CA2010569A1 - Multi-layered test card for the determination of substances in liquid - Google Patents
Multi-layered test card for the determination of substances in liquidInfo
- Publication number
- CA2010569A1 CA2010569A1 CA002010569A CA2010569A CA2010569A1 CA 2010569 A1 CA2010569 A1 CA 2010569A1 CA 002010569 A CA002010569 A CA 002010569A CA 2010569 A CA2010569 A CA 2010569A CA 2010569 A1 CA2010569 A1 CA 2010569A1
- Authority
- CA
- Canada
- Prior art keywords
- layer
- site
- reaction site
- liquid
- sample
- 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.)
- Abandoned
Links
Landscapes
- Automatic Analysis And Handling Materials Therefor (AREA)
- Investigating Or Analysing Biological Materials (AREA)
- Apparatus Associated With Microorganisms And Enzymes (AREA)
Abstract
ABSTRACT
A composite device for detecting or determining the presence of components in liquids is described. The device has, in combination at least a first and a second layer of porous material in contact with each other, at least one sample receiving site in said device and at least one reaction site connected to the sample receiving site via the second layer. A
pre-determined liquid flow path in and through said layer is defined by liquid barrier means located in said layers whereby liquid deposited at the sample site is transferred to the reaction site along a path from one member to the other.
A composite device for detecting or determining the presence of components in liquids is described. The device has, in combination at least a first and a second layer of porous material in contact with each other, at least one sample receiving site in said device and at least one reaction site connected to the sample receiving site via the second layer. A
pre-determined liquid flow path in and through said layer is defined by liquid barrier means located in said layers whereby liquid deposited at the sample site is transferred to the reaction site along a path from one member to the other.
Description
2 ~
1 MULTI.-~YERED TEST CARD FOR THE DETERMINATION
OF SUBSTANCES IN LIQUIDS
Background of the Invention This invention relates to a diagnostic test device for determining the pre~ence of substances in liquid ~edia. More specifically, it relates to the provision of a multi-layered test device for determining the presence of immunological, biological, enzymatic materials or other analytes in liquids especially biological, industrial or agricultural liquids. Still more specifically, it relates to the provision of a multi-layered device for the detection of such substances in a rapid manner and wherein the results thereof are determinable without a reading ~ instrument.
: General Description of the Prior Art In the field of diagnostic testing, the art has evolved ~rom the use of complex radioimmunoassays and enzyme immunoassays to .: .
the use of single card- ype devices. In general, the art has ~ought to both increase the reada~ility of such de~ices to eliminate the need for an in~trument and to render the device readable in a shorter period of time so that one may maXe a determination of the analyte under field condition. ~he art has also attempted ~o shorten the number of steps that are required to conduct t~e test so that elements of simplicity and convenience are introduced into the test system.
- 'i 2 ~
1 The art-would indeed ~enefi't from a test device which is portable, develops a visual color change almost immediately upon the introduction of test sample, and is readable by the naked eye in a remote location without the need for instrumentation. The art would benefit ~rom a system which eliminates the need ~or multiple steps in performing the test and spscifically, from the eliminatîon of multiple wash steps and long incubation times so that the time for xeading the test could be shortened and the convenience could be amplified dramatically.
~ Objecl:s and Advantages of the Invention It is an object of the invention to provide a test device which can be employed at the ~ite and in the field and at the immediate location where the ~ubstances are to be detected.
It is a further object of the invention to provide a diagnostic kest device which following the addition of the sample reguires little or no ~urther intervention prior to the development of the r~action ~or the visualization of the end result.
It is an additional ob~ect of the invention to provide a test device having multi-layers and comprised of ~ilter type planar m~mbranes which incorporate therein binding materials at appropriate sites such as antibodies and/or antigens to ~ 2 ~
1 facil~tate the r~action mechanism. Other obj~cts and advantages will be apparent from the following specification and the accompanying drawings.
- General Description of the Invention The invention provldes a composite structure of porous materials wherein, through the selection of different pore sizes ; in appropriate areas of the structure and the juxtaposition of liquid barrier means, a liquid flow path is defined which results in an unexpected liquid flow force sufficient to cause a discernible cha~ge in an immunologic complex or in othe~
reactions when appropriate materials are selected.
A commonly encountered problem in the field of immunoassay occurs ^~hen competi~ive or sandwich type binding assays are parformed on a solid porous matrix. ~he immunological reaction in such procedures often does not occur rapidly enough nor conveniently visibly enough in the absence of several wash steps or reagent additions. Even with 1:he additional steps, often : times the reaction is not sufficiently visibl~ within a convenient time to be useful.
In the typical competitive binding assay, an externally supplied tagged antigen competes with the antigen of a sample to react with an externally supplied antibody. tIf the analyte is - ~ 2 ~
1 an ~ntibody, the appropriate binding partners are chosen.~ Each antigen molecule whether tagged or present in the sample has an opportunity to react with the supplied antibody and the extent to which they do react is a measure of the concentration of the antigen in the original sample. Such a system lends itself well to the present invention.
Theoretically, it is p~ssible to perform a competitive assay by displacing tagged antigen from a tagged antigen/antibody complex by contacting the complex with antigen from the sample.
Thus, if a tagged antigen/antibody complex were immobilized on a solid substrate, and that complex contacted with a source of untagged ant~gen, one might expect a displacement of the tagged antigen to occur. Unfortunately, when the solid substrate is a porous material, the mere contact as described above, does not always result in a displacement which i~ suitable ~or commercial analy~e detection. Applicant has discovered a structure and technique which favors in a ~imple one step operation the displacement of tagged antigen from a tayged antigen/antibody complex by sample antigen (if the complex is originally configured and supplied in this ~anner) or the ef~ective competition between the sample analyte and externally supplied tagged analyte for the immob~lized capture binding partner with rapid xevelation of a visual indication of 6uch reaction.
2 ~
1 Other ~orms of immunoassay formats such as sandwich r~actions and competitive binding using a detection system Por antibodies as the analyte rather than antigens as described, may also be employed as will be seen in the detailed description of the invention.
Brie~ly, and without regard to the drawings at this point, a structure is provided with a combination of various pore sizes and li~uid ~low barriers so as to produce rapid wicking of a sample in a pre-determined liquid flow direction to a reaction lQ site at which the clesired re~ctinn takes place.
In its most generalized form, the present lnvention contemplates a structure having a least two planar, flat porous members in intimate contact with each other at their planar surfaces. The multi layered.device is configured in such a way that when a small amount, such as a drop or two, of a liquid test sample is placed onto or into a sample receiving site provided at the top member, the liquid is forced to travel transversely into the bottom member owing to the presence of liquid flow barriers placed or created adjacent to the sample receiving site. The ~ample receiving site may be a hole.in the top member, or may be the top member itself appropriately shaped or confined in consideration of the type of test to be performed.
2 ~ 9 ~:
1 The device is con~igured in such a way as to Eorce the ~low o~ sample liquid from the sample receiving port or site along a pre-determined pathway to the bottom member and ultimately to a reaction site on the bottom or top member depending upon the pre-S determined path selected. ~he sample liquid thus ultimately reaches the reaction site not by lateral flow ~rom the sample receiving -eite, but rather by traversing the sample receiving site in or on the top member in a transverse flow into the second member and up into the top member. Usually, the reaction site is placed on the top member. It may be placed at the bottom member - under appropriate circumstances.
The characteristics of the members can be varied in such a way as to create either a rapid pulling action from the top ~ember and/or a pumplng action due to di~ferential wicking characteristics between the lower member and the top member.
Sample flow in the second member ~hich receives the sample from the sample receiving site is also restricted by barrier means which constrain the flow of liqui~ in the second member to a de~ined space and a direction of that ~low up into the first member.
; By this action there is facilitated a wide variety of potential reactions and reaction ~ites. For example, the analyte o~ the sampl~ dropped onto a top member in a manner in which the sample is prevented from flowing laterally to any substantial ~ 2~ 69 ~
1 degree across the top member but $s constrained to flow transversely, can be ultimately transferrad to a reaction site located on the top member. This reaction site (whether located on the top member or on the bottom member) may either have ~ 5 xeagents deposited thereon or may be itself a receiving site for- additional reagents either directly applied or directed through the same route as the original sample deposition. The present - invention reguires the placement of a defined sample receiving site juxtaposed with certain liquid flow barriers and a reaction site in a pre-determined fashion 50 as to direct the flow of the sample li~uid ~n the pre-selected fashion.
The versatility of the device of the present invention is quite wide. For example, the members themselves may be ~ither hydrophilic or hydrophobic depending on the test characteristics and the analytes to be tested. For example, by appropriate choice of structure and composition of members, analyses of aqueous or non-aqueous samples may be performed. Non-aqueous ~amples containing organic solvenl:-based material may be employed with hydrophobic members in appropriate circumstances. The invention al50 permits the use of ~ydrophobic material with ~qu~ous samples should personal pref~rences dictate. ~xamples of hydrophobic materials are glàss fiber, certain nylons, teflon, and polyvinyl chloride polymers. Examples of hydrophilic materials are paper, certain cellulose acetates, polyvinylidene difluoride, cellulose nitrate, polypropylene, certain microfiber-glass compositions and the like.
~- 2B~6~ ~-1 A combination of member~ with di~erent porosities and binding characteristics with the added capability of being either hydrophilic or hydrophobic provides in the device a) the ability to perfo~m on both aqueous and nonaqueous samples, b) the binding of reactants on one or both of the ~embers and at different ~ites in the flow path of sample or reagents, and c) through impermeable barriers or slots, the ability to differentially control flow rates.
In one form of an immunoassay, the sample is added to the sample port to hydrate a reactant in the bottom or lower member.
The reactant may be a competing analyte bound to an indicator ~uch as enzyme or colloidal gold. A binding (capture) antibody is in this case, located at the reaction site. The member may be protein-binding, if desired to retain the capture anti~ody. The lower member could be non-protein-binding in the region of the placement of the indicator conjugate but could be protein-~inding at the terminus past the reaction site to retain reactants and prevent them from diffusing bacX to the reaction site.
In another assay, the bottom member could be initially protein binding and during manufacture have adhered thereto one or more enzymes for an as5ay to determine the presence of a substrate in a ample solution. The sample would ~ove through the lower member contaoting specific enz~mes in a determined seguential manner to effect the production of a product which could then ba observed at the reaction site.
~; 2 ~
1 It will be obvious to those skilled in the art that numerous modifications o~ immunoassay procedures can be performed on 'he device~ These include ~ut are not limited to competitive assays for small analytes, sandwich assays, and direct detection of reactants in samples. It will also be obvious that other non~
immunologically based assays, such as substrate and product detection, use of nucleic acid probes, lectins, or any other ligand-receptor pairs with various indicator systems can be performed on the device as well.
To illustrate further, when a liquid sample is applied to the sample site in or on the upper member, the li~uid will wick by capillary action into the lower member in either a rapid fashion or slower fashion depending upon the characteristics of the member selected. It is preferred under certain circumstances that the lower member have a pore size su~stantially larger than the pore size of the upper member to facilitate a pumping action on the return flow fxom the bottom member to the top member.
Sample is prevented from movin~ laterally from the sample receiving site because the edge of the sample site has been r~ndered impermeable by the installed ~arrier means. These barrier means may be compression sites, slots, discontinuitias in the material, sonic or heat-generated barriers and the like and are all within the skill cf the art to construct and place.
1 Once liciuid enters the lower member it ~oves laterally and transversely until it contacts an impermeable barrier installed in the lower member and juxtaposed in such a way as to permit ~low of liquid back up into the top member therein to come in contact with reagents or the like at a reaction site. The reaction site may contain the elements of an indicator system useful in detecting the ~nalyte (or substrate) of interest. In addition, if desired, the reaction site may be located in the lower member with the top mem~er serving as the remote site for accumulation of reactants and sample past the reaction site.
For example, in a preferred embodiment, wherein a competitive immunoassay is performed, the reaction site may conveniently contain antibodies (capture antibodies) to the analyte of interest, which said antibodies are covalently bonded or otherwise attached to the upper member. In this regard, if desired, a protein-binding type of member may be selected as the top member to ~acilitate the binding of the antibody. A
conjugate of an indicator molecule 2Ittached to the analyte of interest is selected. A preferred c:onjugate is the analyte bound directly to colloidal gold if feasible, or to a carrier molecule if, for example, the analyte is unable or poorly able to bind to the gold itself. Colloidal gold is a well-known reagent used in diagnostic procedures because of its charaoteristic r~ddish color. As carrier molecules ~here may be employed for example, natural or synthetic proteins or other macromolecules such as 1 BSA, poly L-Lysine, polysaccharides, histones, casein, horse-radish peroxidase and the like. The conjugate may be admixed with the sample prior to applying the sample to the receiving ~ite or may be installed in the device somewhere in the pre-det~rmined liquid flow path prior to the reaction site. If the analyte in the sample is homologous to the analyte adhered to the colloidal gold, it will compete with the analyte-gold conjug~te at the reaction site f or the capture antibody. Assuming appropriate selection of antigen/analyte-gold conjugate concentration in consideration of the conditions of the assay, the analyte gold conjugate will lose in the ~ompetition to the analyte in the sample, and no conjugate will remain bound to the capture antibody. The reaction can then be traced by the absence of the accumulation of gold at the reaction site. Thus, a positive rea~tion is signified by a lack of change of color at the reaction site (i.e., absence of conjugate). This reaction, normally termed a competitive binding assay, is typical of the ones that may be per~ormed with the device of the present invention. Other formats may be used as well as will be described hereinafter.
~he following is ~ brief description of the drawings presented herein from a consideration of which the present in~ention will be further understood.
2 ~
Figure i i~ A cross-sectional view taken across the plane A-A of Figure 2 of a device of the present invention. Figure 2 is an embodiment of the device of the invention shown in circular form. Figure 3 is a device of the invention shown after it has been acted upon by a test liquid operating sn the device of Figure 1. Figure 4 is a top view of another embodiment of a device of the present invention.
Detailed Description of the Drawings Figure 1 shows a device of the present invention at 10 wherein a bilayered device is shown with two of the four reaction sites 15 shown i~ the plane of dissection A-A of Figure 2. Upper layer 20 is provided with a sample port 16 and vent ports 19, and communicates with member 11 at interface 14. Bounding sample port 16 are barriers 13. ~ember 20 and member 11 may be the same or di~ferent material and may have the same or different porosities andJor the same or different wicking actions. In a preferred embodiment of the invention, the bottom layer has a pore size about 5 to 10 times qreater than the pore size of the upper member and the pore ~ize of the upper member is in the ~0 range of 0.2-0.75 microns.
Wîth regard to the varying pore sizes, it should be noted that the larqer pore size should not be so large as to provide a sink for the liquid, ~ince this will frustrate the pumping action desired. What is highly d~sirable however is a pore size that 1 re~ults in a "push" of the ~ample through the sample port into the lower member followed by a "pull" (as will be described later) of the liquid ~rom the lower member back into the first member.
Members 11 and 20 are also equipped with barriers 13a and 13b which are generally incorporated during the manufacturing process as by welding or by incorporation o* slots, discontinuities or the liXe. Barriers 13b are incorporated to proYide additional reservoir compartments and are optional depending on the size of th~ reservoir desired. Barriers 13c are also optional; in practice, the barrier at 13 is usually sufficient. There may be some circumstances, however, where the kinetics o~ the test and the device size are such that it would be desirable to direct the upward flow of liquid into the top member at a point somewha~ remote from the sample receiving site.
In such a case, barriers 13c may be provided and interface 14a rendered impermeable or not, as desired.
Present on member 20 are reaction sites 15 containing various reactants placed in accordance with and in consideration o the ultimate test that is to be performed. As shown in Figure 2, these reaction ~ites may ~e ~ore than one in number and may be for the s~me or di~ferent analytes coming from the same ~ample or may be for a control. ~he device 10 may also have either an~ibodies or antigens, but preferably in ~he discussion given ~' ~
1 herein, will have antibody 17 attached to the member 10 either ~y covalent bonding or some other physical or chemlcal attachment.
~here is also provided in member 11, at 18, a conjugate shown as Au ~ of colloidal gold or some other indicator system conjugated to an antigen which is specific for or will react with the antibody at 17. Thus, in its completed composite form ready for use, there i5 a conjugate 18 of the gold (or other indicator system) to the antigen incorporated into the flow path of the device prior to the reaction site 15. Alternatively, the conjugate may be admixed with ~ample instead o~ being incorporated into the device, and the sample/conjugate mixture be allowed to follow the flow path ~o reaction site 15.
Instead of gold, there may b~ employed any other detection systems used in immunoassays such as enzymes, fluorescing agents, latex beads, luciferases, chemilumniscent agents and the like depending upon the best mode of reaction for the given analyte as ;~ determined by individual pre~erences.
In use, a liquid sample is dropped into sampl~ port 16 and the sample allowed to diffuse into member 11 and mix ~ith conjugate 18. Lateral flow is prevented by the barriers 13 which direct flow of the sample in~o the second member. Upon reaching the second member, the liquid is directed laterally until ~t reaches a barrier (e.g. 13a) or until it is not permitted to go any further and is l'pulled" into member 20 in admixture with 1 conjugate 18. The mixture then migrates to the reaction site 15.
At the reaction site 15, if the sample contains analyte corresponding to the antigen which is conjugated to the indicator system, it will compete with the conjugate in reaction with antibody 17. I~ the sample contains no such antigen, then the only reactant at site 15 other than antibody 17 will be conjugate which will then react and show ~ color change. If sample does contain relevant antigen, the reaction at 15 will be almost excl usively due to the presence of such antigen because ~he concentration of con3ugate and antibody 17 selected in constructing the device has deliberately been adjusted to favor reaction from the normally encountered concentration of analyte in the sample. Thus, a positive result is shown as no color change. For example, in Figure 3 such a result is shown by an "S" ~or sample being attached to the antibody 17. The gold/antigen complex does not attach at reaction site 15 and i~
further removed ~rom that area by the flow of liquid continuing past the reaction site and into the further reaches of members 20 and 11~ If desired, larger amounts of reservoir typs material can be supplied simply by extendinc3 member 20 laterally or providing additional reservoir space in member 11 depending upon how ~uch res~rvoir space is needed as a function of the test that is bein~ performed. Also, a reservoir of absorbent material may be placed in ~u~taposition with member 20.
- ~ 2 ~
1 Following ~ddition of the sample, it is desirable though not necessary in many cases, to add a wash solution to further direct the sample away from the reaction site so that any indicator antigen complex adjacent to the reaction site is moved ~urther away as is evidenced by Figure 3.
If the reaction device as shown in Figure 4 for example, is equipped with viewing ports so that the mi~ration of the gold or indicator system away from the reaction site 15 is obscured, then a change in color ak the reaction site 15 is all that one needs to observe. Sufficient wash matarial or sample may be applied to parmit the visualization of the clear spot in the vent that ~ample does contain the suspected analyte.
Although Figure 2 has been shown as being circular in form, it may be of any con~enient shape such as rectangular, cross-shaped or the like. In addition, it need not be restricted toone reaction site or sample receiving port but may include a variety and a plurality of either or both o~ those and may include reactants for detection of various analytes.
With respect to the material that may be employed as tha members, particular success has been observed with polyvinylidene difluoride with pore sizes of about 0.2 to 0.75 microns for the top member and from 3-5 microns for the lower ~ember. Various ~a 2 ~
1 other materials may be employed ~uch as cellulose acetates, cellulose nitrates, polypropylenes, certain microglass ~iber compositions and the like.
Although the above description has been given with reference to a competitive binding assay wherein the analyte to be detected i6 an antigen and the immunoreagent at reactio~ site 15 is an antibody and the indicator system at 18 is gold complexed to an antigen which binds with the antibodyr the present invention is also suitable for a competitive assay in which the analyte is an lQ antibody to be determined instead of an antigen. Moreover, the present in~ention is also suitable for the detection o~ an antigen or antibody as an analyte wherein a sandwich technique is employed for the reaction. For example, in an immunoassay for human chorionic gonadotropin (h~G), gold conjugated to anti-beta hCG is placed in the bottom member at 18 (Figure 1) and anti-alpha hCG tcapture Ab) is covalent}y or otherwise attached to the upper member at ~5. I~ sample cont:ains hCG it binds to the gold/antibody conjugate and migrates to site 15 where the sample hCG part of the complex binds to the capture antibody (17) and yields a red color at site 15 indicating a positive result. If hCG is absen from the sample, the gold-anti-beta hCG complex has . no hCG bound to it. The oomplex would not bind to capture antibody 17 ~ut would instead ~igrate pas~ the reaction site to the remote reaches of member 20 and/or member 11 (e.g. to 12 on member 20).
~ 17 -
1 MULTI.-~YERED TEST CARD FOR THE DETERMINATION
OF SUBSTANCES IN LIQUIDS
Background of the Invention This invention relates to a diagnostic test device for determining the pre~ence of substances in liquid ~edia. More specifically, it relates to the provision of a multi-layered test device for determining the presence of immunological, biological, enzymatic materials or other analytes in liquids especially biological, industrial or agricultural liquids. Still more specifically, it relates to the provision of a multi-layered device for the detection of such substances in a rapid manner and wherein the results thereof are determinable without a reading ~ instrument.
: General Description of the Prior Art In the field of diagnostic testing, the art has evolved ~rom the use of complex radioimmunoassays and enzyme immunoassays to .: .
the use of single card- ype devices. In general, the art has ~ought to both increase the reada~ility of such de~ices to eliminate the need for an in~trument and to render the device readable in a shorter period of time so that one may maXe a determination of the analyte under field condition. ~he art has also attempted ~o shorten the number of steps that are required to conduct t~e test so that elements of simplicity and convenience are introduced into the test system.
- 'i 2 ~
1 The art-would indeed ~enefi't from a test device which is portable, develops a visual color change almost immediately upon the introduction of test sample, and is readable by the naked eye in a remote location without the need for instrumentation. The art would benefit ~rom a system which eliminates the need ~or multiple steps in performing the test and spscifically, from the eliminatîon of multiple wash steps and long incubation times so that the time for xeading the test could be shortened and the convenience could be amplified dramatically.
~ Objecl:s and Advantages of the Invention It is an object of the invention to provide a test device which can be employed at the ~ite and in the field and at the immediate location where the ~ubstances are to be detected.
It is a further object of the invention to provide a diagnostic kest device which following the addition of the sample reguires little or no ~urther intervention prior to the development of the r~action ~or the visualization of the end result.
It is an additional ob~ect of the invention to provide a test device having multi-layers and comprised of ~ilter type planar m~mbranes which incorporate therein binding materials at appropriate sites such as antibodies and/or antigens to ~ 2 ~
1 facil~tate the r~action mechanism. Other obj~cts and advantages will be apparent from the following specification and the accompanying drawings.
- General Description of the Invention The invention provldes a composite structure of porous materials wherein, through the selection of different pore sizes ; in appropriate areas of the structure and the juxtaposition of liquid barrier means, a liquid flow path is defined which results in an unexpected liquid flow force sufficient to cause a discernible cha~ge in an immunologic complex or in othe~
reactions when appropriate materials are selected.
A commonly encountered problem in the field of immunoassay occurs ^~hen competi~ive or sandwich type binding assays are parformed on a solid porous matrix. ~he immunological reaction in such procedures often does not occur rapidly enough nor conveniently visibly enough in the absence of several wash steps or reagent additions. Even with 1:he additional steps, often : times the reaction is not sufficiently visibl~ within a convenient time to be useful.
In the typical competitive binding assay, an externally supplied tagged antigen competes with the antigen of a sample to react with an externally supplied antibody. tIf the analyte is - ~ 2 ~
1 an ~ntibody, the appropriate binding partners are chosen.~ Each antigen molecule whether tagged or present in the sample has an opportunity to react with the supplied antibody and the extent to which they do react is a measure of the concentration of the antigen in the original sample. Such a system lends itself well to the present invention.
Theoretically, it is p~ssible to perform a competitive assay by displacing tagged antigen from a tagged antigen/antibody complex by contacting the complex with antigen from the sample.
Thus, if a tagged antigen/antibody complex were immobilized on a solid substrate, and that complex contacted with a source of untagged ant~gen, one might expect a displacement of the tagged antigen to occur. Unfortunately, when the solid substrate is a porous material, the mere contact as described above, does not always result in a displacement which i~ suitable ~or commercial analy~e detection. Applicant has discovered a structure and technique which favors in a ~imple one step operation the displacement of tagged antigen from a tayged antigen/antibody complex by sample antigen (if the complex is originally configured and supplied in this ~anner) or the ef~ective competition between the sample analyte and externally supplied tagged analyte for the immob~lized capture binding partner with rapid xevelation of a visual indication of 6uch reaction.
2 ~
1 Other ~orms of immunoassay formats such as sandwich r~actions and competitive binding using a detection system Por antibodies as the analyte rather than antigens as described, may also be employed as will be seen in the detailed description of the invention.
Brie~ly, and without regard to the drawings at this point, a structure is provided with a combination of various pore sizes and li~uid ~low barriers so as to produce rapid wicking of a sample in a pre-determined liquid flow direction to a reaction lQ site at which the clesired re~ctinn takes place.
In its most generalized form, the present lnvention contemplates a structure having a least two planar, flat porous members in intimate contact with each other at their planar surfaces. The multi layered.device is configured in such a way that when a small amount, such as a drop or two, of a liquid test sample is placed onto or into a sample receiving site provided at the top member, the liquid is forced to travel transversely into the bottom member owing to the presence of liquid flow barriers placed or created adjacent to the sample receiving site. The ~ample receiving site may be a hole.in the top member, or may be the top member itself appropriately shaped or confined in consideration of the type of test to be performed.
2 ~ 9 ~:
1 The device is con~igured in such a way as to Eorce the ~low o~ sample liquid from the sample receiving port or site along a pre-determined pathway to the bottom member and ultimately to a reaction site on the bottom or top member depending upon the pre-S determined path selected. ~he sample liquid thus ultimately reaches the reaction site not by lateral flow ~rom the sample receiving -eite, but rather by traversing the sample receiving site in or on the top member in a transverse flow into the second member and up into the top member. Usually, the reaction site is placed on the top member. It may be placed at the bottom member - under appropriate circumstances.
The characteristics of the members can be varied in such a way as to create either a rapid pulling action from the top ~ember and/or a pumplng action due to di~ferential wicking characteristics between the lower member and the top member.
Sample flow in the second member ~hich receives the sample from the sample receiving site is also restricted by barrier means which constrain the flow of liqui~ in the second member to a de~ined space and a direction of that ~low up into the first member.
; By this action there is facilitated a wide variety of potential reactions and reaction ~ites. For example, the analyte o~ the sampl~ dropped onto a top member in a manner in which the sample is prevented from flowing laterally to any substantial ~ 2~ 69 ~
1 degree across the top member but $s constrained to flow transversely, can be ultimately transferrad to a reaction site located on the top member. This reaction site (whether located on the top member or on the bottom member) may either have ~ 5 xeagents deposited thereon or may be itself a receiving site for- additional reagents either directly applied or directed through the same route as the original sample deposition. The present - invention reguires the placement of a defined sample receiving site juxtaposed with certain liquid flow barriers and a reaction site in a pre-determined fashion 50 as to direct the flow of the sample li~uid ~n the pre-selected fashion.
The versatility of the device of the present invention is quite wide. For example, the members themselves may be ~ither hydrophilic or hydrophobic depending on the test characteristics and the analytes to be tested. For example, by appropriate choice of structure and composition of members, analyses of aqueous or non-aqueous samples may be performed. Non-aqueous ~amples containing organic solvenl:-based material may be employed with hydrophobic members in appropriate circumstances. The invention al50 permits the use of ~ydrophobic material with ~qu~ous samples should personal pref~rences dictate. ~xamples of hydrophobic materials are glàss fiber, certain nylons, teflon, and polyvinyl chloride polymers. Examples of hydrophilic materials are paper, certain cellulose acetates, polyvinylidene difluoride, cellulose nitrate, polypropylene, certain microfiber-glass compositions and the like.
~- 2B~6~ ~-1 A combination of member~ with di~erent porosities and binding characteristics with the added capability of being either hydrophilic or hydrophobic provides in the device a) the ability to perfo~m on both aqueous and nonaqueous samples, b) the binding of reactants on one or both of the ~embers and at different ~ites in the flow path of sample or reagents, and c) through impermeable barriers or slots, the ability to differentially control flow rates.
In one form of an immunoassay, the sample is added to the sample port to hydrate a reactant in the bottom or lower member.
The reactant may be a competing analyte bound to an indicator ~uch as enzyme or colloidal gold. A binding (capture) antibody is in this case, located at the reaction site. The member may be protein-binding, if desired to retain the capture anti~ody. The lower member could be non-protein-binding in the region of the placement of the indicator conjugate but could be protein-~inding at the terminus past the reaction site to retain reactants and prevent them from diffusing bacX to the reaction site.
In another assay, the bottom member could be initially protein binding and during manufacture have adhered thereto one or more enzymes for an as5ay to determine the presence of a substrate in a ample solution. The sample would ~ove through the lower member contaoting specific enz~mes in a determined seguential manner to effect the production of a product which could then ba observed at the reaction site.
~; 2 ~
1 It will be obvious to those skilled in the art that numerous modifications o~ immunoassay procedures can be performed on 'he device~ These include ~ut are not limited to competitive assays for small analytes, sandwich assays, and direct detection of reactants in samples. It will also be obvious that other non~
immunologically based assays, such as substrate and product detection, use of nucleic acid probes, lectins, or any other ligand-receptor pairs with various indicator systems can be performed on the device as well.
To illustrate further, when a liquid sample is applied to the sample site in or on the upper member, the li~uid will wick by capillary action into the lower member in either a rapid fashion or slower fashion depending upon the characteristics of the member selected. It is preferred under certain circumstances that the lower member have a pore size su~stantially larger than the pore size of the upper member to facilitate a pumping action on the return flow fxom the bottom member to the top member.
Sample is prevented from movin~ laterally from the sample receiving site because the edge of the sample site has been r~ndered impermeable by the installed ~arrier means. These barrier means may be compression sites, slots, discontinuitias in the material, sonic or heat-generated barriers and the like and are all within the skill cf the art to construct and place.
1 Once liciuid enters the lower member it ~oves laterally and transversely until it contacts an impermeable barrier installed in the lower member and juxtaposed in such a way as to permit ~low of liquid back up into the top member therein to come in contact with reagents or the like at a reaction site. The reaction site may contain the elements of an indicator system useful in detecting the ~nalyte (or substrate) of interest. In addition, if desired, the reaction site may be located in the lower member with the top mem~er serving as the remote site for accumulation of reactants and sample past the reaction site.
For example, in a preferred embodiment, wherein a competitive immunoassay is performed, the reaction site may conveniently contain antibodies (capture antibodies) to the analyte of interest, which said antibodies are covalently bonded or otherwise attached to the upper member. In this regard, if desired, a protein-binding type of member may be selected as the top member to ~acilitate the binding of the antibody. A
conjugate of an indicator molecule 2Ittached to the analyte of interest is selected. A preferred c:onjugate is the analyte bound directly to colloidal gold if feasible, or to a carrier molecule if, for example, the analyte is unable or poorly able to bind to the gold itself. Colloidal gold is a well-known reagent used in diagnostic procedures because of its charaoteristic r~ddish color. As carrier molecules ~here may be employed for example, natural or synthetic proteins or other macromolecules such as 1 BSA, poly L-Lysine, polysaccharides, histones, casein, horse-radish peroxidase and the like. The conjugate may be admixed with the sample prior to applying the sample to the receiving ~ite or may be installed in the device somewhere in the pre-det~rmined liquid flow path prior to the reaction site. If the analyte in the sample is homologous to the analyte adhered to the colloidal gold, it will compete with the analyte-gold conjug~te at the reaction site f or the capture antibody. Assuming appropriate selection of antigen/analyte-gold conjugate concentration in consideration of the conditions of the assay, the analyte gold conjugate will lose in the ~ompetition to the analyte in the sample, and no conjugate will remain bound to the capture antibody. The reaction can then be traced by the absence of the accumulation of gold at the reaction site. Thus, a positive rea~tion is signified by a lack of change of color at the reaction site (i.e., absence of conjugate). This reaction, normally termed a competitive binding assay, is typical of the ones that may be per~ormed with the device of the present invention. Other formats may be used as well as will be described hereinafter.
~he following is ~ brief description of the drawings presented herein from a consideration of which the present in~ention will be further understood.
2 ~
Figure i i~ A cross-sectional view taken across the plane A-A of Figure 2 of a device of the present invention. Figure 2 is an embodiment of the device of the invention shown in circular form. Figure 3 is a device of the invention shown after it has been acted upon by a test liquid operating sn the device of Figure 1. Figure 4 is a top view of another embodiment of a device of the present invention.
Detailed Description of the Drawings Figure 1 shows a device of the present invention at 10 wherein a bilayered device is shown with two of the four reaction sites 15 shown i~ the plane of dissection A-A of Figure 2. Upper layer 20 is provided with a sample port 16 and vent ports 19, and communicates with member 11 at interface 14. Bounding sample port 16 are barriers 13. ~ember 20 and member 11 may be the same or di~ferent material and may have the same or different porosities andJor the same or different wicking actions. In a preferred embodiment of the invention, the bottom layer has a pore size about 5 to 10 times qreater than the pore size of the upper member and the pore ~ize of the upper member is in the ~0 range of 0.2-0.75 microns.
Wîth regard to the varying pore sizes, it should be noted that the larqer pore size should not be so large as to provide a sink for the liquid, ~ince this will frustrate the pumping action desired. What is highly d~sirable however is a pore size that 1 re~ults in a "push" of the ~ample through the sample port into the lower member followed by a "pull" (as will be described later) of the liquid ~rom the lower member back into the first member.
Members 11 and 20 are also equipped with barriers 13a and 13b which are generally incorporated during the manufacturing process as by welding or by incorporation o* slots, discontinuities or the liXe. Barriers 13b are incorporated to proYide additional reservoir compartments and are optional depending on the size of th~ reservoir desired. Barriers 13c are also optional; in practice, the barrier at 13 is usually sufficient. There may be some circumstances, however, where the kinetics o~ the test and the device size are such that it would be desirable to direct the upward flow of liquid into the top member at a point somewha~ remote from the sample receiving site.
In such a case, barriers 13c may be provided and interface 14a rendered impermeable or not, as desired.
Present on member 20 are reaction sites 15 containing various reactants placed in accordance with and in consideration o the ultimate test that is to be performed. As shown in Figure 2, these reaction ~ites may ~e ~ore than one in number and may be for the s~me or di~ferent analytes coming from the same ~ample or may be for a control. ~he device 10 may also have either an~ibodies or antigens, but preferably in ~he discussion given ~' ~
1 herein, will have antibody 17 attached to the member 10 either ~y covalent bonding or some other physical or chemlcal attachment.
~here is also provided in member 11, at 18, a conjugate shown as Au ~ of colloidal gold or some other indicator system conjugated to an antigen which is specific for or will react with the antibody at 17. Thus, in its completed composite form ready for use, there i5 a conjugate 18 of the gold (or other indicator system) to the antigen incorporated into the flow path of the device prior to the reaction site 15. Alternatively, the conjugate may be admixed with ~ample instead o~ being incorporated into the device, and the sample/conjugate mixture be allowed to follow the flow path ~o reaction site 15.
Instead of gold, there may b~ employed any other detection systems used in immunoassays such as enzymes, fluorescing agents, latex beads, luciferases, chemilumniscent agents and the like depending upon the best mode of reaction for the given analyte as ;~ determined by individual pre~erences.
In use, a liquid sample is dropped into sampl~ port 16 and the sample allowed to diffuse into member 11 and mix ~ith conjugate 18. Lateral flow is prevented by the barriers 13 which direct flow of the sample in~o the second member. Upon reaching the second member, the liquid is directed laterally until ~t reaches a barrier (e.g. 13a) or until it is not permitted to go any further and is l'pulled" into member 20 in admixture with 1 conjugate 18. The mixture then migrates to the reaction site 15.
At the reaction site 15, if the sample contains analyte corresponding to the antigen which is conjugated to the indicator system, it will compete with the conjugate in reaction with antibody 17. I~ the sample contains no such antigen, then the only reactant at site 15 other than antibody 17 will be conjugate which will then react and show ~ color change. If sample does contain relevant antigen, the reaction at 15 will be almost excl usively due to the presence of such antigen because ~he concentration of con3ugate and antibody 17 selected in constructing the device has deliberately been adjusted to favor reaction from the normally encountered concentration of analyte in the sample. Thus, a positive result is shown as no color change. For example, in Figure 3 such a result is shown by an "S" ~or sample being attached to the antibody 17. The gold/antigen complex does not attach at reaction site 15 and i~
further removed ~rom that area by the flow of liquid continuing past the reaction site and into the further reaches of members 20 and 11~ If desired, larger amounts of reservoir typs material can be supplied simply by extendinc3 member 20 laterally or providing additional reservoir space in member 11 depending upon how ~uch res~rvoir space is needed as a function of the test that is bein~ performed. Also, a reservoir of absorbent material may be placed in ~u~taposition with member 20.
- ~ 2 ~
1 Following ~ddition of the sample, it is desirable though not necessary in many cases, to add a wash solution to further direct the sample away from the reaction site so that any indicator antigen complex adjacent to the reaction site is moved ~urther away as is evidenced by Figure 3.
If the reaction device as shown in Figure 4 for example, is equipped with viewing ports so that the mi~ration of the gold or indicator system away from the reaction site 15 is obscured, then a change in color ak the reaction site 15 is all that one needs to observe. Sufficient wash matarial or sample may be applied to parmit the visualization of the clear spot in the vent that ~ample does contain the suspected analyte.
Although Figure 2 has been shown as being circular in form, it may be of any con~enient shape such as rectangular, cross-shaped or the like. In addition, it need not be restricted toone reaction site or sample receiving port but may include a variety and a plurality of either or both o~ those and may include reactants for detection of various analytes.
With respect to the material that may be employed as tha members, particular success has been observed with polyvinylidene difluoride with pore sizes of about 0.2 to 0.75 microns for the top member and from 3-5 microns for the lower ~ember. Various ~a 2 ~
1 other materials may be employed ~uch as cellulose acetates, cellulose nitrates, polypropylenes, certain microglass ~iber compositions and the like.
Although the above description has been given with reference to a competitive binding assay wherein the analyte to be detected i6 an antigen and the immunoreagent at reactio~ site 15 is an antibody and the indicator system at 18 is gold complexed to an antigen which binds with the antibodyr the present invention is also suitable for a competitive assay in which the analyte is an lQ antibody to be determined instead of an antigen. Moreover, the present in~ention is also suitable for the detection o~ an antigen or antibody as an analyte wherein a sandwich technique is employed for the reaction. For example, in an immunoassay for human chorionic gonadotropin (h~G), gold conjugated to anti-beta hCG is placed in the bottom member at 18 (Figure 1) and anti-alpha hCG tcapture Ab) is covalent}y or otherwise attached to the upper member at ~5. I~ sample cont:ains hCG it binds to the gold/antibody conjugate and migrates to site 15 where the sample hCG part of the complex binds to the capture antibody (17) and yields a red color at site 15 indicating a positive result. If hCG is absen from the sample, the gold-anti-beta hCG complex has . no hCG bound to it. The oomplex would not bind to capture antibody 17 ~ut would instead ~igrate pas~ the reaction site to the remote reaches of member 20 and/or member 11 (e.g. to 12 on member 20).
~ 17 -
Claims (19)
1. A composite device for detecting or determining the presence of components in liquids which comprises in combination at least a first and a second layer of porous material in contact with each other, at least one sample receiving site in said device and at least one reaction site in communica-tion with said sample receiving site via said second layer and a liquid flow path in and through said layers defined by liquid barrier means located in said layers whereby liquid deposited at the sample site is transferred to the reaction site along a path from one member to the other.
2. The device of claim 1 wherein the porous material is flat and planar.
3. The device of claim 2 wherein the porous material is nylon, teflon, glass fibers, polyvinyl chloride, cellulose acetate, polyvinylidene difluoride, cellulose nitrate or polypropylene.
4. The device of claim 2 wherein each layer is hydrophobic, or each layer is hydrophillc, or either layer is hydrophobic and the other layer is hydrophilic.
5. The device of claim 2 wherein the sample receiving site is on the first layer.
6. The device of claim 5 wherein the reaction site is on the second layer.
7. The device of claim 5 wherein the reaction site is on the first layer.
8. The device of claim 1 wherein the reaction sites are for the determination of one or more immunologic component of a liquid.
9. The device of claim 8 wherein there are present a plurality of reaction sites.
10. The device of claim 8 wherein there is present at the reaction site a binding partner of that immunologic component to be determined.
11. The device of claim 10 wherein the immunologic binding partner is an antibody and the component to be determined is an antigen.
12. The device of claim 11 wherein there is present in said second layer in the liquid flow path prior to the reaction site an antigen corresponding to the component to be determined which antigen is conjugated to an indicator system.
13. The device of claim 12 wherein the indicator system is colloidal gold.
14. The device of claim 11 wherein there is present in aid second layer in the liquid flow path prior to the reaction site an antibody reactive with the antigen to be determined which antibody is conjugated to an indicator system.
15. The device of claim 14 wherein the indicator system is colloidal gold.
16. The device of claim 1 wherein the barriers are slots, discontinuities, welds, or compressions and are located in the liquid pathway so as to control flow direction and rates.
17. The device of claim 1 wherein there is present in said device in the liquid flow path prior to the reaction site reactants whereby when sufficient liquid flows along said pathway, said reactants are delivered to said reaction site.
10. The device of claim 16 wherein each layer is protein-binding or each layer is non-protein-binding or either layer is protein-binding and the other is non-protein-binding.
19. The device of claim 16 wherein one layer has the same or different porosities and wicking actions.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA002010569A CA2010569A1 (en) | 1990-02-21 | 1990-02-21 | Multi-layered test card for the determination of substances in liquid |
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA002010569A CA2010569A1 (en) | 1990-02-21 | 1990-02-21 | Multi-layered test card for the determination of substances in liquid |
| EP19900301907 EP0443231B1 (en) | 1990-02-22 | 1990-02-22 | Multi-layered diagnostic test device for the determination of substances in liquids |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2010569A1 true CA2010569A1 (en) | 1991-08-21 |
Family
ID=25673969
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002010569A Abandoned CA2010569A1 (en) | 1990-02-21 | 1990-02-21 | Multi-layered test card for the determination of substances in liquid |
Country Status (1)
| Country | Link |
|---|---|
| CA (1) | CA2010569A1 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102128918A (en) * | 2010-11-11 | 2011-07-20 | 艾康生物技术(杭州)有限公司 | Detecting test paper |
-
1990
- 1990-02-21 CA CA002010569A patent/CA2010569A1/en not_active Abandoned
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102128918A (en) * | 2010-11-11 | 2011-07-20 | 艾康生物技术(杭州)有限公司 | Detecting test paper |
| CN102128918B (en) * | 2010-11-11 | 2013-12-04 | 艾康生物技术(杭州)有限公司 | Detecting test paper |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US5202268A (en) | Multi-layered test card for the determination of substances in liquids | |
| EP0443231B1 (en) | Multi-layered diagnostic test device for the determination of substances in liquids | |
| AU2001253354B9 (en) | Diagnostic device with multiple independent flow paths | |
| EP0465266B1 (en) | Complementary visual signal immunoassay | |
| US7189522B2 (en) | Dual path immunoassay device | |
| US20110229913A1 (en) | Method for Amplification of Signal in Immunochromatographic Assay and Immunochromatographic Kit Using the Method | |
| US7569397B2 (en) | Immunoassay devices and use thereof | |
| US5759866A (en) | Device and method for assaying biological components in sample | |
| US20100323369A1 (en) | Diagnostic Testing Process | |
| JP2010512537A (en) | Indirect lateral flow sandwich assay | |
| WO2007055712A1 (en) | Immuno-gold lateral flow assay | |
| CA2460072C (en) | Multi-analyte assay device with multi-spot detection zone | |
| US20030073121A1 (en) | Multi-analyte assay device with multi-spot detection zone | |
| US20050221386A1 (en) | Chromatographic exclusion agglutination assay and methods of use thereof | |
| EP1845375A2 (en) | Flow through assay device, diagnostic kit comprising said device and use in the detection of an analyte in a sample | |
| JP2006038700A (en) | Analyzer and analysis method | |
| CA2010569A1 (en) | Multi-layered test card for the determination of substances in liquid | |
| JPH03276067A (en) | Composite device for measuring substance in liquid | |
| US20070042504A1 (en) | Method for determining substance or substances in liquid sample | |
| KR20220047198A (en) | Strips, kits for immunochromatography and sandwich immunochromatographic assays for measuring tryptase using the same | |
| WO1992018869A1 (en) | Colorfast reference device for immunoassays | |
| Kimball | Corstjens et al.(45) Date of Patent: Dec. 28, 2010 |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| FZDE | Discontinued |