WO1989005978A1 - Dispositif d'immuno-analyse en couches contenant une barriere de courant de fluide - Google Patents

Dispositif d'immuno-analyse en couches contenant une barriere de courant de fluide Download PDF

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Publication number
WO1989005978A1
WO1989005978A1 PCT/US1988/004459 US8804459W WO8905978A1 WO 1989005978 A1 WO1989005978 A1 WO 1989005978A1 US 8804459 W US8804459 W US 8804459W WO 8905978 A1 WO8905978 A1 WO 8905978A1
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WIPO (PCT)
Prior art keywords
reactive zone
enzyme
fluid flow
antigens
antibodies
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PCT/US1988/004459
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English (en)
Inventor
Lance A. Liotta
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Liotta Lance A
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Publication of WO1989005978A1 publication Critical patent/WO1989005978A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • G01N33/54386—Analytical elements

Definitions

  • the present invention relates to an improved device and method for determining the presence of antigens and/or antibodies in sample fluids. More particularly, the present invention is directed to improvements in the immunoassay field, specifically in layered immunoassays containing immobilized antigens such as that described in Liotta, U.S. Patent No. 4,446,232.
  • the Liotta '232 patent discloses an immunoassay device fabricated out of matrix material having a first layer or zone impregnated with specific enzyme-linked antibodies which are capable of immunologically reacting with the antigens being tested for, a trapping layer or zone containing bound and immobilized antigens which are of the type recognized by the antibodies of the first layer, and a third layer or zone containing a color forming substrate which reacts with the enzyme linked to the antibodies.
  • the free antigens in the sample combine with the enzyme- linked antibodies of the first layer to form antigen- antibody(enzyme-linked) complexes which freely diffuse through the trapping layer into the third layer to produce a color reaction. If the fluid sample contains no antigens, all of the enzyme-linked antibodies will have free binding sites and will combine with the immobilized antigens present in the trapping layer, and no color reaction will be produced.
  • the device as originally described by the Liotta patent does not have the desired degree of sensitivity. This is because the reaction between the free antigens in the test sample and enzyme-linked antibodies present in the first layer occurs as the fluid passively flows or permeates through the test strip. As a resu]t of this fairly quick fluid flow process, antigens in low abundance may not have enough time to react sufficiently with the enzyme linked antibodies.
  • Dr. Liotta the present, as well as the original inventor of the Liotta immunoassay, has done a great deal of research in order to develop a built-in delay mechanism which would allow the free antigens present in the sample fluid and the enzyme-linked antibodies of the first layer to react for a longer period of time before entering the trapping layer. It has been discovered that as a result of this increased incubation period, a greater number of antigen-antibody(enzyme-linked) complexes can be formed, thereby increasing the color forming reaction produced in the substrate zone and in turn improving the sensitivity of the assay.
  • the present invention concerns the addition of an enzymatically regulated fluid flow barrier between the first reactive zone and the trapping layer of the immunoassay to act as such a delay mechanism.
  • the enzymatically regulated fluid flow barrier increases the incubation period for the formation of the antigen- antibody(enzyme-linked) complexes in the first reactive zone, and overcomes the problem of short unregulated incubation time in the first zone of the Liotta device as it was originally described, resulting in an immunoassay exhibiting improved sensitivity.
  • the present invention concerns a device for detecting the presence of antigens in a sample fluid which comprises a first reactive zone containing bacterial collagenase and enzyme-labeled antibodies which are capable of immunologically reacting with the antigens being tested for.
  • a protease regulated fluid flow barrier is operably connected to the first reactive zone of the device and the barrier is composed of a sufficient amount of collagen to allow fluid flow only when degraded by the bacterial collagenase of the first reactive zone.
  • a second reactive zone having two interconnecting matrix layers, i.e. a trapping layer and a substrate layer is also operably connected to the fluid flow barrier of the device.
  • the trapping layer contains bound and immobilized antigens which are of the type recognized by the enzyme- linked antibodies of the first reactive zone.
  • the substrate layer contains material capable of reacting with the enzyme linked to the enzyme-linked antibodies of the first reactive zone to produce a color forming reaction.
  • the present invention is directed to a unique method for detecting the presence of antigens in a sample fluid which comprises bringing a fluid which is to be tested for the presence of antigens into contact with a device having a first reactive zone, an enzyme regulated fluid flow barrier, and a second reactive zone.
  • the first reactive zone is composed of a matrix layer or reservoir containing dried or lyophilized bacterial collagenase and enzyme-linked or otherwise labeled antibodies which are capable of immunologically reacting with the antigens being tested for.
  • a protease regulated fluid flow barrier is operably connected to the first reactive zone of the device and the barrier is composed of a sufficient amount of collagen to allow fluid flow only when sufficiently degraded by the bacterial collagenase of the first reactive zone.
  • a second reactive zone having two interconnecting matrix layers, i.e. a trapping layer and a substrate layer, is also operably connected to the fluid flow barrier of the device.
  • the trapping layer contains bound and immobilized antigens which are of the type recognized by the enzyme-linked antibodies of the first reactive zone and the substrate layer contains material capable of reacting with the enzyme linked to the antibodies of the first reactive zone to produce a color forming reaction.
  • the present invention concerns a device for detecting the presence of antibodies in a sample fluid comprising a first reactive zone containing bacterial collagenase and enzyme-linked antigens which are capable of immunologically reacting with the antibodies being tested for.
  • a protease regulated fluid flow barrier is operably connected to the first reactive zone of the device, and the barrier is composed of a sufficient amount of collagen to allow fluid flow only when degraded by the bacterial collagenase of the first reactive zone.
  • a second reactive zone having two interconnecting matrix layers, i.e. a trapping layer and a substrate layer, is also operably connected to the fluid flow barrier of the device.
  • the trapping layer contains bound and immobilized antibodies which are of the type recognized by the enzyme- linked antigens of the first reactive zone.
  • the substrate layer contains material capable of reacting with the enzyme linked to the antigens of the first reactive zone to produce a color forming reaction.
  • the instant invention is directed to a unique method for detecting the presence of antibodies in a sample fluid which comprises bringing a fluid which is to be tested for the presence of antibodies into contact with a device having a first reactive zone, an enzyme regulated fluid flow barrier, and a second reactive zone.
  • the first reactive zone is composed of a matrix layer or reservoir containing bacterial collagenase and enzyme-linked antigens which are capable of immunologically reacting with the antibodies being tested for.
  • a protease regulated fluid flow barrier is operably connected to the first reactive zone of the device.
  • the barrier is composed of a sufficient amount of collagen to allow fluid flow only when degraded by the bacterial collagenase of the first reactive zone.
  • a second reactive zone having two interconnecting layers, i.e. a trapping layer and a substrate layer, is also operably connected to the fluid flow barrier.
  • the trapping layer contains bound and immobilized antibodies which are of the type recognized by the enzyme-linked antigens of the first reactive zone and the substrate layer contains material capable of reacting with the enzyme linked to the enzyme-linked antigens of the first reactive zone to produce a color forming reaction.
  • FIGURE 1 is a diagrammatical illustration of the device 10 which may be utilized to detect the presence of antigens in sample fluids.
  • Device 10 is constructed in four distinct layers, 12, 13, 14, and 16.
  • Layer 12 forms the first reactive zone 18 and is fashioned from a porous material which has dispersed therein, enzyme-linked antibodies 24, which are capable of immunologically reacting with the antigen being tested for, and bacterial collagenase 25.
  • Layer 13 is an enzyme regulated fluid flow barrier which separates the first reactive zone 18 from the second reactive zone 20 and is composed, at least in part, of collagen.
  • Layers 14 and 16 form the second reactive zone 20.
  • Layer 14 is formed of a porous material and has bound thereto antigens 26 which are of the type recognized by enzyme-linked antibodies 24.
  • Layer 16 is also fabricated from a porous material and contains a color forming reagent 17 which generates a signal in the presence of the enzyme linked to the antibodies 24.
  • the device 10 is shown positioned on a supporting member 22.
  • FIGURES 2A, 2B, and 2C are diagrammatical illustrations showing the utilization of the device of FIGURE 1 for the detection of antigens in sample fluids.
  • a sample fluid generally identified by the numeral 28, containing free antigens 32
  • the enzyme- linked antibodies 24 and the bacterial collagenase 25 become solubilized.
  • Free antigens 32, of the sample fluid 28 then contact and bind to some of the soluble enzyme- linked antibodies 24 present in layer 12 to form antigen- antibody (enzyme-linked) complexes 34 with saturated recognition sites.
  • the collagen fluid flow barrier 13 prevents the fluid containing the free antigens 32, the soluble enzyme-linked antibodies 24 and the antigen- antibody(enzyme-linked) complexes 34 from diffusing into layer 14. As a result of the increased incubation period due to the collagen fluid flow barrier 13, additional antigen-antibody(enzyme-linked) complexes 34 with saturated recognition sites are formed in layer 12 while the bacterial collagenase 25 begins to degrade the collagen fluid flow barrier 13.
  • the collagen fluid flow barrier 13 is digested by the bacterial collagenase
  • the fluid containing the antigen-antibody(enzyme- linked) complexes 34 having saturated recognition sites then freely diffuses through layer 14 and enters layer 16 where the enzyme linked to the antibodies of the antigen- antibody complexes 34 reacts with the color forming reagent 17 to produce a color which indicates the presence of the antigens 32 in the sample (FIGURE 2C) .
  • FIGURES 3A, 3B, and 3C are a diagrammatical illustration showing the method of the invention using the device of FIGURE 1 and showing what happens when the test fluid is devoid of antigens.
  • a fluid generally designated 34
  • the enzyme-linked antibodies 24 and the bacterial collagenase 25 are solubilized (FIGURE 3A) .
  • the collagen fluid flow barrier 13 is digested by the bacterial collagenase 25, allowing the fluid containing the soluble enzyme-linked antibodies 24 to diffuse into layer 14 (FIGURE 3B) , where the enzyme-linked antibodies 24 become attached to the bound and immobilized antigens 26. Accordingly, no enzyme-linked antibodies 24 reach the color forming reagent 17 in the second zone 20 (layer 16) and no color change is observed (FIGURE 3C) , indicating that the sample fluid 34 is devoid of antigen.
  • FIGURE 4 is a diagrammatically illustration of device 40, which is an alternative embodiment of the present invention.
  • Device 40 may be utilized to detect the presence of antibodies as opposed to antigens in sample fluids and is constructed of the same layers and zones as in device 10. However, device 40 contains in layer 12, enzyme-linked antigens 36, and not the enzyme-linked antibodies of device 10. In addition, device 40 contains in layer 14, bound antibodies 38, and not the bound antigens of device 10.
  • FIGURES 5A, 5B, and 5C are diagrammatical illustrations showing the utilization of the device of FIGURE 4 for the detection of antibodies in sample fluids.
  • a sample fluid generally identified by the numeral 42, containing free antibodies 44
  • the enzyme- linked antigens 36 and the bacterial collagenase 25 become solubilized.
  • Free antibodies 44, of the sample fluid 42 then contact and bind with most the soluble enzyme-linked antigens 36 present in layer 12 to form antibody- antigen(enzyme-linked) complexes 46 with saturated recognition sites.
  • the collagen fluid flow barrier 13 _g The collagen fluid flow barrier 13 _g .
  • the collagen fluid flow barrier 13 is digested by the bacterial collagenase 25, allowing the fluid containing the soluble enzyme-linked antigens 36 and the antibody-antigen(enzyme- linked) complexes 46 with saturated recognition sites to diffuse into layer 14 (FIGURE 5B) , where the remaining enzyme-linked antigens 36 become attached to the bound antibodies 38.
  • the fluid containing the antibody- antigen (enzyme-linked) complexes 46 having saturated regulated sites then freely diffuses through layer 14 and enters layer 16 where the enzyme-linked to the antigen of the antibody-antigen complexes 46 reacts with the color forming reagent 17 to produce a color which indicates the presence of the antibodies 44 in the sample (FIGURE 5C) .
  • FIGURES 6A, 6B, and 6C are diagrammatical illustrations of the method of the invention using the device of FIGURE 4 and showing what happens when the test fluid is devoid of antibodies.
  • a fluid generally designated 48
  • the enzyme-linked antigens 36 and the bacterial collagenase 25 are solubilized (FIGURE 6A) .
  • the collagen fluid flow barrier is digested by the bacterial collagenase 25, allowing the fluid containing the soluble enzyme-linked antigens 36 to diffuse into layer 14 (FIGURE 6B) , where the enzyme-linked antigens 36 become attached to the bound and immobilized antibodies 38. Accordingly, no enzyme-linked antigens 36 reach the color forming reagent 17 in the second zone 20 (layer 16) and no color change is observed (FIGURE 6C) , indicating that the sample is devoid of antibodies.
  • the present invention relates to an improved method and device for determining the presence of antigens in sample fluids.
  • the present invention is directed to the addition of an enzymatically regulated fluid flow barrier between the first reactive zone and the trapping layer of the immunoassay device of the type disclosed in Liotta, U.S. Patent No. 4,446,232. It has been discovered that the addition of the enzymatically regulated fluid flow barrier enhances the incubation period for the antigen-antibody reaction occurring in the first reactive zone between the enzyme-linked antibodies presented therein and the antigens found in the sample fluid.
  • the device of the present invention includes (see FIGURE 1) a first reactive zone having a matrix layer containing dried or lyophilized bacterial collagenase and enzyme-linked antibodies which are capable of immunologically reacting with the antigens being tested for.
  • Attached to the first reactive zone is a protease type enzyme regulated fluid flow barrier which is composed of a sufficient amount of collagen to allow fluid flow only when degraded by the bacterial collagenase of the first reactive zone.
  • a second reactive zone is attached to the fluid flow barrier having a matrix layer containing bound and immobilized antigens which are of the type recognized by the enzyme-linked antibodies of the first reactive zone (i.e.
  • the trapping layer a matrix layer containing material capable of reacting with the enzyme linked to the enzyme-linked antibodies of the first reactive zone to produce a color forming reaction to indicate the presence of antigens in the sample fluid (i.e. the substrate layer) .
  • FIGURES 2A, 2B, and 2C The fluid sample, containing the antigen being tested for, is placed in contact with the first reactive zone of the device. As the sample fluid diffuses through the first reactive zone, the enzyme-linked antibodies and the bacterial collagenase presented therein become solubilized. The free antigens of the sample fluid then contact and bind with most of the soluble enzyme- linked antibodies to form antigen-antibody(enzyme-linked) complexes with saturated recognition sites.
  • the collagen fluid flow barrier inhibits or prevents the fluid containing the free antigens being tested for, the soluble enzyme-linked antibodies and the antigen-antibody(enzyme- linked) complexes with saturated recognition sites from diffusing out of the first reactive zone and into the second reactive zone. As a result of the increased incubation period, due to the collagen fluid flow barrier preventing the diffusion of the fluid, etc. , additional antigen-antibody(enzym -linked) complexes with saturated recognition sites are formed.
  • the solubilized bacterial collagenase also present in the first reactive zone begins to degrade the attached collagen fluid flow barrier.
  • the collagen fluid flow barrier is digested by the collagenase, allowing the fluid containing the remaining soluble enzyme- linked antibodies and antigen-antibody(enzyme-linked) complexes with saturated recognition sites to diffuse into the second reactive zone.
  • the leftover enzyme-linked antibodies become attached to the bound and immobilized antigens present in the trapping layer of the second reactive zone.
  • the complexes freely diffuse through the bound and immobilized antigens of the trapping layer into the substrate layer of the second reactive zone where the enzyme linked to the antibodies of the antigen- antibody(enzyme-linked) complexes reacts with the substrate to produce a color forming reaction which indicates the presence of antigens in the sample.
  • the concentration of antigen in the test sample will be reflected in the level of the color reaction over time in the substrate layer. A darker color will indicate a higher concentration of antigen.
  • the fluid sample is devoid of free antigens
  • no color reaction will be produced in the substrate layer of the second reactive zone of the present invention.
  • the enzyme-linked antibodies of the first reactive zone will have free binding sites (i.e. no free antigens in the sample fluid to bind with) when the collagen fluid flow barrier is digested by the solubilized collagenase (see FIGURES 3A, 3B, 3C) .
  • the enzyme-linked antibodies with the free binding sites combine with the bound and immobilized antigens of the trapping zone.
  • no enzyme-linked antibodies reach the color forming substrate layer of the second reactive zone and no color change is observed, indicating the sample fluid is devoid of antigens.
  • the technique of the present invention is equally applicable to both the detection of antibodies as well as antigens in sample fluids (see FIGURE 4) .
  • the roles of the antigens and the antibodies present in the invention would be simply reversed.
  • antigens, as opposed to antibodies, linked with enzymes are present with the bacterial collagenase in the first reactive zone and referenced antibodies, as opposed to antigens, are immobilized in the trapping layer of the second reactive zone.
  • the same materials utilized in the first embodiment of the invention, including the collagen fluid flow barrier, are also used in the adapted version of the invention.
  • the operation of the adapted version for the detection of antibodies in sample fluids is also similar to the first device utilized to detect the presence of antigens in sample fluids (see FIGURES 5A, 5B, and 5C) .
  • the enzyme-linked antigens and the bacterial collagenase present in the first reactive zone become solubilized.
  • antibody-antigen(enzyme- linked) complexes with saturated recognition sites are formed between the antibodies present in the sample fluid and the enzyme—linked antigens of the first reactive zone.
  • the collagen fluid flow barrier is digested by the collagenase, allowing the fluid containing the remaining enzyme-linked antigens and the antibody-antigen(enzyme- linked) complexes with saturated recognition sites to diffuse into the second reactive zone, where the leftover enzyme-linked antigens bind with the immobilized antibodies of the trapping layer.
  • the fluid containing the antibody- antigen(enzyme-linked) complexes with saturated recognition sites freely diffuses through the trapping layer into the substrate layer of the second reactive zone where the enzyme linked to the antigen of the antibody- antigen(enzyme-linked) complexes reacts with the substrate to produce a color forming reaction which indicates the presence of antibodies in the sample fluid.
  • the operation of the adapted device for sample fluids devoid of free antibodies is also similar to that described above.
  • No color forming reaction will occur in the substrate layer because the enzyme-linked antigens of the first reactive zone will diffuse, upon digestion of the collagenase fluid flow barrier, into the trapping layer of the second reactive zone where all of the immobilized antibodies present therein will bind with the enzyme-linked antigens. Since no free antibodies are present in the sample fluid, no antibody-antigen(enzyme-linked) complexes will be formed. Hence, no color transformation will occur in the substrate layer of the second zone.
  • the materials utilized to fabricate the first and second reactive zones of the present invention are similar to those disclosed in Liotta, U.S. Patent No. 4,446,232.
  • the zones may be constructed from interwoven fibers succh as cellulose, nitrocellulose, ethylcellulose , or diazobenzyloxymethyl (DBM) paper, and/or Pall nylon or polyvinyldene difluoride membranes.
  • Nitrocellulose paper directly binds proteins and has been shown to be useful for immobilizing antigens.
  • DBM paper binds DNA, RNA, and proteins by means of covalent linkages to the diazonium group.
  • Nylon and polyvinyldene difluoride membranes have been found useful for binding proteins including IgG.
  • zone 1 can be an open reservoir containing lypholized bacterial collagenase and enzyme linked antibodies. The outflow from the bottom of the reservoir which leads to the trapping zone is blocked by the fluid flow barrier.
  • porous gels resistant to enzyme degradation by bacterial collagenases such as polyacrylamide or agarose can be utilized to fabricate the reactive zones.
  • the antigens can be trapped within the pores of the gel, or they can be cross-linked to the gel via amino groups of the ligand and carboxylic groups of the matrix.
  • particles or beads containing the bound ligands trapped within a cellulose or plastic fiber matrix can also be used.
  • a satisfactory example is polyacrylamide beads, 5-10 microns in diameter, with antigens bound to the surface via peptide bonds. The beads are trapped within a cellulose filter matrix of pore size 1-2 microns.
  • the fluid flow barrier may be constructed out of collagen which is the main protein component of bone, cartilage and connective tissue.
  • the collagen layer prevents the fluid present in the first reactive zone from diffusing into the second reactive zone of the device.
  • a suitable collagen matrix is that formed by bovine type I collagen in triple helical (native) or denatured (gelatin) form.
  • the collagen can be used alone or with an additive of sugar polymer, cellulose, or non-collagenous proteins.
  • the collagen barrier can be formed as a dry sheet or coated onto one side of either the first reactive zone or the trapping layer of the second reactive zone.
  • the collagen barrier can also be impregnated into a porous material.
  • Clostridium perfinorens and Clostridium histolvticum produce specific collagenases which are capable of recognizing amino acid sequences specific for collagen and degrading collagen into small peptides.
  • the preferred bacterial collagenase utilized in the instant invention is that produced by the microorganism, Clostridium histolvticum, which can be obtained from commercial sources such as Boehringer Mannheim.
  • the present invention incorporates the collagen fluid flow barrier and the specific bacterial collagenases set forth above into the device in order to act as a built- in delay mechanism for allowing the fluid present in the first reactive zone, to diffuse, upon degradation of the collagen barrier, into the second reactive zone of the device.
  • the amount of time required for the degradation of the collagen fluid flow barrier depends on the concentration of the collagenase present in the first reactive zone, as well as the composition and thickness of the collagen layer. In this regard, the following degradation periods were determined for various concentrations of bacterial collagenase and various thicknesses of collagen layers:
  • the amount of bacterial collagenase present in the first reactive zone and the thickness of the collagen fluid flow barrier utilized for each device determines or regulates the amount of increased incubation time desired.
  • Suitable substrates or color forming reagents are well known in the art.
  • a number of different types of purified enzymes are commonly labeled reagent for immunoassays, such as ELISA. These include horseradish peroxidase, alkaline phosphates, and beta- galactosidase.
  • the present invention is not limited to the use of these enzymes to label the antibody or antigen.
  • Other enzyme substrates combinations well known in the art may also be utilized.
  • the enzyme used to label the antibodies or antigens can produce a color in the second reactive zone of the test device by acting directly or indirectly with the color forming agent.
  • substrates well known in the art such as diaminobenzidine or p- nitrophenylphosphate react with horseradish peroxidase in the presence of hydrogen peroxide to form a brown to black color.
  • hydrogen peroxide is added exogenously during the use of the device.
  • the lyophilized color forming substrate layer can contain bound glucose oxidase and the first reactive zone can contain glucose. Upon use of the device, the glucose in the first reactive zone diffuses upon degradation of the collagen fluid flow barrier into the second reactive zone and generates hydrogen peroxide by reacting with the glucose oxidase.
  • Example 1 Utilization of a layered immunoassay device containing a fluid flow barrier for the detection of theophylline in biological samples.
  • This stable intermediate (8-carboxylpropyl theophylline) was attached to bovine serum albumin (BSA) by carbodiimide medicated coupling using l-ethyl-3 (3-dimethyl amino propyl) carbodiimide (EDC) .
  • BSA bovine serum albumin
  • EDC l-ethyl-3 (3-dimethyl amino propyl) carbodiimide
  • the resulting product (8- carboxypropyl theophylline BSA) was dialyzed in deionized water and lyophilized.
  • the theophylline hapten produced by the above reactions is then injected into mammals which are repeated immunized.
  • the mammals are then sacrificed and the antiserum is collected and purified by affinity chromatography utilizing controlled pore glass (CPG) the solid matrix.
  • CPG controlled pore glass
  • Preactivated horseradish peroxidase is then injected into the affinity column and reacted with the purified antibodies.
  • excess enzyme is eluted with phosphate buffer from the affinity column.
  • the theophylline antibodies linked with the enzyme are then eluted from the affinity column and collected for use with the present invention.
  • Tris buffer solution (pH 7.6) containing 0.05 M Tris, 0.2 M NaCl, 0.01 M CaCl 2 , 2% w/v ovalbumin and 5 ug/ml of the anti-theophylline antibody peroxidase conjugate produced above, was mixed with various concentrations (i.e. from 0 to 0.5% w/v) of a bacterial collagenase obtained from Clostridium histolvticum (0.28 u/mg, Boehringer Mannheim 103578) .
  • Pieces of cellulose filter paper (coarse grade) were then impregnated with the antibody enzyme conjugate solutions containing the various concentrations of collagenase by dipping pieces of the filter paper into the solutions and allowing the pieces to dry for 40 minutes in an oven at 30 degrees C.
  • Bovine type I collagen was dissolved in distilled water at a concentration of 6.25% w/v.
  • the dried collagen was dissolved by the slow addition of the collagen to the water which had been previously heated to 90 degrees C.
  • the solution was poured into a mold and cooled to 4 degrees C to form a collagen gel 1.0 mm in thickness.
  • the gel was submerged in liquid nitrogen and then inserted into a chamber of a lyophilizer and freeze dried for 5 hours. The resulting dried layer was approximately 0.25 mm in thickness.
  • the theophylline-BSA hapten produced above was solubilized at a concentration of 10 mg/ml in phosphate buffered saline (PBS) at a pH of 7.2.
  • PBS phosphate buffered saline
  • a protein binding membrane of the derivatized nylon variety was immersed into the protein solution for 2 hours. The membrane was then removed, rinsed, and dried for 20 minutes in an oven at 40 degrees C.
  • Cellulose filter paper (coarse grade) was immersed in a solution containing 200 u/ml of glucose oxidase and 0.1% w/v of triton X-100 in acetate buffer (0.1 M NaH 2 P0 4 , and 0.05 M citric acid, pH 5.5) .
  • the filter paper was dried for 30 minutes in an oven at 40 degrees C and then immersed into a second solution containing 2 mg/ml tetramethyl benzidine and 15 mg/ml of B-D glucose in methanol and dried for one minute in an oven at 100 degrees C.
  • F Preparation of the layered immunoassay device containing a fluid flow barrier
  • the dried layers were cut into squares or circles of the following dimensions:
  • the device was then constructed by attaching the side of each layer in reverse order to a piece of polycarbonate plastic having on one side a strip of double- sided clear micro-industrial tape.
  • the substrate layer was first attached on one side via the double-sided tape to the plastic strip.
  • the trapping layer containing the immobilized antigens was then laid on top of the substrate layer and attached on its side to the plastic strip.
  • the collagen fluid flow barrier was laid on top of the trapping layer and attached on its side to the plastic strip.
  • the first reactive zone containing the collagenase and the antibody-enzyme conjugates was laid on top of the collagen layer and attached on one side to the plastic strip.
  • the plastic strip containing the attached layers was then covered with micro-industrial tape to prevent excess fluid flow. A small hole for receiving the sample fluid was inserted into the tape covering the first reactive zone.
  • human serum samples containing theophylline assayed at 0, 0.5, and 15 ug/ml were utilized to determine the effectiveness of the collagen fluid flow barrier in test strips containing various concentrations of collagenase in the antibody- enzyme conjugate zone (i.e. the first reactive zone) .
  • approximately 50 microliters of the human serum samples containing the various amounts of theophylline were applied to the surface of the first reactive zone (i.e. the antibody-enzyme conjugate zone containing the collagenase) of the test strips fabricated as described above.
  • the amount of time required by the collagenase to degrade the collagen fluid flow barrier was determined for each zone.
  • the color density of the substrate layer for each test strip was also determined after 2 (two) minutes. The results obtained are set forth below.
  • 0color reflectance density is defined as a color reaction not distinguishable from background color reaction in the absence of sample antigen in which the maximum amount of free antibodies were trapped in the trapping zone.
  • the sensitivity of the test strips for the detection of theophylline in test samples increases as a result of the extended incubation periods for the antigen-antibody reaction to occur in the first reactive zone.
  • the sensitivity of the test strips for the detection of theophylline present at 0.5 ug/ml in the sample fluids increased from 0.12 color density units at an incubation period of 15 seconds to 0.31 color density units at an
  • the increase in the incubation periods is due to the addition of the collagen layer and the collagenase enzyme to the first reactive zone of the test strip.
  • the collagen layer acts as a fluid flow barrier between the first reactive zone (containing the bacterial collagenase and the enzyme-linked antibodies which are capable of immunologically reacting with the antigens of the second reactive zone) and the second reactive zone (containing immobilized antigens and the color forming substrate) of the test strip.
  • the incubation period for the antigen-antibody reactions to occur in the first reactive zone between the antigens existing in the test sample and the enzyme-linked antibodies present in the test strip is extended, depending upon the amount of collagenase enzyme present in the first layer and the composition of the collagen fluid flow barrier.
  • Example 2 Utilization of a la ered immunoassa
  • the hCG antigen standard was obtained from Monoclonal Antibodies, Inc., lot 10841, 50 mlU/ml hCG positive calibrator.
  • the conjugated anti hCG antibodies were obtained from Genesis Labs, Inc. (Minneapolis, MN) The method of conjugation was as set forth in Example 1.
  • This zone was fabricated as set forth in Example 1 except the enzyme linked antibodies utilized were the horseradish peroxidase conjugated anti-hCG monoclonal antibodies indicated above, and the collagenase enzyme concentration was approximately 0.05% w/v.
  • the trapping zone was fabricated from the nylon based membrane utilized in Example 1 except that the antigen used was approximately 1000 mlV of Beta hCG.
  • the components of the layered immunoassay device were assembled according to Example 1, except that the collagenase enzyme concentration of the first reactive zone was consistently about 0.05% w/v in each test strip.
  • 50 microliters of a test sample containing hCG antigens (50 lU) and 50 microliters of a test sample devoid of hCG antigen were applied to both a layer immunoassay device containing a fluid flow barrier and a layer immunoassay device lacking such a barrier.
  • the amount of time required for the fluid to enter the substrate layer of each test strips, as well as the color density of the substrate layer, were determined and set forth below.
  • the fluid flow barrier increases the incubation period for the antigen- antibody reaction to occur in the first reactive zone of the test strips.
  • the sensitivity of the assays to determine the presence of hCG antigen in test samples is also increased. For example, when only 50 mlU was present in the test sample, a strong positive blue color was exhibited in the assay containing the fluid flow barrier. However, when the sample containing the hCG was tested with the assay lacking the fluid flow barrier, a weak blue color was observed.
  • the addition of the collagen fluid flow barrier and the corresponding collagenase enzyme to the layered immunoassay devices increased the incubation time from 15 seconds to 3.25 minutes, resulting in a significant increase in sensitivity.

Abstract

La présente invention se rapporte à un procédé et à un dispositif améliorés qui servent à détecter la présence d'antigènes dans des échantillons de fluide. Ledit procédé consiste à placer le fluide à tester pour déterminer la présence d'antigènes en contact avec le dispositif, lequel comporte une première zone réactive (18), une barrière de courant de fluide régulée par enzyme (13) et une seconde zone réactive (20). La première zone réactive (18) se compose d'une couche matricielle (12) contenant de la collagénase bactérienne et des anticorps à liaison enzymatique (24) qui ont le pouvoir de réagir immunologiquement avec les antigènes faisant l'objet du test. Une barrière de courant de fluide régulée par enzyme (13) est connectée opérationnellement à la première zone réactive (18) du dispositif et la barrière (13) est constituée par une quantité suffisante de collagène pour permettre l'écoulement du fluide lorsqu'elle est dégradée par la collagénase bactérienne de la première zone réactive. Une seconde zone réactive (20), qui comporte deux couches matricielles (14, 16) reliées entre elles, à savoir une couche de piégeage (14) et une couche de substrat (16), est également connectée opérationnellement à la barrière de courant de fluide (13) du dispositif. La couche de piégeage (14) contient des antigènes liés et immobilisés, qui sont reconnus par les anticorps à liaison enzymatique (24) de la première zone réactive (18), et la couche de substrat (16) contient une substance pouvant réagir avec l'enzyme liée aux anticorps à liaison enzymatique (24) de la première zone réactive (18), afin de produire une réaction colorée. Après un temps suffisant pour permettre à l'échantillon de fluide de pénétrer le dispositif par infiltration, on observe la présence ou l'absence d'un changement de couleur dans la seconde zone réactive pour déterminer la présence des antigènes recherchés dans ledit échantillon de fluide.
PCT/US1988/004459 1987-12-14 1988-12-13 Dispositif d'immuno-analyse en couches contenant une barriere de courant de fluide WO1989005978A1 (fr)

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EP0418765A2 (fr) * 1989-09-21 1991-03-27 Becton, Dickinson and Company Appareil d'analyse comportant des moyens de contrôle de flux
WO1993003175A1 (fr) * 1991-07-29 1993-02-18 Serex, Inc. Procede et dispositif permettant de detecter la presence d'un analyte dans un echantillon
EP0547114A1 (fr) * 1990-09-07 1993-06-23 THE GOVERNMENT OF THE UNITED STATES OF AMERICA, as represented by THE SECRETARY OF THE NAVY Microanalyse sur une carte
WO1997035205A1 (fr) * 1996-03-20 1997-09-25 Serex, Inc. Dispositif chromatographique de dosage immunologique et procede d'utilisation de la valence des particules pour la quantification
EP0884594A2 (fr) * 1997-06-13 1998-12-16 Giorgio Torelli Dispositif immunochromatographique pour la fixation d'un analyte
US6258548B1 (en) 1997-06-05 2001-07-10 A-Fem Medical Corporation Single or multiple analyte semi-quantitative/quantitative rapid diagnostic lateral flow test system for large molecules
US6306665B1 (en) 1999-10-13 2001-10-23 A-Fem Medical Corporation Covalent bonding of molecules to an activated solid phase material
US6699722B2 (en) 2000-04-14 2004-03-02 A-Fem Medical Corporation Positive detection lateral-flow apparatus and method for small and large analytes
US7611860B2 (en) * 2000-10-13 2009-11-03 Cambridge Meditech Limited Indicator for in-situ detecting of lysozyme
US7718375B2 (en) 2002-02-27 2010-05-18 Binax, Inc. Modification of bioassays for detection of antigens characteristic of bacteria that are causative of ear and respiratory infections to eliminate false positive results caused by nasopharyngeal colonization of children
JP2017026635A (ja) * 2005-12-21 2017-02-02 メソ スケール テクノロジーズ エルエルシー アッセイ試薬を具備するアッセイモジュールとその製造方法およびその使用方法
US11300571B2 (en) 2005-12-21 2022-04-12 Meso Scale Technologies, Llc. Assay apparatuses, methods and reagents

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FR2630827B1 (fr) * 1988-04-28 1994-06-03 Oris Ind Dispositif et procede pour la determination qualitative et quantitative rapide de la presence d'un ligand reactif dans un fluide

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US4446232A (en) * 1981-10-13 1984-05-01 Liotta Lance A Enzyme immunoassay with two-zoned device having bound antigens
US4522786A (en) * 1983-08-10 1985-06-11 E. I. Du Pont De Nemours And Company Multilayered test device for detecting analytes in liquid test samples

Cited By (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0418765A2 (fr) * 1989-09-21 1991-03-27 Becton, Dickinson and Company Appareil d'analyse comportant des moyens de contrôle de flux
EP0418765A3 (en) * 1989-09-21 1992-08-19 Becton Dickinson And Company Test device including flow control means
EP0547114A1 (fr) * 1990-09-07 1993-06-23 THE GOVERNMENT OF THE UNITED STATES OF AMERICA, as represented by THE SECRETARY OF THE NAVY Microanalyse sur une carte
EP0547114A4 (en) * 1990-09-07 1996-07-24 Us Health Microassay on a card
WO1993003175A1 (fr) * 1991-07-29 1993-02-18 Serex, Inc. Procede et dispositif permettant de detecter la presence d'un analyte dans un echantillon
US5451504A (en) * 1991-07-29 1995-09-19 Serex, Inc. Method and device for detecting the presence of analyte in a sample
US6121008A (en) * 1996-03-20 2000-09-19 Serex, Inc. Chromatographic immunoassay device and method utilizing particle valency for quantification
WO1997035205A1 (fr) * 1996-03-20 1997-09-25 Serex, Inc. Dispositif chromatographique de dosage immunologique et procede d'utilisation de la valence des particules pour la quantification
AU740812B2 (en) * 1996-03-20 2001-11-15 Serex, Inc. Chromatographic immunoassay device and method utilizing particle valency for quantitation
US6258548B1 (en) 1997-06-05 2001-07-10 A-Fem Medical Corporation Single or multiple analyte semi-quantitative/quantitative rapid diagnostic lateral flow test system for large molecules
EP0884594A2 (fr) * 1997-06-13 1998-12-16 Giorgio Torelli Dispositif immunochromatographique pour la fixation d'un analyte
US6306665B1 (en) 1999-10-13 2001-10-23 A-Fem Medical Corporation Covalent bonding of molecules to an activated solid phase material
US6699722B2 (en) 2000-04-14 2004-03-02 A-Fem Medical Corporation Positive detection lateral-flow apparatus and method for small and large analytes
US7611860B2 (en) * 2000-10-13 2009-11-03 Cambridge Meditech Limited Indicator for in-situ detecting of lysozyme
US7718375B2 (en) 2002-02-27 2010-05-18 Binax, Inc. Modification of bioassays for detection of antigens characteristic of bacteria that are causative of ear and respiratory infections to eliminate false positive results caused by nasopharyngeal colonization of children
JP2017026635A (ja) * 2005-12-21 2017-02-02 メソ スケール テクノロジーズ エルエルシー アッセイ試薬を具備するアッセイモジュールとその製造方法およびその使用方法
US11300571B2 (en) 2005-12-21 2022-04-12 Meso Scale Technologies, Llc. Assay apparatuses, methods and reagents
US11892455B2 (en) 2005-12-21 2024-02-06 Meso Scale Technologies, Llc. Assay apparatuses, methods and reagents

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