CA1267081A - Multizone analytical element having labeled reagent concentration zone - Google Patents

Multizone analytical element having labeled reagent concentration zone

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Publication number
CA1267081A
CA1267081A CA000506751A CA506751A CA1267081A CA 1267081 A CA1267081 A CA 1267081A CA 000506751 A CA000506751 A CA 000506751A CA 506751 A CA506751 A CA 506751A CA 1267081 A CA1267081 A CA 1267081A
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Prior art keywords
reagent
test device
analyte
immobilized
layer
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
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CA000506751A
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French (fr)
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CA1267081C (en
Inventor
Alfred C. Greenquist
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Bayer Corp
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Miles Laboratories Inc
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Priority to CA000506751A priority Critical patent/CA1267081A/en
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Publication of CA1267081C publication Critical patent/CA1267081C/en
Publication of CA1267081A publication Critical patent/CA1267081A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Classifications

    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366Apparatus specially adapted for solid-phase testing
    • G01N33/54386Analytical elements
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/52Use of compounds or compositions for colorimetric, spectrophotometric or fluorometric investigation, e.g. use of reagent paper and including single- and multilayer analytical elements
    • G01N33/525Multi-layer analytical elements
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S435/00Chemistry: molecular biology and microbiology
    • Y10S435/805Test papers
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S435/00Chemistry: molecular biology and microbiology
    • Y10S435/968High energy substrates, e.g. fluorescent, chemiluminescent, radioactive
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S436/00Chemistry: analytical and immunological testing
    • Y10S436/807Apparatus included in process claim, e.g. physical support structures
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S436/00Chemistry: analytical and immunological testing
    • Y10S436/807Apparatus included in process claim, e.g. physical support structures
    • Y10S436/81Tube, bottle, or dipstick
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S436/00Chemistry: analytical and immunological testing
    • Y10S436/815Test for named compound or class of compounds

Abstract

ABSTRACT OF THE DISCLOSURE

A multizone test device for the determination of analyte from a liquid test medium upon contact with the liquid test medium and a labeled reagent comprising a chemical group having a detectable physical property. The test device preferably com-prises multilayers including a reagent layer incor-porated with an immobilized reagent and a detection layer incorporated with an immobilized form of a binding substance for the labeled reagent. The im-mobilized reagent and the labeled reagent comprise specific binding partners which will bind to each other dependent upon the amount of analyte present.
Labeled reagent which does not become bound to the immobilized reagent in the reagent layer migrates into the detection layer and becomes bound to and immobilized by the immobilized binding substance therein. As a result, reverse migration of the lab-eled reagent into the reagent layer is prevented and the detectable physical property provided by the label of the labeled reagent is localized in the de-tection layer for the precise measurement thereof and correlation to the amount of analyte in the test medium.

Description

MULTIZONE ANALYTICAL ELEMENT HAVING
LABELED REAGENT CONCENTRATION ZONE

BACKGROUND OF THE INVENTION

Field of the Invention The present invention relates to multizone analytical elements which are useful for the determination of an analyte in a liquid test medium. In particular, the present invention relates to multilayer immunoassay test devices involving the use of labeled reagents comprising a chemical group having a detectable physical property such as fluorescence or color.

Description of the Prior Art Multizone analytical elements or test devices have been pxeviously proposed and have been applied to binding assays, e.g., immunoassays, which depend upon the ability of an antibody or antigen to bind to a specific analyte for the determination of the analyte in the liquid test medium. Such assays include those immunoassays where a labeled reagent, such as a labeled form of the analyte or an antibody thereto, participates in an antigen-antibody reaction to form a free species and a bound species thereof such that the amount of :~67~

the labeled reagent in one of such species can be correlated to the amount of analyte in the liquid test medium. In principle, such assays are referred to as heterogeneous immunoassays because the free and bound species must be separated in order to complete the assay.
Multizone, particularly multilayer, analytical elements are now known in the art which inherently perform the required separation step so that no additional manipulations are needed after application of the liquid test medium. In general, such devices include a plurality of layers having the necessary reagents for carrying out an immunoassay and for accomplishing the necessary separation step incorporated therein. A number of such devices further include a detection layer from which the signal produced by a labeled reagent in . either the bound or free species is detected and measured. Detectable signals provided by such devices are usually optical in na~ure such as color changes, fluorescence, or the like. Alternatively, detection can be accomplished by electrochemical measurements using, for example, potentiometric or ampometric techniques.
For example, such multilayer immunoassa~
analytical elements are described by European Patent Publication No. 97,952 and &erman Publication No. DE-OS 3329728 where an immobilized form o a binding partner, such as an immobilized antibody to an antigen, and an antigen labeled with a detectable substance are incorporated therein.
Upon the application of a liquid test medium to such device, antigen from the test medium competes with labeled antigen incorporated into the device .

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for binding to the immobilized antibody.
Separation of the bound species from the free species occurs upon migration of the free species of the labeled antigen away from the immobilized zone.
Similarly, European Patent Publication Nos.
51,183 and 66,648 disclose such devices where the determination of antigen or antibody in a liquid test medium is dependent upon the competitive binding of the antigen (or antibody) with a labeled form of the antigen (or antibody) for an immobilized form of a binding partner thereof, such as immobilized antibody (or antigen).
Other multilayer immunoassay t~st devices have also been proposed, such as described in U.S.
Patent No. 4,258,001, which include one or more layers comprising particulate, three-dimensional lattices formed by a plurality of organopolymeric particlPs. The particles form interconnected void spaces which are claimed to provide for the transport o~ high molecular weight analytes therethrough. Although not required, it is suggested that interactive compositions, such as antigens or antibodies, can be immobilized onto the particles by providing active linking or binding sites on the particles to which such interactive compositions can be covalently bonded.
Another of such devices is described in U.S.
Patent No. 4,446,232 which is based on the 3Q principle of competition between bound and free species of analyte for a fixed number of recognition sites on an enzyme-labeled antibody.
The determination of analyte in a test sample depends upon the binding of the analyte to .

enzyme-labeled antibodies in one zone of the device and which then pass into another zone of the device where the enzyme activity of the enzyme-linked antibodies bound to analyte is detected. One of the zones further includes bound and immobilized analyte which competes with analyte from the test sample for binding to the enzyme-labeled antibodies and which bind and immobilize any of the enzyme-labeled antibodies which do not become bound to analyte fro~ the test sample.
A particular disadvantage, however, of such devices is that reverse fluid migration results in reaction products, which have migrated into the lower or detection layer, to migrate back up into the upper layers, resulting in chemical interferences and diminished test response. To overcome this disadvantage, analytical test devices have been proposed which attempt to localize or otherwise prevent such,reverse fluid migration of the reaction products.
For example, European Patent Publication Nos.
51,183 and 66,648 suggest layers for collection of the detectable reaction product comprising hydrophilic high molecular weight substances. EP
66,648 further suggests the incorporation of mordanting agents in the detection layer which have a strong interaction with the detectable reaction product in order to collect the detecta~le reaction product therein. Such mordanting agents include 3~ cationic polymers, anionic polymers and quaternary salts.
Similarly, U.S. Patent Nos. 4,144,306 and 4,042,335 disclose multilayer analytical elements which include a registration layer incorporated ~L~67~

with a mordant for a detectable species in order to collect the detectable species therein and thereby prevent diffusion or migration of the detectable species out of the registration layer.
A variation of such devices is disclosed by U.S. Patent No. 4,459,358 which describes a multilayer element comprising a spreading layer, a reaction layer incorporated with a diffusible labeled antibody, and a registration layer incorporated with materials adapted to non-specifically bind, immobilize or "mordant"
antibodies, such as latex particles. Upon application of a liquid test medium to the device, analyte from the test medium associates with the labeled antibody in the reaction layer and immunoprecipitates therein. Any of the labeled antibody which does not become bound to the analyte diffuses into the registration layer where it is immobilized by the mordant incorporated therein.
However, the use of mordantin~ agents can interfere with the prerequisite reactions which are necessary for the formation or release of the detectable reaction product as a result of non-specific binding of the mordanting agent. Such interference can make both detection and measurement unreliable, as well as decrease the sensitivity of the test device.
In attempts to overcome the disadvantages of mordanting agents in a registration layer, other analytical elements have been proposed employing mordanting agents in a layer other than a registration layer in order to prevent the migration of a formed detectable reaction product into a layer other than a registration or detection ~ ~67~
~ 6 --layer which would otherwise render the detectable reaction product undetectable. Such a device is disclosed by U.S. Patent ~o. 4,166,093 which includes a species migra-tion-inhibiting layer interposed between a radiation-blocking layer and a reagent layer of a`multilayer analytical element.
The detectable species miqration-inhibiting layer is permeable to analyte and fixes or otherwise prevents a significant portion of any detectable species, such as a dye formed in the reagent layer, from further migrating up into the - radiation-blocking layer. Such detectable species migration-inhibiting layer comprises a mordant for the particular detectable species formed in the reagent layer. However, such an inhibiting layer still presents the disadvantage of a mordanting agent which may interfere with reactions initiated by the presence of analyte and prevent or substantially inhibit the formation or release of the detectable species.
Still another attempt to overcome the problem of reverse fluid migration in multilayer analytical elements is disclosed by International Publication No. WO 84/02193 which provides for a chromogenic support immunoassay which comprises collection of an immune complex comprising analyte bound to an enzyme-labeled anti-analyte antibody on a porous or microporous support material. The support functions to concentrate the chromatic signal 3~ generated by the label component upon reaction with signal generating reagents in the support material.
Concentration of the chromatic signal results from covalent attachment of the reaction product to the support, and the problem of reverse fluid migration .

.~6'7~

being overcome by providing a single layer. The im-munoassay, however, requires a number of incubation and washing steps in order to localize and concen-trate the signal on the support. Although the im-munoassay overcomes reverse fluid migration by pro-viding a single layer support within which the nec-essary reactions for production of the chromatic signal occur, it still presents the disadvantages of extensive incubation and washing steps which are not necessary with a multilayer anal~tical element.
Accordingly, it is an object of the present in-vention to overcome the aforementioned disadvantages by providing a specific binding assay in a multizone, or multilayer, test device which concentrates the detectable response of a labeled reagent without in-terfering with the specific binding reactions in-volved in the assay.
Another object of the present invention is to provide, in a multizone, or multilayer, test device, a specific binding assay having an end point in the assay where further migration of the detectable spe-cies does not occur.
Further, it is an object of the present inven-tion to provide a sensitive specific binding assay for the highly accurate determination of analyte from a liquid test medium and which has substantially little or no background signal.

3L~6'7~

SUl~MARY OF THE INVENTION

The present invention provides a multizone test device for the determination of analyte from a liquid test medium based on binding interactions among the analyte, a labeled reagent, and an immobilized bind-ing substance for the labeled reagent~ The test de-vice comprises, in fluid flow contact, (1) a reagent zone incorporated with the immobilized reagent which will be an immobilized form of the analyte or a bind-ing analog thereof, or an immobilized form of a bind-ing partner of the analyte, depending on the immuno-assay scheme used, and (2) a detection zone incorpor-ated with an immobilized form of a binding substance for the labeled reagent. Tne labeled reagent is a form of a binding partner of the analyte, or a form of the analyte or a binding analog thereof, which is labeled with a chemical group having a detectable physical property and which further comprises a bind-ing site for the immobilized binding substance in the detection zone.
The present invention derives its principal ad-vantages from the use of a labeled reagent which has its own detectable property and which can be rendered immobilized in the detection zone by an inherent or introduced binding affinity. No separately migrat-able detectable species is generated as with prior art devices and immobilization and concentration of the response results from highly specific and strong binding interactions.

7~
_ 9 _ The immobilized reagent in the reagent zone and the labeled reagent are selected to comprise specific binding partners which will bind to one another dependent upon the amount of analyte present. When the labeled reagent is a labeled form of the analyte or an analog thereof, the immobilized reagent will be an immobilized form of a binding partner for the analyte, and the analyte and labeled reagent will compete for binding to the immobilized reagent. When the labeled reagent is a labeled form of a binding partner for the analyte, the immobilized reagent will be an immobilized form of the analyte or an analog thereof, and the labeled reagent thak does not become bound to analyte will become immobilized by binding to the immobilized reagent. Whether labeled analyte or labeled binding partners are involved, a portion of the labeled reagent will remain or become unbound to the immobilized reagent dependent upon the amount of analyte present.
The resulting labeled reagent which remains or becomes free to migrate within and out of the reagent zone then passes into the detection zone where the binding site of the labeled reagent binds with the immobilized binding substance in the detection zone. The resulting immobilized labeled reagent is prevented from migrating from the detection zone up into the reagent zone and the detectable chemicaI group of the labeled reagent provides a detectable physical signal in the detection zone which is measured and correlated to the amount of analyte in the test medium.

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BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a sectional view of a multilayer test device having a reagent layer and a detection layer constructed according to the present invention.
FIG. 2 is a section~l view of a multilayer test device having two reagent layers and a detection layer constructed according to the present invention.
FIG. 3 is a sectional view of a multilayer test device having two reagent layers, a detection layer, and a support constructed according to the present invention.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

The multizone test device of the present invention provides a specific binding assay in a zoned or layered test strip or device. The assay depends upon the partitioning of a labeled reagent, which is either applied to the device or incorporated within the device, between being retained in the reagent zone by being bound or immobilized to the immobilized reagent and being free to migrate into the detection zone. The present invention provides an advantageous means for concentrating the labeled reagent which migrates to the detection zone.
In order to simplify the disclosure hereinafter, the test device of the present invention will now be described pxincipally as comprising a layered structure. It will be understood that other types of zones can accomplish 67~

the same result. Also, the labeled reagent will be selected to be a labeled form of a binding partner of the analyte and the immobilized reagent will be selected to be an immobilized form of the analyte (with immobilized analyte being replaceable by an immobilized form of an analog of the analyte as is understood in the art).
In particular, the test device of the present invention comprises at least one reagent layer and a detection layer, and, as will be described in greater detail hereinafter, can further include a second reagent layer. 1'he reagent layer is incorporated with the immobili~ed reagent which comprises an immobilized form of the analyte which is not capable of being solubilized or otherwise removed from the reagent layer upon contact with the test medium. The detection layer is incorporated with an immobilized form of a binding substance for the labeled reagent, which binding ~o substance is similarly not capable of being solubilized or otherwise removed from the detection layer. Where a second reagent layer is employed, the first reagent layer is incorporated with the labeled reagent which is solubilized by the test medium when applied thereto, and the second reagent layer is incorporated with the immobilized form of the analyte.
It is to be appreciated that according to the - teachings of the present invention, the layers which comprise the test device are in fluid contact with one another whereby the layers of the test device which are associated with each other permit the diffusion of a fluid into and between these layers. Such fluid contact permits passage of at ~6~8~

least some components of a fluid sample, e.g., antigens, haptens, and/or antibodies, between the layers of the device and is preferably uniorm along the contact interface between the fluid contacting layers. Accordingly, upon application of the liquid test medium and labeled reagent to the reagent layer, the liquid test medium and labeled reagent are permitted to diffuse and permeate into and through the reagent layer and into the detection layer. Where a first and second reagent layer are provided, the liquid test medium is similarly permitted to diffuse and permeate into and through the first reagent layer whereby the labeled reagent incorporated therein is solubilized and the liquid test medium and the labeled reagent - urther diffuse and permeate into and within the second reagent layer and into and within the detection layer.
Once the liquid test medium and the labeled reagent have been applied to and permeate the reagent layer as heretofore described, if the analyte being detected is present in the liquid test medium~ then substantially all of the analyte present is brought into direct fluid contact with and specifically bound to the labeled reagent. As a result of the fluidity between the reagent layer and the detection layer, the resulting analyte-(labeled reagent) complex thereby formed is free to migrate within and out of the reagent layer 3Q and into the detection layer. As will be described in greater detail hereinafter 7 the labeled reagent preferably provides only one available binding site for binding of the analyte to the labeled reagent.
As a result, once such available binding site has 1~7~

been occupied by analyte, the analyte-(labeled reagent) complex is free to migrate within and out of the reagent layer without being immobilized by the immobllized analyte lncorporated therein.
Similarly, where a first and second reagent layer are provided, upon application of the liq~id test medium to the first reagent layer, the labeled reagent is solubilized and substantially all of the analyte present is brought into direct fluid contact with and specifically bound to the labeled reagent. The resulting analyte-(labeled reagent) complex thereby formed is permitted to migrate within and out of the first reagent layer, through the second reagent layer, and into the detection layer. Any of the labeled reagent which does not become bound to analyte from the test medium is bound to and immobilized by the immobilized analyte in the reagent layer, or, where a first and second reagent layer are provided, immobilized in the second reagent layer.
It is to be appreciated that according to the teachings of the present invention, once the analyte-(labeled reagent) complex migrates into the detection layer, the complex becomes specifically bound to and immobilized by a binding substance for s the labeled reagent which is immobilized in the detection layer. As will be described in greater detail hereinafter, the labeled reagent includes a chemical group having a detectable physical property, which, upon binding to the analyte from the liquid test medium and migration into the detection layer, can be detected, measured and correlated to the amount of analyte in the liquid test medium. Accordingly, immobilization of the .

~ ~;i7~

analyte-(labeled reagent) complex in the detection layer prevents migration of the complex out of the detection layer and into the reagent layer(s~ and permits the accurate and sensitive detection and measurement of all of the labeled reagent bound to analyte from the test medium in the detection layer.

Labeled Reagent and Detection Systems According to the teachings of the present invention, the labeled reagent comprises a chemical - group having a detectable physical property and a binding site for the binding substance immobilized in the detection layer. It is to be appreciated that the immobilized binding substance in the detection layer does not participate in the initial binding reaction among the analyte, labeled rèagent, and immobilized reagent. Accordingly, selection of an appropriate binding substance for immobilization in the detection layer necessarily depends upon the selective recognition for such binding site by the binding substance. Preferably, the labeled reagent comprises a ligand moiety which forms a specific binding pair with the binding substance. In particular, preferred representative binding pairs for the ligand moiety and the binding substance include such binding pairs as haptens and antibodies, or fragments thereof, to such haptens;
biotin and avidin; carbohydrates and lectins; and antibody, or fragment thereof, having an intact 3Q binding site for Protein A and Protein A; and the like. Additional binding pairs include complementary single stranded oligonucleotide ~6 sequences; effector molecules and receptor pairs;
prosthetic groups and apoprotein; enzyme cofactors and enzyme~, polymeric acids and bases~ dyes and protein binders; peptides and specific protein binders (e.g., ribonuclease, S-peptide and ribonuclease S protein?; enzyme inhibitors Ireversible and irreversible~, lenzymes and the like.
Further, the labeled reagent can be selectively immobilized by binding to an adsorbent material for the labeled reagent, such as an ion exchange matzrial, which ac~s as the b~nding substance which is immobilized in the detection layer. Other materials may also be employed as the binding substance of the present invention provided, of course, tha~ the binding site on the label~d reagent and the binding substance have selecti~ity for binding each other and would not be subject to substantial non-specifically binding to other reagents within the assay system.
Th2 detectable chemical group of the labeled reagent will be a substance which ha a detectable physical property. Such substances have been well developed in the field of immunoassays and i~
general most any s~ch label employed in immunoassays can be applied to the labeled reagent of the present invention.
In particular, chemical groups having de~ectable physical properties are those groups which are detected on the basis of their own physical properties which do not require a chemical reaction with another chemical or substance to provide a detectable signal. Such groups princi-pally include fluorescers such as umbelliferone, fluorescein, resorufin, various rhodamines, dansyl . . .~ . ~, .

~L~6~

derivatives, and aminonaphthalenesulfonic acid, (see Clin. Chem. (lg79) 25:353), phosphorescent molecules such as pyrene, chromophores such as para- or ortho-nitrophenol, phenolpthalein, napthol AS, paranitroanilide and thymolpthalein, radioisotopes such as 3H 35S 32p 125I d 14 spin labels including nitroxide radicals such as DOXYL, PROXYL and TEMPO derivatives; or electroactive moieties such as protons, fluoride, oxygen, ammonia and hydrogen peroxide.
Once the appropriate binding reactions have taken place as heretofore described, the resulting labeled reagent which migrates into the detection layer is bound to and immobilized by the appropriate binding sukstance for the labeled reagent which has been immobilized therein.
Accordingly, immobilization of the complex results in a locali~ed or concentrated signal which is provided by the chemical group of the labeled reagent in the detection layer and ~rom which the detectable signal provided thereby is detected and measured. It is to be appreciated that the inherent physical property or characteristic of such label having a detectable physical property obviates the need for incorporating a chemical reactant or interactive substance in the detection layer ~ince the signal is produced and thereby detectable without a chemical reaction or interaction with an interactive substance.
The detectable signal is preferably measured by passing the test device through a zone which is provided with suitable apparatus for detecting the ultimate optical signal such as by reflection, transmission or fluorescence photometry. Such ~7~

apparatus, for example, directs a source of energy, such as light, on and/or into the test device ele-ment. The light is then reflected from the element back to a detecting means where a reflec-tive sup-port is employed, or passes through the element to a detector in the case of transmission detection where a radiation-transmissive or transparent sup-port is employed. Conventional techniques of fluor-escence spectrophotometry or luminescence measure-ments can also be employed if desired. In techniques where an electroactive species are used as a label, detection can be accomplished with ampometric or po-tentiometric detection devices.

Multilayer Analytical Elements Referring now to the drawings, Fig. 1 illus-trates one embodiment of the multilayer test device of the present invention which comprises at leas-t one reagent layer and a detection layer which are in fluid contact with one another. The reagent layer is incorporated with the immobilized form of the analyte (represented as 11 ~An"), and the detec-tion layer is incorporated with an immobilized form of a binding substance for the labeled reagent (rep-resented as " ~Binder") as heretofore described.
Upon application of both the liquid test medium containing analyte and the labeled reagent to the reagent layer, the test medium and labeled reagent diffuse into the reagent layer and are thereby brought into fluid contact with the ~6'~8~L -immobilized analyte in the reagent layer. In this embodiment, the labeled reagent and the test medium can be applied independently or together as a mixture, the latter being preferred since such provides equal competition between the labeled reagent and the analyte from the test medium for binding to the immobilized analyte. Accordingly, any of the analyte present in the liquid test medium becomes bound to the binding partner for the analyte of the labeled reagent and the resulting complex thereby formed is free to migrate within and out of the reagent layer and into the detection layer. Any of the excess labeled reagent which does not become bound to analyte from the test medium becomes bound to the immobilized analyte in the reagent layer through the binding partner of the analyte of the labeled reagent and prevented from migrating into the detection layer.
Alternatively, as is known in the art, rather ~than adding the labeled reagent as a separate component, whether by addition with the liquid test medium or by being incorporated in a separate reagent layer as described in more detail below, the labeled reagent can be prebound to the immobilized reagent in the reagent layer. Since the binding will be reversible, the presence o~
analyte will reverse some of such binding to release a detectable amount of the labeled reagent.
It is to be appreciated that according to the teachings of the present invention, the binding partner for the analyte preferably has only one specific binding site for the analyte. Preferably, such binding partner is a monovalent fragment of an ~S-1391 ~6~8P

antibody prepared against the analyte and which is purified or derived from a monoclonal antibody.
Such monovalent antibody fragments can be readil~ prepared by digestion of normal whole IgG
antibody with a proteolytic enzyme, such as papain, to produce antibody fragments commonly referred to in the art as Fab fragments. Alternatively, such monovalent antibody fragments can also be prepared by digestion of normal whole IgG antibody with a proteolytic enzyme such as pepsin, followed by chemical reduction to produce antibody fragments commonly referred to in the art as Fab' fragments.
However, other binding partners can also be usPd, preferably of course having only one specific, available binding or recognition site for the analyte under determination. Such other binding partners include whole antibody hybrids, receptor molecules, and the like. For example, a whole antibody hybxid can be used which can be obtained from a number of procedures. Such hybrids can be prepared in vivo from a monoclonal cell line produced by hybridization between a secreting myeloma cell and a splenic cell which secretes the antibody of interest. The resulting cell line can spontaneously produce hybrid molecules consisting of one binding subunit with the specificity of interest and a second subunit with a specificity which is defined by the myeloma cell line. ~uch antibody can be isolated from homogeneous dimers of the original myeloma antibody or splenic cell by conventional protein purification techniques known in the art. Hybrids can also be chemically formed by co-mixing anti-analyte antibody with a second antibody under appropriate denaturing conditions, B~

such as by the addition of urea (8 Molar) and reduc-ing agents such as dithiothreitol, followed by re-moval of the denaturing agent to permit reconstitu-tion of the antibody hybrids. Accordingly, a portion of the reconstituted sample will contain hybrids with a binding site for -the second carrier antibody which can be further purified by conventional protein pur-ification techniques known in the art.
Accordingly, once the analyte from the test me-dium has become bound to the monovalent binding part-ner thereof of the labeled reagent, e.g., the mono-valent fragment of the antibody to the analyte, non-specific immobilization of the resulting complex by the immobilized analyte in the reagent layer is pre-vented as a result of the unavailability of a binding site on the labeled reagent for the immobilized ana-lyte. Upon migration of the analyte-(labeled reagent) complex into the detection layer, the labeled reagent becomes bound to and is immobilized by the immobilized binding substance therefor. The binding interaction of the analyte-(labeled reagent) complex with the im-mobilized binding substance concentrates or localizes the signal provided by the label of the labeled re-agent in the detection layer for the detection and measurement thereof either visually or with the use of an appropriate instrument.
As will be described in greater detail hereinaf-ter, except for reflecting layers and radiation-blocking agents, the various zones or layers and sup-ports of the present invention are radiation-trans-missive in most instances. Such zones or layers and supports permit effective passage of visible light, fluorescent or ~t7~8~

luminescent emission, radioactive radiation, and the like. The choice of a particular radiation~transmissive material will depend upon the particular radiation selected for use with an element in which the material is to be incorporated. Accordingly, the test device as heretofore described permits detection of the signal produced by either the immobilized labeled reagent in the reagent layer or the immobilized analyte-(labeled reagent) complex in the detection layer. As a result, the signal produced thereby, e.g., fluorescence or color, can be detected, measured and correlated to the amount of analyte present in the liquid test medium. Howsver, the presence of the labeled reagent in both the reagent layer and the detection layer would result in detection of the signals produced from both layers, regardless from which direction the signal is detected, i.e., detected with an appropriate 2Q instrument directed at the reagent layer or the detection layer, such signals being indistinguishable from each other. It is therefore desirable to use either radiation-blocking agents incorporated into a particular layer or a reflective or radiation-blocking layer between one or more layers of the device.
In particular, as applied to the multilayer device of the present invention, a radiation-blocking layer would be positioned 3~ between the reagent layer and the detection layer of the device illustrated in Fig. 1. By incorporating such layer between the reagent layer and the detection layer, any signal produced from the immobilized labeled reagent in the reagent MS-13gl .

~6'7~

layer would be detected without an interfering signal produced by the immobilized analyte-(labeled reagent) complex in the detection layer as a result of such non-transmissive layer incorporated therebetween. In this manner, the signal produced by each layer can be detected, measured, and correlated to the amount of analyte in the li~uid test medium without an interfering signal produced by the other layer.
Alternatively, it may be desirable to utilize radiation-blocking agents which would be incorporated into either the reagent layer or the detection layer. Opacifying pigments, such as ti.tanium dioxide, barium sulfate or zinc oxide can be used for this purpose. Blush polymers can also be used, either independently, or incorporated with pigment to enhance radiation-blocking or other properties. Such radiation-blocking layers and agents are known in the art and include those described in U.S. Pat. Nos. 4,042,335 and 4,255,384.
Where a fluorophore is used as the label in - the labeled reagent, the detectable signal can be alternatively masked from the detection system by ~ the use of quenching phenomena without the need for radiation-blocking layers or materials. Those layers or zones in which the signal is to be blocked, e.g., the reagent layer when measuring in the detection layer, can be incorporated with an immobilized substance that effectively quenches the fluorescence of the label as a result of changes in media polarity or incorporation of quenching groups such as heavy atoms, e.g., I .

.
.

~L;Z67~

Detection of the signal produced by the labeled reagent from either the reagent layer or the detection layer can be accomplished with the use of an appropriate instrument, such as a spectrophotometer, reflectometer, fluorometer or luminometer. For example, where detection is based upon absorbance or fluorescence, an energy source from such instrument is directed either at and through the reagent layer or at and through the detection layer. On the other hand, where detection is based upon luminescence, an appropriate instrument which detects such luminescence without the need of an energy source is utilized.
Referring now to Fig. 2 of the drawings, a test device similar is illustrated that is similar to the test device of Fig. 1. In this embodiment, the test device further includes a second reagent layer positioned between the first reagent layer and the detection layer. The additional reagent layer permits incorporation of a test medium soluble form of the labeled reagent therein which obviates the need for pre-mixing the liquid test medium and the labeled reagent prior to the application thereof to the test device or the independent application thereof, such as with the test device illustrated in Fig. 1. In particular, the first reagent layer is incorporated with the test medium soluble labeled reagent, (represented 3Q as "Labeled Reagent"), which i5 solubilized upon fluid contact with the liquid test medium which diffuses therein. The second reagent layer is incorporated with the immobilized form of the analyte (represented as lZs~81 " ~An"), and the detection layer is incorporated with the immobilized form of the binding substance for the labeled reagent (represented as " ~Binder") as here-tofore described.
Upon application o the liquid test medium to the first reagent layer, the liquid test medium dif-fuses into the first reagent layer bringing any ana-lyte from the test medium into direct fluid contact with the labeled reagent therein while, at the same time, solubilizing the labeled reayent. Accordingly, any analyte from the test medium becomes bound to the binding partner thereof of the labeled reagent and the analyte-(labeled reagent) complex thereby formed migrates within and out of the first reagent layer and into the second reagent layer. It is to be appreciated that any of the unbound labeled re-agent in the first reagent layer, i.e., excess lab-eled reagent, will also migrate within and out of the first reagent layer and into the second reagent layer.
Since the binding site of the monovalent binding part-ner for the analyte of the labeled reagent has been occupied by binding to the analyte from the test med-ium, once within the second reagent layer, the analyte-(labeled reagent) complex is permitted to migrate with-in and out of the second reagent layer without becoming immobilized, and into the detection layer. Once within the detection layer, the labeled reagent becomes bound to and is immobilized by the immobilized binding sub~
stance incorporated therein to localize the signal provided by the label of the labeled reagent as here-tofore described. However, since the unbound labeled reagent in the second reagent layer has an available binding site for the immobilized analyte in the sec-ond reagent layer, the labeled reagent becomes bound thereto and immo-bilized thereby and prevented from further migrating into the detection layer. The resulting signal pro-vided by the label of the immobilized analyte-llab-eled reagent) complex is then detected, measured and correlated to the amount of analyte from the test medium as heretofore described.
Although the various layers of the multilayer device of the present invention can be self-support-ing, it is preferred that such layers be coated or otherwise positioned onto a support member. The sup-port member is transparent to light or other energy and will be compatible with the intended mode of sig-nal detection. For example, where the chemistry of the test device generates a gaseous product for de-tection thereof with a gas sensing electrode, the support member is a fluid permeant layer in liquid contact with such electrode. Preferred support mem-bers include transparent support materials capable of transmitting electromagnetic radiation of a wave-length within the region between about 200 nm and about 900 nm. The support need not, of course, trans-mit over the entire 200-900 nm region, although for fluorometric detection of analytical results through ~5 the support it is desirable for the support to trans-mit over a wider band or, alternatively, to transmit at the excitation and emission spectra of the fluor-escent materials used for detection. It may also be desirable to have a support that transmits over a nar-row wavelength band width and which has reduced trans-mittance to adjacent wavelengths. This could be ac-complished, for example, by impregnating or coating the support ~7~1 with one or more colorants having suitable absorption characteristics.
A radiation-transmissive or transparent support member permits a beam of energy, such as light, to pass therethrou~h. The beam is then reflected, such as from a radiation-blocking layer, back to a sensing component of the instrument.
For example, there is illustrated in Fig. 3 a multilayer test device constructed according to the teachings of the present invention having first and second reagent layers and a detection lay~r mounted or otherwise positioned onto a radiaticn-transmissive support member through which an energy source is directed. The first reagent layer is incorporated with the liquid test medium soluble labeled reagent comprising a monovalent antibody fragment of an antibody to the analyte under determination, labeled with a number of dye molecules and having biotin linked thereto as the binding moiety ~represented as "Fab-Dyen-Biotin").
The second reagent layer is incorporated with an immobilized form of the analyte (represented as n ~n"), and the` detection layer is incorporated with an immobilized form of avidin (represented as " ~Avidin") as the binding substance for the biotin binding moiety of the labeled reagent. The immobilized avidin is incorporated in an e~cess amount relative to the labeled reagent so that substantially all of the analyte-(labeled reagent) complex which migrates into the detection layer is immobilized. Upon application of the liquid test medium containing analyte to the first reagent layer, the analyte therefrom is brought into direct fluid contact with the labeled reagent and becomes ' ~7 ~ ~7 -bound to the monovalent antibody fragment of the antibody to the analyte thereof. The analyte-5antibody ragment)-biotinylate~ dye complex formed thereby migrates with~n an~ out of the first reagent layer, through the ~econd reagent layer and into the detection layer where the complex i5 immobilized therein by binding of the biotin binding moiety to the i.mmobilized avidin binding substance therein. Accordingly, as heretofore describsd, once the analyte from the test medium has become bound to the monov lent ant7body fragment of the label.ed reagent, nonspecific immobilization of the resulting complex by ~he immob~lized analyte in the second reagent layer is prevented as a result of the unavailability of a binding site on the labeled reagent for th~ immobilized analyte. Any of the unbouna labeled reagent r however, which migrates into the second reagent layer is immobilized therein by binding of the monovalent antibody fragment o~ the labeled reagent to ~he immobilized analyte.
Since any o the labelea reagent which does not become bound to the analyte from ~he test medium will be immobilized in the second reagent layer, it is necessary to prevPnt detection of the interfering sign~l produced therefrom when detecting the signal produced by the labeled reagent complex immobilized in the detection layer.
3~ This is accomplished by incorporating a radiation-blocking substance into the second reagent layer, or, alternatively, interposing a radiation-blocking layer between the second reagent layer and the detection layer. Accordingly r when a 1~7~

source of energy is directed from an instrument through the radiation-transmissive support member and into the detection layer, the energy i5 reflected back through the detection layer and support member by the radiation-blocking substance or layer and thereby affected only by the label which is present in the detection layer. A
radiation-blocking substance or layer is particularly desirable when the liquid test medium includes a colored substance t such as red blood cells where the liquid test medium is whole blood, in which case the radiation-blocking substance or layer prevents interference of the coloration of red blood cells which would be filtered out and remain in a layer above the detection layer.
It is to be appreciated that the various layers of the multilayer,test device of the present invention are not limited to the layers and configurations as heretofore described. Additional layers for use with the multilayer test device have been described and are known in the art which enhance and/or modulate the performance of such test devices. For example, a spreading zone or layer could be included which would be positioned immediately above and adjacent to the first reagent layer. The spreading zone meters and evenly distributes ~an applied liquid test sample to the underlying first reagent layer. Such spreading zones or layers are known in the art and include those described in U.S. Pat. Nos. 3,992,158 and 4,427,632.
The device can als~, includ'e an intermediate zone or layer between the various layers which serves as an adhesive or subbing layer to . ' ' ' .

~;~6~
.

~acilitate adhesion between the layers and to further facilitate adhesion of the layers to a solid support member. Intermediate zones or layers can also be employed which, for example, contain reagents for removing interferants which may prevent detection of some of the analyte or, can be a radiation-blocking zone or layer which masks zones or layers of the device to prevent interference in detection of the product. Such radiation-blocking layers can also be employed which mask the presence of various interfering substances found in test samples, such as red blood cells in whole blood.
It is also sometimes preferred to provide a timing zone or layer which controls the rate of diffusion of the various -eagents incorporated into the multilayer test device through the various layers thereof. Such timing zones or layers are incorporated into the test device in order to provide controlled incubation times and sequential reactions or to facilitate manufacture of the device by preventing premature interaction of the reagents in the device.
The device o the present invention can also be a multizone device having reagent zones, detection zones, and the like assembled in a configuration particularly adapted for chromatographic analysis. Such a device would include an absorbant region which would be immersed 3Q into the liquid test medium wherein the test medium would diffuse in an upward direction into the vario~s zones.
The zones of such multizone device can be in the form of reagent pads which are mounted onto a plastic support member adapted to be immersed or dipped into a liquid test medium. The zone-forming reagent pads are positioned onto the support member in an end to end relationship wherein the ends thereof are in fluid flow contact with one another.
In particular, such reagent pads include a lower-most, liquid test medium-absorbtive pad or zone, first and second reagent pads or zones, respectively, positioned thereabove, and a detection pad or zone positioned above the second reagent zone.
It is to be appreciated that the reagent and detection zones are incorporated with the various reagents of the multilayer device previously des-cribed and perform the same functions thereof. In this embodiment, however, instead of a liquid test medium sample being applied to the device, the low-ermost absorbtive pad oE the multizone device is immersed into the liquid test medium. In this man-ner, the absorbtive pad serves as a wick for the ab-sorption of the test medium and the upward diffusion thereof into the first reagent zone, the second re-agent zone, and the detection zone, respectively.
Devices in configurations such as described in U.S.
Patents Nos. 4,301,139 and 4,361,537 which use a de-veloping fluid can also be adapted to -the present in-vention. As was previously described, analyte from the test medium which diffuses into the first reagent zone binds to the labeled reagent incorporated there-in and the complex formed thereby continues to mi-grate through the second reagent zone and into the detection zone where the analyte-(labeled reagent) complex becomes bound to and is immobilized by the immobilized binding substance r~. .

1~6~

immobilized therein to thereby localize the signal provided thereby for the further detection and mea-surement thereof. Similarly, any of the labeled re-agent in the first reagent zone which is not bound by analyte from the test medium migrates into the second reagent zone where it is immobilized by the immobilized form of the analyte incorporated therein.
According to the teachings of the present inven-tion, the various layers described herein preferably comprise a porous matrix which is permeable to at least some components of a fluid sample, e.g., anti-gens, haptens and/or antibodies, such permeability generally arising from porosity, ability to swell or any other characteristic. The matrix material can include various porous fibrous materials such as cellulose, papers, fleeces, felts, woven fabrics and the like, whether formed from natural or synthetic materials. Such materials, for example, are des-cribed in U.S. Patents Nos. 3,802,842; 3,809,605;
3,897,214 and 3,987,213. Other porous, but nonfib-rous materials include microporous polymers such as those referred to in U.S. Patent No. 3,552,929.
Preferably, the matrix-forming materials of the various layers of the multilayer test device of the present invention are permeable materials such as gelatin, agarose and the like. Such materials permit the passage of fluids by diffusion, rather than by capillary flow as with fibrous, porous materials such as papers or woven materials. Although the porous, fibrous materials described above can be used, gela-tin, agarose and the like are particularly preferred because of their uniform ~ 6 _ 3~. --parmeability to liquids, as well as their ability to permit the passage of light or other electromagnetic radiation therethrough. Knowing the liquid test medium under analysis, the choice of an appropriate material will be appaxent to one skilled in the art.
Various methods known in the art are available for the immobilization of analyte in the test device of the present invention, or, a derivative or suita~le analog of the analyte can be prepared in order to facilitate the immobilization thereof into the test device. Although immobilization through covalent attachment of the analyte or analog thereof is preferred, other means which utilize non-covalent association such as ion exchange or adsorption can also be used.
Immobilization of analyte can be achieved, for example, by direct incorporation into the carrier matrix of the device, such as cellulose in paper, or into gelatin or agarose in films.
Alternatively, the analyte analog can be linked to a polymeric carrier which is then subsequently incorporated into the matrix of the device, the polymer being of sufficient size to prevent significant diffusion between the binding and detection layers. In gelatin, for example, polymers greater than 10,000 in molecular weight will exhibit negligible diffusion through the gelatin matrix. Similarly, in agarose, polymers greater than two million in molecular weight will be restricted from difusing through the matrix.
The analyte can also be linked directly or through a polymer backbone to very small particles such as polystyrene microbeads which can then be .

~2t;7~

subsequently incorporated into the matrices of the device. Such particles are readily available in a range of sizes and include polystyrene, microcrystalline cellulose, cross-linked dextrans and cross-linked agaroses, ion exchange resins, and the like. A wide range of chemistries are available to couple the agents onto the carrier.
For example, water soluble carbodiimides can be used to activate free carboxyl groups for subsequent reaction with nucleophiles including various amine compounds; amide residues or beads can be converted by reaction with hydrazine to hydrazides which can be further reacted with bifunctional reagents such as glutaraldehyde, 1,5-difluoronitroben~ene, 4,4'-difluoro-3,3'-dinitrophenyl sulfone~
2,4-dichloro-6-carboxymethyl-amino-5-triiazine, dimethyladipimidate or dimethylsuberimidate, and the like, ollowed by reaction with amines or other nucleophiles linked to the analyte or analog of interest; hydrazides can be converted to azide groups by reaction with nitrous acid through a diazotization reaction; hydrazides can be reacted with succinic anhydride to incorporate carboxylate groups with a spacer arm; aliphatic amines or particles can also be reacted with bifunctional reagents analogous to the hydrazide chemistry, including ~he use of heterobifunctional crosslinkers which allow attachment to the amines of functional groups with differing specificities such as a maleimide group which shows enhanced specificity for sulfhydryl derivatives; hydroxyl groups can be activated by cyanogen bromide, tosyl chloride, carbonyl diimidazole, or .

p-nitrophenylchloroformate; particles such as polystyrene can be nitrated, the nitro groups reduced to aromatic amines, and the aromatic amines can ~e diazotized prior to reaction with a nucleophilic-analyte/analog of interest.
Nitrocellulose, diazobenzoxymethyl (DMB) paper, derivatized nylon mesh, Ol paper activated with cyanogen bromide, p-nitrophenylchloroformate, or carboxyldiimidazole can also be utilized to link nucleophile reagents or reagents linked to reactive polymers.
As an alternative to directly binding the appropriate binding reagent to a material immobilized in the reagent layer, one can also take advantage of specific binding partners to obtain the necessary immobilization in situ during performance of the assay. The material to be immobilized, i.e., the analyte or analog or binding partner, can comprise or be modified to comprise a binding site for a distinct binding substance which in turn can be immobilized in the reagent layer.
The immobilizable material thus can be situated in any convenient location in the device and upon p~rformance of the assay will result in the appropriate immobilization. Binding interactions such as described previously for immobilizing the labeled reagent in the detection layer can be used.
Similarly, the methods described above for the immobilization of analyte can also be generally applied for immobilization of the various detection reagents or derivatives thereof.
The test device of the present invention utilizes multiple reagent layers which are assembled to permit fluid contact between adjacent 7~8~

layers as heretofore described. The various layers can be prepared using ilm formers to prepare consecutive over-laying coatings or prepared by superimposing layers of fibrous reagent matrix such as a filter paper, glass fiber or woven polyester.
Alternatively, adjacent ~ones can be configured into a chromatography format with each zone attached on the support member with the edges of each reaction zone being in direct fluid contact as heretofore described.
Multiple layers of paper, for example, can be held in juxtaposition with an enclosing plastic frame, or alternatively with a liquid permeant mesh screen, or by incorporation of a water-soluble adhesive between the layers. The casting of multilayer films can be accomplished by a number of techniques in the art for casting films, including the use of a doctor blade, extrusion coater, Meyer rod, puddle coater or gravure coater.
Alternativel~, multiple consecutive layers can be cast with a cascade coater. Film layers formed by the above procedures can be overlayed with a fabric or mesh material containing reagents which is incubated for a predetermined period of time.

Analyte The present assay can be applied to the detection of any analyte for which there is a binding counterpart available. The analyte usually is a peptide, polypeptide, protein, carbohydrate, glycoprotein, steroid, nucleic acid or other organic molecule for which a binding counterpart exists or which is producible in biological systems - 1~67~8~L
. - 36 -or can be synthesized. The analyte, in functional terms, is usually selected from the group comprising antigens and antibodies thereto; haptens and antibodies thereto; complementary polynucleotide sequences; and hormones, vitamins, metabolites and pharmacological agents, and their binding counterparts. Usually, the analyte is an immunologically-active po.lypeptide or protein, usually having a molecular weight of between about 1,000 and about 10,000,000, such as an antibody or antigenic polypeptide or protein~ or a.hapten having a molecular weight of at least about 100, and usually less than about 1,500.
Representative polypeptide analytes are angiotensin I and II, C-peptide, oxytocin, vasopressin, neurophysin, gastrin, secretin, bradykinin, and glucagon.
Representative protein analytes include the classes of protamines, mucoproteins, glycoproteins, 2~ globulins, albumins, scleroproteins, phosphoproteins, histones, lipoproteins, chromoproteins, and nucleoproteins. Examples of specific proteins are prealbumin, al-lipoproteins, human serum albumin, a1-acid glycoprotein, al-antitrypsin, a1-glycoprotein, transcortin, thyroxine binding globulin, haptoglobin, hemoglobin, myoglobulin, ceruloplasmin, a2-macroglobulin, ~-lipoprotein, erythropoietin, transferrin, hemopexin, fibrinogen, the
3~ immunologublins such as IgG, IgM, IgA, IgD, and IgE, and their fragments, e.g., Fc and Fab, complement factors, prolactin, blood clotting factors such as fibrinogen, thrombin and so forth, insulin, melanotropin, somatotropin, thyrotropin, ~;t7¢~1 ~ 37 -follicle stimulating hormone, leutinizing hormone, gonadotropin, thyroid stimulating hormone, placental lactogen, instrinsic factor, transcobalamin, serum enæymes such as alkaline phosphatase, lactic dehydrogenase, amylase, lipase, phosphatases, cholinesterase, glutamic oxaloacetic transaminase~ glutamic pyruvic transaminase, and uropepsin, endorphins, enkephalins, protamine, tissue antigens, bacterial antigens, and viral antigens such as hepatitis associated antigens (e.g., HBsAg, HBcAg and ;HBeAg).
Representative hapten analytes include the general classes of drugs, metabolites, hormones, vitamins, tOXillS and the like organic compounds.
Haptenlc hormones include thyroxine and triiodothyronine. Vitamins include vitamins A, B, e.g., B12, C, D, E and K, folic acid and thiamine.
Drugs include antibiotics such as aminoglycosides, e.g., gentamicin, tobramycin, amikacin, sisomicin, kanamycin, and netilmi~in, penicillin, tetracycline, terramycin, chloromycetin, and actinomycetin; nucleosides and nucleotides such as adenosine diphosphate (ADP) adenosine triphosphate (ATP), flavin mononucleotide (FMN), nicotinamide adenine dinucleotide (NAD) and its phosphate derivative (NADP), thymidine, guanosine and adenosine; prostaglandins: steroids such as the estrogens, e.g., estriol and estradiol, sterogens, androgens, digoxin, digitoxin, and adrenocortical steriods; and others such as phenobarbital, phenytoin, primidone, ethosuximide, carbamazepine, valproate, theophylline, caffeine, propranolol, procainamide, quinidine, amitryptiline, cortisol, desipramine, disopyramide, doxepin, doxorubicin, ~ 6~

nortryptiline, methotrexate, imipramine, lidocaine, procainamide, N-acetylprocainamide, amphetamines, catecholamines, and antihistamines. Toxins include acetyl T-2 toxin, alfatoxins, cholera toxin, citrinin, cytochalasins, staphylococcal enterotoxin B, HT-2 toxin, and the like.

Liquid Test Medium The liquid test medium containing the analyte under determination can be a naturally occurring or artifically formed liquid suspected to contain analyte, and is usually a biological fluid or a dilution thereof. Biological fluids from which analyte can be d~termined include serum, whole blood, plasma, urine, saliva, and amniotic and cerebrospinal fluids.
The present invention will now be illustrated, but is not intended to he limited, by the following examples:

Preparation of Dye/Biotin Labeled Antibody Ascites fluid containing an anti-digoxin antibody ~~6 mg/mL) is diluted five-fold in 0.1 M
citrate buffer, pH 3.5 and incubated with a 1:50 (w/w) pepsin:antibody solution for 48 hours at 37C. After concentration to -5 ml by ultxafiltration over an ~icon P~30 membrane (Amicon Corp., Danvers, MA, US~), the sample is gel filtexed on a Sephacryl S-300 (Pharmacia, Inc., Piscataway, NJ, USA) column (2.4 x 90 cm) and * Trade Mark ~26~

equilibrated with 50 mM sodium phosphate and 0.10 M
sodium chloride (pH 7.6) to isolate the F(ab')2 fragment of the antibody. The antibody is reduced with 3 mM dithiothreitol for ~5 minutes, followed by the addition o~ 4 mM iodoacetamide ~final concentration) for 1 hour to alkylate free sulfhydryl groups. The protein peak is pooled after desalting on a P-6DG polyacr~lamide gel resin - (Bio. Rad. Co., Richmond, CA).
An aliquot of the pooled protein is reacted for 2 hours with a five-fold molar excess of N-hydroxysuccinimide aminobiotin (Pierce Chemical Co., Rockford, IL). The reaction product is then desalted on a P-6DG column and concentrated to 1 mg/mL protein by-ultrafiltration over an Amicon PM30 membrane.
An aliquot of protein is then reacted overnight with a twenty-fold molar excess of tetramethyl rhodamine-~-isothiocyanate (Research Organics, Inc., Cleveland, OH) previously dissolved in dimethylsulfoxide. The reaction product is passed over an immobilized avidin column (Pierce Chemical Co.) previously equilibrated with 0.1 M
sodium phosphate and 0.5 M sodium chloride (pH
7.8). The bound protein is eluted with 0.2 M
sodium acetate, 0.5 M sodium chloride (pH 4.0), then followed by gel filtration on a P-6DG column (equilibrated with 20 mM sodium phosphate, 100 mM
sodium~chloride [pH 7.2] and the protein peak 3~ collected.

_ 40 ~ 267~

Preparation of the Immobilized Analyte Layer Whatman 31-ET (Whatman, Inc., Clif~on~ NJ, USA) paper i~ activated for subsequent derivati~atiQn wi~h para-nitrophenylchloroformate (NPCF). Paper sheets are ilmnersed for flfteerl minutes in distilled water and the water is then decanted and the paper rinsed wi~h six successive volumes of acetone to remove free water. The paper is then i~ersed ~n a 10% solution of NPCF ~n acetone, incu~ated for six hours 7 and then unreacted NPC~ removed by successive rinses with acetone~ The rinse solu~ion is tested for the presence of the formate by adding 100 1-~ of 1 N
NaOE~ to 300 llL of the rinse solu~ion. The riI~sing is continued with three ~rolumes of acetone until ~here is no detectable yellow color, followed by w~shing with 1 L o d~ 3ti lled water and subsequently washed with 5 ~ 100 mL volumes of acetone, and the solYent remo~ed by air drying.

2 0 EXAI lPLE 3 Preparation of Immobi.lized Binder Layer *

Wha~man 54 paper ~3.7 g) is incubated with 2 g of 1,1'-car~onyldiimidazole in 100 mL of acetone for one hour at room ~emperature with occasional stirring. The paper is washed with 3 x 200 ~L
volumes of acetone and dried at 50~ for approximately ken minutes (or until there is no detectable acetone odor) and stored with silica gel * Trade Mark 7~

desiccant at 4C until further use. The paper is subsequently reacted with 10 mg/ml strepavidin ISigma Chemical Co., 54762, Sigma Chemical Co., St.
Louis, MO 63178) in 50 mM sodium phosphate pH 7.4 for fourteen hours. The paper is washed extensively with 10 mM sodium phosphate buffer pH
7.4.

_ ~LE 4-Dye/Biotin-Antibody Conjugate Layer Whatman 31 ET paper is dipped through a solution containing 10 mg/mL of anti~digoxin Fab dye/biotin in a 0.6 M sodium phosphate buffer, pH
7.4 and driPd at 40C for twenty minutes.

.

Assembly of the Multilayer Device -A composite strip device is assembled from the three reagent elements described above. The conjugate layer is laminated onto a double-faced adhesive tape (3M Company, St. Paul, MN, USA~ and 70 cut into a 1 cm wide x 12.7 cm long ribbon. This material is then laminated onto and along the length of an edge of one surface of an 8.3 cm wide x 12.7 cm long clear polystyrene support (Trycite~, Dow Chemical Co., Midland, MI, USA). A 1-2 mm strip of double-faced adhesive tape is mounted along the back edge of the conjugate layer and a 1 cm wide ribbon of reagent paper containing the immobilized analyte analog is mounted thereon by 7~8~ -the strip of double-faced adhesive tape. The above method is repeated to mount the ribbon of binding layer paper containing the immobili~ed binding protein. The resulting multilayer device is slit into 5 mm wide x 8.3 cm long reagent strips having the various layers mounted to the ends thereof.

EXAMI?LE 6 Operation of the Device A normal human serum sample is spiked to 5 nM
with digoxin. A range o~ concentration from 0.2 to 5.0 nM ~igoxin are prepared by dilution of the stock reagent with normal human serum. An 80 ~L
- aliquot of sample is applied to the test device to initiate the test. The test device is mounted in a fluoromet~r which is capable of measuring a front face fluorescent measurement of the test device - (e.g., Howard, W. et al., Analyt. Chem. 55 878-888 [1983]). The excitation light illuminates the surface of the device with light passing through a 540 nm interference filter t3 cavity, Ditric Optics, Inc., Hudson, MA) through a fiber optic bundle mounted at a 45 angle relative to the normal of the reagent pad. Emitted light is detected by a fiber optic bundle mounted normal to the pad which carries the light to a 570 nm interference filter (3 cavity, Ditric Optics, Inc., Hudson, MA, USA) and associated detection electronics. The change in fluorescence is measured and related to the concentration of digoxin applied.

. '' . ~ .

:

Claims (33)

The embodiments of the invention in which an exclusive property or privilege is claimed are defined as follows:
1. A multizone test device for the specific binding assay determination of an analyte in a liquid test medium involving binding among (i) the analyte, (ii) a labeled or immobilized form of the analyte or of a binding analog thereof, and (iii) an immobilized or labeled form, respectively, of a binding partner of the analyte, the labeled one of the analyte, analog thereof, or binding partner being a labeled reagent comprising a detectable chemical group having a detectable physical property, the test device comprising, in fluid flow contact:, (1) a reagent zone comprising a solid, porous matrix incorporated with the immobilized one of the analyte, analog thereof, or binding partner, and (2) a detection zone comprising a solid, porous matrix for receiving and measuring labeled reagent which migrates into such zone and incorporated with an immobilized form of a binding substance for the labeled reagent.
2. The test device of Claim 1 wherein the labeled reagent additionally comprises a ligand moiety and the immobilized binding substance for the labeled reagent in the detection zone is a binding partner of such ligand moiety.
3. The test device of Claim 2 wherein the binding partner of the ligand moiety is a protein which specifically recognizes such moiety.
4. The test device of Claim 3 wherein the protein which specifically recognizes the ligand moiety is an antibody or a fragment thereof.
5. The test device of Claim 4 wherein the ligand moiety is a hapten.
6. The test device of Claim 3 wherein the ligand moiety is biotin or avidin, and the binding partner for the ligand moiety is the other thereof.
7. The test device of Claim 2 wherein the ligand moiety is a carbohydrate or a lectin which specifically binds therewith, and the binding partner for the ligand moiety is the other thereof.
8. The test device of Claim 1 wherein the immobilized binding substance for the labeled reagent in the detection zone is an antibody, or a fragment thereof, which binds the labeled reagent.
9. The test device of Claim 8 wherein the labeled reagent comprises an antibody, or a fragment thereof, to the analyte and the binding substance for the labeled reagent immobilized in the detection zone is an antibody, or a fragment thereof, to said anti-analyte antibody or fragment thereof.
10. The test device of Claim 1 wherein the labeled reagent comprises an antibody, or a fragment thereof having an intact binding site for protein A, and the binding substance for the labeled reagent immobilized in the detection zone is protein A.
11., The test device of Claim 1 wherein the immobilized binding substance for the labeled reagent in the detection zone is an adsorbent material for the labeled reagent.
12. The test device of Claim 11 wherein the adsorberit material is an ion exchange material.
13. The test device of Claim 1 wherein the detectable chemical group is a fluorescer or a chromophore.
14. The test device of Claim 1 wherein the binding substance for the labeled reagent is immobilized in the detection zone by being covalently coupled to the matrix comprised therein.
15. The test device of Claim 1 wherein the binding substance for the labeled reagent is immobilized in the detection zone by being attached to, a high molecular weight polymeric substance dispersed in said matrix.
16. The test device of Claim 1 wherein the binding partner for the analyte is an antibody or a fragment thereof.

MS-1391 ,
17. The test device of Claim 1 wherein the reagent and detection zones are in the form of layers in fluid flow contact.
18. The test device of Claim 17 which additionally comprises a reagent layer comprising a solid, porous matrix incorporated with a test medium soluble form of the labeled reagent.
19. The test device of Claim 17 which additionally comprises a support element situated on the opposite side of the detection layer from the reagent layer.
20. The test device of Claim 1 which comprises a solid, porous chromatographic element and wherein the reagent and detection zones are discrete sections of such element.
21. In a multilayer immunoassay test device for the determination of an analyte in an aqueous liquid medium, which test device provides a detectable optical signal upon contact with aqueous medium containing analyte, the test device comprising, in fluid flow contact and in the following ordered sequence, (1) a first reagent layer comprising a solid, porous matrix incorporated with a water soluble form of a labeled reagent-comprising an antibody, or a fragment thereof, for the analyte and a fluorescer or chromophore label which provides the detectable optical signal, (2) a second reagent layer comprising a solid, porous matrix incorporated with an immobilized form of the analyte or a binding analog thereof, (3) a detection layer comprising a solid, porous matrix for receiving and measuring labeled reagent which migrates into such layer and incorporated with an immobilized form of a binding substance for the labeled reagent, and (4) a support element comprising a solid, nonporous substrate.
2. The test device of Claim 21 wherein the labeled reagent additionally comprises a ligand moiety and the immobilized binding substance for the labeled reagent in the detection zone is a binding partner of such ligand moiety.
23. The test device of Claim 22 wherein the binding partner of the ligand moiety is a protein which specifically recognizes such moiety.
24. The test device of Claim 23 wherein the protein which specifically recognizes the ligand moiety is an antibody or a fragment thereof.
25. The test device of Claim 24 wherein the ligand moiety is a hapten.
26. The test device of Claim 23 wherein the ligand moiety is biotin or avidin, and the binding partner for the ligand moiety is the other thereof.
27. The test device of Claim 21 wherein the binding substance for the labeled reagent immobilized in the detection zone is an antibody, or a fragment thereof, to said anti-analyte antibody or fragment thereof.
28. The test device of Claim 21 wherein the binding substance for the labeled reagent is immobilized in the detection layer by being covalently coupled to the matrix comprised therein.
29. The test device of Claim 21 wherein the labeled reagent comprises a monovalent anti-analyte antibody fragment.
30. The test device of Claim 29 wherein the antibody fragment is derived from a monoclonal antibody.
31. The test device of Claim 21 wherein the support element is transparent to the detectable optical signal.
32. The test device of Claim 31 wherein the second reagent layer is opaque to the detectable optical signal.
33. The test device of Claim 31 which additionally comprises an opaque layer comprising a solid, porous matrix which is opaque to the detectable optical signal and which is situated between the second reagent layer and the detection layer.
CA000506751A 1985-08-28 1986-04-15 Multizone analytical element having labeled reagent concentration zone Expired - Lifetime CA1267081A (en)

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IL78478A (en) 1990-11-05
CA1267081C (en) 1990-03-27
JPS6250664A (en) 1987-03-05
NO863249D0 (en) 1986-08-12
ES2001891A6 (en) 1988-07-01
AU556852B1 (en) 1986-11-20
DK405586A (en) 1987-03-01
DE3679871D1 (en) 1991-07-25
FI863454A (en) 1987-03-01
EP0212603B1 (en) 1991-06-19
DK405586D0 (en) 1986-08-26
IL78478A0 (en) 1986-08-31
EP0212603A3 (en) 1988-11-30
US4806311A (en) 1989-02-21
EP0212603A2 (en) 1987-03-04
NO863249L (en) 1987-03-02
FI863454A0 (en) 1986-08-26
ZA863752B (en) 1987-01-28
ATE64658T1 (en) 1991-07-15

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