of human chorionic gonadotropin with a 30-s rate measurement. Urease proved to be an excellent labeling enzyme, retaining its activity under the nonionic conditions necessary to maintain low background conductance. Good agreement was obtained between observed rates and those expected from conductimetric theory and known physical parameters. The potential utility of the conductimetric immunoassay lies in the fabrication of biosensor devices for simplification and cost reduction of immunochemical-based instrumentation. Further improvements to the technique are proposed to achieve lower detection limits.     

Antibody-antigen complex formation with immobilized immunoglobulins.

We have investigated the complex formation between an immobilized monoclonal antibody and antigens that differ in size about 50-fold. As a model system, we used an iodinated progesterone derivative and a progesterone-horseradish peroxidase conjugate as tracer and a monoclonal antibody as binding protein. The antibody was immobilized by four different methods: physical adsorption, chemical binding, and binding via protein G in the absence or presence of a protective protein (gelatin). These investigations have shown that the performance of competitive immunoassays is determined by a combination of factors: (a) the relative size of the analyte and the tracer, (b) the antibody density on the solid matrix, (c) the method of immobilization of the antibody, and (d) the binding constants between antibody-analyte and antibody-tracer. All of these interactions have to be considered in designing an optimal immunoassay. The smaller antigen can form a 3- to 35-fold higher maximal complex density than the larger antigen. Dose-response curves are less affected by the size of the tracer than by the binding constant with the antibody. A large enzyme tracer with a relatively low binding constant can, therefore, provide a more sensitive assay. On the other hand, the increase in complex density achieved with a smaller tracer yields a higher signal that in turn can provide a better signal-to-noise ratio in highly sensitive competitive solid-phase immunoassays. We have suggested a model for antibody immobilization that accounts for the interdependence of tracer size, complex formation, and antibody density. The methods described can be used to design and optimize immunoassays of predefined performance characteristics. The results are particularly useful for converting radioimmunoassays to enzyme immunoassays.     

Preparation of an insulin conjugate with beta-galactosidase from E. coli for immunoenzyme assay

A modified procedure has been worked out for preparing a conjugate of porcine insulin with E. coli beta-galactosidase employing a heterobifunctional reagent, N-hydroxysuccinimidyl m-maleimidobenzoate. Optimal conditions for insulin acylation and subsequent coupling with beta-galactosidase were selected that afforded the conjugate in a high yield. The ability of the modified antigen to react with antibody was evaluated in the reaction of conjugate binding with immobilized monoclonal antibody to insulin. The conjugate almost completely retained the enzymatic activity and reacted with high specificity with the antibody to insulin. The conjugate can be used in competitive ELISA of insulin.     

Electrochemical enzyme immunoassay for detection of toxic substances.

Sensors that provide reliable, rapid measurement of toxic substances are needed to solve significant human health and safety problems. We developed a new biosensor design that combines the advantages of immunoassay with electrochemical response. We established that this enzyme-linked immunosensor measures toxic substances in biological samples. The biosensor consists of two major elements: (1) an electrical conducting layer having immobilized enzyme, polyclonal or monoclonal antibodies, and other necessary reagents, and (2) the electronic components used in the signal readout. The result is an amperometric immunoassay based on coupling the immunochemical reaction to the enzyme electrode response by using a soluble, electrochemically active mediator. The specific question addressed was: Does the system's immunochemical detection reliably respond at sufficiently low analyte concentrations? We present our results in these areas: (1) enzyme immobilization on colloidal gold; (2) colloidal gold-enzyme deposition on the electrode surface; (3) mediator-antigen conjugate synthesis; (4) antibody incorporation at the electrode surface; (5) bioelectrode characterization and optimization; and (6) immunosensor demonstration to detect antigen. Sensors that employ immunochemical detection will have broad applicability to detect/diagnose toxic substances in biological samples such as blood and urine and in environmental samples such as wastewater and drinking water.     

A highly sensitive flow-through amperometric immunosensor based on the Peroxidase chip and enzyme-channeling principle

A concept based on the Peroxidase-chip (P-chip), antibody co-immobilization, competitive and enzyme-channeling principle was exploited to develop an integrated flow-through amperometric biosensor for detection of environmental pollutants such as s-triazine herbicides. In this concept, recombinant peroxidase is immobilized on the gold electrode (P-chip) in such a way that direct electron transfer is achieved. The recognition and quantitation the target analyte is realized through the competition between the simazine-glucose oxidase (GOD) conjugate and free simazine for the binding sites of the monoclonal antibody co-immobilized with peroxidase on the gold electrode. The arrangement allows to generate a specific signal in the presence of glucose through the channeling of H2O2 produced by GOD conjugate bound to the antibody. The immunosensor exhibited 50% signal decrease (IC50 value) at approximately 0.02 microg l(-1). A concentration of 0.1 ng l(-1) gave a signal clearly distinguishable from the blank whereas the ELISA using the same antibody had a typical detection limit of about 1 microg l(-1), which is four orders of magnitude higher compared to the presented biosensor system. The results demonstrated that gene engineering biomolecules, in this case recombinant peroxidase, might be attractive reagents for the development of electrochemical immunosensors.     

Modeling of immunosensors under nonequilibrium conditions. II. Experimental determination of performance characteristics.

In an attempt to optimize immunosensors operating with an immobilized antibody as binding protein and an analyte-enzyme conjugate as signal generator that is significantly larger in molecular size than the analyte, in a previous communication (Part I) (S.-H. Paek and W. Schramm (1991) Anal. Biochem. 196) we developed mathematical models for the prediction of performance characteristics. These models are compared in this contribution with experimentally obtained results. As an example, a monoclonal antibody to the steroid hormone progesterone has been used as binding protein, an 125I-progesterone derivative, and a progesterone-horseradish peroxidase derivative as tracers for signal generation. A minimum of parameters needs to be experimentally determined to calculate the performance: the amount of immobilized antibody, the diffusion coefficient of antigens, the thickness of the penetration layer, and the on- and off-rates for binding of the antigen to the antibody. We have described simple methods to obtain these data for the labeled antigen and for the unlabeled analyte that does not provide a signal per se. Kinetic binding curves for antigen-antibody complex formation obtained with the mathematical models correlated well with experimentally obtained results for antigens of different sizes. Although equilibrium of the antigen-antibody complex for the enzyme-labeled analyte conjugate requires about 4 h in the absence of free analyte, dose-response curves can be obtained after 5 min and the relative position of these curves does not change significantly after 30 min. Using a total volume of 200 microliters for the analytical procedure in microtiter wells, agitation as a means to accelerate convective diffusion during an incubation period of 30 min is not necessary with the analyte-enzyme conjugate. However, immunosensors using large analyte-enzyme conjugates as signal generators for the detection of small analytes require strict control of the incubation time if operated within short periods of time (less than 30 min).     

Plasminogen activator-anti-human fibrinogen conjugate

A covalent conjugate between the plasminogen activator urokinase and polyclonal rabbit anti-human fibrinogen has been formed using the heterobifunctional coupling reagent N-succinimidyl 3-(2-pyridyldithio) propionate. The resultant urokinase-anti-human fibrinogen conjugate was separated from unreacted material by gel filtration. The conjugate exhibited amidase activity against the small chromogenic substrate pyroglutamyl-glycyl-arginine-p-nitroanilide as well as plasminogen activator activity in an assay employing plasminogen and the plasmin substrate D-valyl-leucyl-lysine-p-nitroanilide. Retention of antibody specificity for fibrinogen was demonstrated using an enzyme linked immunoassay procedure. The conjugate was found to have greater stability in human plasma than unconjugated urokinase.     

Modeling of immunosensors under nonequilibrium conditions. I. Mathematic modeling of performance characteristics.

Immunosensors for the detection of small analytes that use analyte-enzyme conjugates as signal generators require special attention if operated under nonequilibrium conditions. If the size of the analyte and the analyte-enzyme conjugate differ substantially, the two antigens do not diffuse at the same rate. This can cause time-dependent shifts in the sensitivity of competitive immunoassays. Therefore, immunosensors operating at short incubation times require precise timing that meets closely the specifications for which the sensors were calibrated. As an example, we have analyzed kinetic binding curves for the quantitative determination of progesterone with an immobilized monoclonal antibody and a conjugate between horseradish peroxidase and progesterone as signal generator. Mathematical paradigms have been developed to simulate the diffusion, antigen-antibody complex formation, and competitive binding processes in this analytical system. Dose-response curves obtained under nonequilibrium conditions can vary substantially from those obtained at equilibrium of antigen-antibody interaction. The degree of this variation depends on the performance characteristics of the major components of the immunosensor. The developed mathematical solutions reflect experimental results and can be used to model optimal conditions for immunosensors operating under nonequilibrium conditions. In this paper (Part I), we report on the mathematical modeling of the interaction between analyte, analyte-enzyme conjugate, and an immobilized antibody. In Part II (W. Schramm and S.-H. Paek (1991) Anal. Biochem. 196), we present experimental results and compare them with the theoretical models.     

Development of rapid one-step immunochromatographic assay

An analytical system for a one-step immunoassay has been constructed using the concept of immunochromatography. The system employed two different antibodies that bound distinct epitopes of an analyte molecule: an antibody labeled with a signal generator (e.g., colloidal gold), which was placed in the dry state at a predetermined site on a glass-fiber membrane, and another antibody immobilized on the surface of a nitrocellulose membrane. Three membranes, one with the tracer, one with immobilized antibody, and a cellulose membrane as the absorbent of medium (in a sequence from the bottom), were attached to a plastic film and cut into strips. Aqueous medium containing analyte absorbed from the bottom end of the immunostrip dissolved the labeled antibody, and the antigen-antibody binding complex formed was transported into the next nitrocellulose membrane by the flow caused by capillary action. The complex subsequently reacted with the immobilized antibody, which generated a signal in proportion to the analyte concentration. The convective mass transfer of the immunoreactant to the binding partner allowed the assay to be performed with no handling of reagents. The reaction, however, was carried out under nonequilibrium conditions, which resulted in decreased sensitivity as compared with assays performed in an equilibrium mode (e.g., ELISA). To minimize such sacrifice, major factors that control system performance were identified and the system was then devised under optimal conditions.     

Development of a plasma panel test for detection of human myocardial proteins by capillary immunoassay

A chemiluminescence immunoassay for the detection of four heart marker proteins: myoglobin, creatine kinase mb [CKmb], troponin I [TnI], and fatty acid-binding protein [FABP], was designed. The immunoassay was based on enzyme-linked immunosorbent assay [ELISA] and antibodies immobilized in glass capillaries pre-treated with 3-aminopropyltriethoxysilane. The protein bound to the antibody was detected by using an anti-protein-horseradish peroxidase [HRP] conjugate. The reaction of the HRP with luminal and hydrogen peroxide-based substrate generated the chemiluminescence and a photodiode detector was used to measure the light intensity. The same assay protocol was used to detect all four proteins. Ultrasound waves were used to improve the silanization of glass and the antibody immobilization process. The optimization of the duration and intensity of the ultrasound was performed for the myoglobin assay. Ultrasound improved the silanization procedure and the capillaries gave an approximately 2.5 times greater ELISA response. Ultrasound also improved the sensitivity by approximately 100% when monoclonal antibody was immobilized on a glass capillary. Calibration curves corresponding to analyte concentrations ranging from 2.4 to 2400 ng/ml in plasma samples were recorded. The detection limits were in the region of 1.2 myoglobin, 0.6 CKmb, 5.6 TnI, and 4 ng/ml FABP in plasma with a coefficient of variation of 3-9.9%.     

A solid-phase enzyme immunoassay of thromboxane B2

A solid-phase enzyme immunoassay for thromboxane B2 was developed using a conjugate of thromboxane B2 and beta-galactosidase. Anti-thromboxane B2 IgG was bound to a polystyrene tube, and the enzyme-labeled and unlabeled thromboxane B2 were allowed to react in a competitive manner with the immobilized antibody. Then, the specifically bound beta-galactosidase was assayed fluorimetrically, and the enzyme activity was correlated with the amount of unlabeled thromboxane B2. By using a calibration curve, thromboxane B2 was determined in the range of 20 fmol-14 pmol. 2,3-Dinor- and 2,3,4,5-tetranor-thromboxane B2 cross-reacted with thromboxane B2 to the extents of 18.6% and 0.4%, respectively. Most prostaglandins and their metabolites tested showed cross-reactivities of less than 1%. In application of the method to human blood and urine, an octadecylsilyl silica column was utilized for extraction and concentration of thromboxane B2. The crude extract contained a substance(s) which disturbed the enzyme immunoassay and gave an apparently high value of thromboxane B2, and the interfering substance was separated from thromboxane B2 by reverse-phase HPLC. Various amounts of authentic thromboxane B2 added to the purified material from human plasma could be determined by the enzyme immunoassay with a recovery of about 80% and the results correlated well with the values obtained by radioimmunoassay (r = 0.979). When the extract from human urine was analyzed by reverse-phase HPLC, the 2,3-dinor metabolite rather than thromboxane B2 was the predominant compound detected by the enzyme immunoassay.     

A robust method for the preparation and purification of antibody/streptavidin conjugates

The many uses of antibody-protein conjugates, especially antibody-streptavidin conjugates, give rise to the need for a reliable conjugation method offering reasonable yields and reproducible quality. We describe a method for preparing antibody-streptavidin conjugates that has consistently produced conjugates of quality and in sufficient quantity to be used in the clinical development and evaluation of the Pretarget delivery system. In this method antibody disulfides are reduced to generate reactive thiols, and maleimides are linked to streptavidin with the heterobifunctional cross-linking agent, SMCC. The two activated proteins are then mixed briefly before the conjugation is terminated with an oxidizing agent that reforms disulfides from unreacted thiols. The preponderance of the conjugate produced is 1:1 and 1:2 Ab:SA conjugate. This fraction is isolated from unconjugated proteins and high molecular weight byproduct by iminobiotin affinity and ion-exchange chromatography. The resulting conjugate is at least 90% 1:1 + 1:2 Ab:SA conjugate, contains no SA or Ab, and is produced reproducibly in 37% yield.     

Improved sensitivity in homogeneous enzyme immunoassays using a fluorogenic macromolecular substrate: an assay for serum ferritin

A new highly sensitive nonseparation enzyme immunoassay for human serum ferritin is described. Reagents include a beta-galactosidase-ferritin conjugate, sheep anti-ferritin, anti-sheep IgG, and dextran-linked beta-galactosylumbelliferone as enzyme substrate. The method is based on inhibition of enzyme activity when anti-ferritin binds to the enzyme-ferritin conjugate. Ferritin in the sample and enzyme-labeled ferritin compete for a limited quantity of anti-ferritin. The enzyme activity of the reaction mixture is directly related to the ferritin content of the sample. Some patients' samples caused strong interference in the assay due to the presence of antibody to beta-galactosidase. Several ways of eliminating the interference are presented. When measures were adopted to suppress sample interference, the assay results correlated well with those of other immunoassay methods.     

A flow immunoassay for studies of human exposure and toxicity in biological samples

This paper describes a heterogeneous competitive flow immunoassay with a high sample throughput which can be used for the screening of smaller analytes in various samples. The method is based on off-line incubation of the analyte (Ag), a fluorescent labelled tracer (Ag*) and the corresponding antibody (Ab). The separation of bound (Ab-Ag*) and free tracer (Ag*) is based on a size exclusion and reversed phase mechanism utilizing a restricted access (RA) column. The column traps the free unbound tracer (Ag*) in its hydrophobic (C18) inner cavity but excludes the large Ab-Ag* complex, which is passed on and measured by the fluorescence detector. The flow immunoassay was developed using the triazine herbicide atrazine as a model compound owing to its human toxicity and widespread use. A sample throughput of 80 samples per hour and a detection limit of 300 pg ml-1 in water were obtained. Urine samples were successfully applied for direct injections into the flow system, while for human plasma samples an additional clean-up step using solid phase extraction was efficiently included where pure extract is obtained with the highly stable and biocompatible extracting column material. The resulting detection limits for atrazine in plasma and water samples using this clean-up and trace enrichment procedure were found to be 2 ng ml-1 and 20 pg ml-1 respectively.     

A new reliable chemiluminescence immunoassay (CLIA) for prostaglandin E2 using enhanced luminol as substrate

A sensitive and reliable chemiluminescence immunoassay suitable for the quantitative determination of prostaglandin E₂ (PGE₂) has been developed using 96 well microtiter plates (MTP). The assay is based on a competitive reaction between a highly specific monoclonal anti-PGE₂ antibody (mouse), free antigen and solid phase bound antigen. The MTP was first coated with a bovine serum albumin (BSA)-PGE₂ conjugate. Then, after preincubating, the anti-PGE₂ antibody (Ab) and the analyte were added. The remaining amount of free antibody was captured by the solid phase bound BSA-PGE₂ conjugate. The monoclonal antibody captured on the MTP was determined using biotinylated antimouse-Ab and a complex of avidin and biotin-labelled horseradish peroxidase (HRP). Substrate for HRP was the cyclic diacyl hydrazide compound luminol, enhanced by p-iodophenol. Photons emitted during the reaction were measured using a photomultiplier tube. The assay has been validated with assay buffer and human plasma over a concentration range of 10–50,000 pglml. The lower limit of quantification is 100 pglml (2 pglwell) and 150 pglml (3 pglwell) for buffer and plasma, respectively. The intea-day coefficients of variation (CV) for the range of 100–50,000 pglml are 3.2–8.9% (buffer) and 4.2–17.7% (plasma) and inter-day CV are 2.9–19.8% (buffer) and 3.6–21.2% (plasma). The method can be used for quantification of PGE2 in biological fluids like plasma and suction blister fluid.     

Highly sensitive and selective surface plasmon resonance sensor for detection of sub-ppb levels of benzo[a]pyrene by indirect competitive immunoreaction method

A surface plasmon resonance (SPR)-immunosensor for detection of benzo[a]pyrene (BaP) is developed by using a model BaP-hapten compound, BaP-bovine serum albumin conjugate (BaP-BSA), and an anti-BaP-BSA monoclonal antibody. BaP-BSA conjugate is immobilized on a gold thin-film sensor chip by means of simple physical adsorption. The number of BaP-hapten units in BaP-BSA conjugate is estimated to be 28 from the difference in molecular weight (MW) between BaP-BSA conjugate and BSA based on the results of matrix-assisted laser desorption/ionization time-of-flight mass spectrometry (MALDI-TOF MS) measurement. Anti-BaP-BSA antibody on contact with the BaP-BSA conjugate immobilized sensor chip causes an increase in the incident angle of the sensor chip. Binding of anti-BaP-BSA antibody with surface-immobilized BaP-BSA conjugate is inhibited by the presence of BaP in analyte solution, because of the inhibition effect of BaP. The SPR immunosensor for BaP functioning with the indirect competitive immunoreaction of anti-BaP-BSA antibody between the analyte (BaP) in testing solution and the BaP-BSA conjugate immobilized on the sensor chip provides a rapid determination (response time: ca. 15 min) of BaP in the concentration range of 0.01-1000 ppb. The antibody anchored to the sensor chip by antigen-antibody binding is removed on treatment with a pepsin solution (pH 2.0) for few minutes. The SPR sensor chip is found to be reusable for more than 20 times with a little decrease (<7%) in the sensor response. Detection of BaP by direct competitive immunoreactions is also carried out by enzyme-linked immunosorbent assay (ELISA). The concentration of BaP could be determined as low as 0.01 ppb and 2 ppb using the SPR sensor and the ELISA method, respectively. The SPR sensor is found to detect BaP selectively in the presence of 2-hydroxybiphenyl (HBP); the incident angle shift of the SPR sensor for BaP is found to be same irrespective to the presence or the absence of a same concentration (as much as 30 ppb) of HBP together.     

A heterologous enzyme immunoassay of prostaglandin E2 using a stable enzyme-labeled hapten mimic

A sensitive heterologous enzyme immunoassay for prostaglandin E2 was developed using 9-deoxy-9-methylene-prostaglandin F2 alpha as a stable prostaglandin E2 mimic. beta-Galactosidase was conjugated to the hapten mimic. Anti-prostaglandin E2 IgG was bound to a polystyrene tube. The enzyme-labeled hapten mimic mixed with unlabeled prostaglandin E2 was allowed to react in a competitive manner with the immobilized antibody. Then, the beta-galactosidase specifically bound to the antibody was assayed fluorometrically, and the enzyme activity was correlated with the amount of unlabeled prostaglandin E2. According to the calibration curve thus obtained, prostaglandin E2 could be determined in a range of 1.2-430 fmol. Prostaglandin E2 was extracted from human urine by the use of an octadecylsilyl silica column. The crude extract contained a substance(s) which disturbed the enzyme immunoassay and gave an apparently high content of prostaglandin E2. The interfering substance was separated from prostaglandin E2 by reverse-phase high-performance liquid chromatography. The purified urinary extract was examined by the enzyme immunoassay for prostaglandin E2, and the validity of the results was confirmed by gas chromatography-selected ion monitoring.     

The preparation of bacterial luciferase conjugates for immunoassay and application to rubella antibody detection

Bacterial luciferase has been modified with the thiolating reagent S-acetylmercaptosuccinic anhydride and covalently crosslinked to either Staphylococcus aureus protein A or anti-human immunoglobulin G (IgG) with the heterobifunctional reagent m-maleimidobenzoic acid N-hydroxysuccinimide ester. The conjugates retain enzymatic light-emitting activity and have the ability to bind IgG antibody. The ability of these conjugates to detect human IgG has been demonstrated by application to rubella immunity screening. Rubella antibodies are isolated from serum on the surface of rubella antigen-coated tubes and subsequently determined by light emitted from bound conjugate. In a preliminary study, the bioluminescent immunoassay has been compared to a commercial rubella antibody radioimmunoassay and found to be comparable in the ability to determine rubella immunity.