MULTILAYER ION TEST MEANS

Abstract: A multilayer test means for determining the presence of an ion in an aqueous test sample, a method for preparing it and a method for using it. The test means comprises a reagent layer containing an ionophore capable of forming a complex with the ion and reporter substance capable of interacting with the complex of ionophore and ion to produce a detect­ able response, a reflecting layer and optionally an opacifying layer. The multilayer format is particularly suited to whole blood electrolyte determinations and does not require washing or wiping before use. A hematocrit independent whole blood potassium test is provided.

Description: MULTILAYER ION TEST MEANS 1. INTRODUCTION The present invention relates to the measurement of ions, in particular ions in aqueous solution, and to a multi layer test means or devices for performing such measurements. The invention provides a convenient format for determining the presence and/or concentration of ions whereby results are available shortly after contact with an aqueous test sample. Cumbersome, expensive electronic equipment, such as ion-specific electrodes, flame photometers, atomic absorption spectrophotometers or the like, is not needed. A multilayer format for ion testing can be used advantageously to measure ion content of highly colored fluids. For example, the multilayer format is particularly useful for whole blood measurements. The multilayer format is unique in that it can be used to provide information on ultrafilterable or "free" calcium and to determine serum potassium levels using a whole blood sample without interference due to lysed blood cells. Although it is the potassium ion content of serum which provides a critical clinical indication of many conditions leading to muscle irritability and excitatory changes in myocardial function, among others, it would be convenient to use a whole blood specimen and eliminate the separation of blood cells from the serum prior to measurement. However, blood cells contain large amounts of potassium ion and if lysed during the measurement, would lead to large errors in the values reported. Therefore, a whole blood device capable of measuring serum potassium which is independent of "hematocrit" or cell content of the blood would provide a convenience not available with present potassium ion tests. 2. BACKGROUND OF THE INVENTION Methods for determining ions in solution include flame photometry, atomic absorption photometry and ion-specific electrodes. Test strip formats have been disclosed in published European Patent Applications 84 104 824.2; 84 104 828.3; 85 101 4; nd European Patent 41,175 assigned commonly he,reip. Preferred reporter substances have been disclosed in U.S. Patent No. 4,540,520 and 4.552,697 commonly assigned herein. Multilayer formats for the determination of analytes by Chemical reaction of the analyte with the components in the reagent layer have been disclosed (see for example U.S. Patent No. 3,992,158 to Przybylowicz et al). Kitajima et al. in U.S. Patent No, 4,366,149 discloses a multilayer integral element for the chemical analysis of blood wherein the reagent layer is composed of a hydrophilic binder and fine hydrophobic particles dispersed in that binder, which particles contain the reagent capable of producing a color change with the component being analyzed. U.S. Patent No. 4,356,149 to Kitajima et al. is directed toward eliminating extra layers made necessary by incompatible reagent components. Kitajima deals only with the determination of a neutral analyte with a reaction requiring the separation of incompatible reagent components. U.S. Patent No. 4,255,384, to Kitajima et al. concerns a multi layer integrated element for the chemical analysis of blood. 3. BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 diagrammatically depicts a multilayer device format particularly suited for whole blood determinations. Fig. la depicts a supported three layer device; Fig. 1b depicts a supported two layered device. The figures are described in detail in Section 7 entitled "Multilayer Test Device". Figure 2 shows data for a multi layer device given in Example 8.1. The graph depicts apparent millimolar potassium ion concentration [K -t3 determined with test devices of this invention compared to millimolar [K+i obtained with the reference flame photometry method. Figure 2a shows serum data and figure 2b shows whole blood data. Figure 3 shows the decrease of hematocrit dependence of a whole blood potassium determination when sodium chloride is incorporated into the multilayer test device. The graph depicts data obtained as shown in Example 8.2. 4. SUMMARY OF THE INVENTION This invention resides in the discovery of a multilayer test means for detecting the presence of an ion in an aqueous test sample and determining its concentration. The multilayer device is preferred for determining the concentration of ++ cations such as K , Na+, Ca+, Mg and Li in whole blood samples. The multilayer device includes at least a reagent layer and a reflecting layer, and optionally also includes an opacifying layer and a transparent support member. The reagent layer of the multilayer test means comprises either a hydrophilic carrier matrix incorporated with finely divided globules of a hydrophobic vehicle which globules contain two principal ingredients: an ionophdre capable of forming a complex with a specific ion to be determined and a reporter substance capable of interacting with the complex of the ionophore and the ion to produce a detectable response such as a change in, or the appearance of, color or fluorescence; or a substantially non-polar, nonporous carrier matrix incorporated with an ionophore and reporter having the characteristics described above. For the determination of cations a neutral reporter, having a dissociable proton which proton is capable of dissociating upon interaction of the reporter with the complex of the ionophore and the cation to produce a detectable response, is preferred. The addition of the reflecting layer and optionally the opacifying layer with a nonporous, nonpolar reagent layer, permit the addition of such components as a buffer and an interferant removal substance. The addition of the buffer allows ion determination with an unbuffered, undiluted sample. An interferant removal substance can complex with an interfering ion, permitting greater selectivity and precision. A preferred embodiment is a multi layer test means for whole blood potassium wherein sufficient sodium chloride is incorporated in a layer of the multilayer device to provide hematocrit independence. The multilayer format is preferred for whole blood determinations, as electrolyte concentration can be determined colorimetrically without washing or wiping the device. 5. DEFINITIONS The following definitions are provided to clarify the scope of the present invention and to enable its formulation and use. 5.1 The term "ionophore" includes molecules capable of selectively forming a complex with a particular ion in an nonpolar environment to the substantial exclusion of others. For example the cyclic polyether 2,3-naphtho-1,4,7,10,13-pentaoxa- cyclopentadeca-2-ene (sometimes known as 2,3naphtho-15-crown-5 and called Potassium Ionophore I herein) binds to potassium ions selectively to form a cationic complex. Included in the term are coronands, such as are crown ethers, cryptands, podands and antibiotic type ionophores such as valinomycin and macrotetralide actins. 5.2 A "reporter substance is one which is capable of interacting with an ionophore/ion complex to produce a change in, or appearance of, color or other detectable response. Preferred reporters are neutral compounds having a dissociable proton, which is capable of dissociating upon interaction of the reporter with the ionophore/ion complex to produce a detectable response. With the loss of a proton, the reporter becomes charged, effecting a change in electron distribution. The change in electron distribution produces a detectable response. The expression "reporter substance" includes phenolic compounds, such as p-nitrophenol, and naphthols which are relatively colorless in the nonionized state, but which color upon ionization, and fluorescent compounds which produce more or less fluorescence upon a change in electron distribution. The reporter substance can also be one which can trigger a detectable response together with other components. For example, the change in electron distribution in the reporter substance, caused by interaction with the complex, can in turn facilitate the interaction of the reporter with another component which would then produce a detectable response. Preferred reporters are disclosed in U.S. Patent Nos. 4,540,520 and 4,552,697 incorporated herein by reference. 5.3 By "interacting" is meant any coaction between a reporter substance and an ionophore/ion complex which leads to a detectable response. The interaction between an ionophore/cation complex and preferred reporters having a dissociable proton will cause the reporter to lose a proton thus producing a detectable response. An example of the reporter substance. interacting with the complex is the case where the reporter is changed by the complex from a colorless to a colored state, such as in the case of P-nitrophenol. 5.4 The expression "detectable response1, is used herein as a change in, or occurrence of, a parameter in a test means system which is capable of being perceived, either by direct observation or instrumentally, and which is a function of the presence of a specific ion in an aqueous test sample. Some detectable responses are the change in, or appearance of, color, fluorescence, reflectance, pH, chemiluminescence and infrared spectra. 5.5 The term "globule" as used herein refers to spherical or quasi-spherical globes, balls or other shaped particles of a substance such as form in biphasic suspensions or emulsions. When an oil-in-water suspension or emulsion is formed, the oil (hydrophobic) phase exists as spherical entities surrounded by a more or less continuous aqueous phase. The more energy supplied in forming the suspension, the smaller the size of the globules. Likewise, the globular size can be controlled by additives such as detergents and other emulsifying agents. Also included in the meaning of the term "globule" are finely divided particles of a solid material. Thus, where the hydrophobic vehicle is a hydrophobic solid material such as'a polymer, it can be ground or otherwise finely divided into solid particles. 5.6 By "hydrophilic" is meant that characteristic of a substance to have a strong or pronounced tendency to bind or absorb water. Included in the term are those materials which undergo swelling or formation of reversible gels with water, or which are wettable or permeable by water, or which form aqueous solutions. 5.7 As used herein, "substantially nonpolar" is intended as meaning that quality of a substance not to exhibit a substantial dipole moment or electrical polarity. In particular, it includes nonionic substances and substances which are dielectric. A "substantially nonpolar" material is intended to mean a hydrophobic material. Hydrophobic generally means that the material is immiscible with water. With preferred reporters used herein, hydrophobic is additionally taken to mean that in the absence of the complex of ionophore and ion in the nonpolar (or hydrophobic) layer, the reporter substance is in the protonated form. 5.8 The term "nonporous" is intended to mean substantially impervious to the flow of water. Thus, a nonporous carrier matrix is one which precludes the passage of water through it, one side to the other. For example, a polyvinyl chloride film will be considered for the purposes herein as being nonporous. 5.9 The phrase "hydrophobic vehicle" as used herein means a substance or substances which are capable of isolating the ionophore and reporter from the aqueous phase formed by contact of the sample with the test device. Thus the vehicle can be a solid or a liquid or a combination thereof, provided that it increases the ability of the ionophore/ion complex and the reporter to coexist in the hydrophobic globule. Useful vehicles include high boiling liquids such as nitrophenyloctylether, sometimes called "plasticizers" and polymers such as polyvinylchloride. 6. MULTILAYER TEST MEANS A multilayer test means of the present invention is composed of a reagent layer containing the ionophore and reporter substance incorporated in a carrier matrix and at least a reflecting layer, in laminar relationship. The reagent layer and suitable carrier matrices have been fully described in published European patent applications 84 104 824.2 and 84 104 828.3 which are incorporat ed herein by reference. Published European patent application 84 104 828.3 describes a nonporous, nonpolar carrier matrix containing a ionophore capable of interacting with the ion of interest and a suitable reporter substance. The nonporous nonpolar carrier is referred to herein as the "film" format. Published European patent application 84 104 824.2 describes a reagent layer in the form of an emulsion wherein finely divided hydrophobic globule S containing the ionophore and reporter are incorporated in a hydrophilic carrier matrix respectively. This type of reagent layer is referred to herein as the "emulsion" format. For the determination of cations, preferred reporters are neutral compounds having a dissociable proton, which proton is capable of dissociating upon interaction of the reporter with the complex of the ionophore and the cation to produce a detectable response. The preferred detectable response is color. Multilayer test devices will usually be read by reflectance measurement taken from the side opposite the side of sample application through a transparent support member. Additional components can be added to the reagent layer. Light scattering centers, described more fully below, can be added top either reagent layer format. When the reagent layer is a hydrophilic carrier containing finely divided hydrophobic globules, the. hydrophilic carrier provides a matrix for the incorporation of buffers, sodium chloride and preferred water soluble interferant removal substances. However, the addition of the reflecting layer and optionally the opacifying layer, provides a vehicle for the addition of sodium chloride and buffer which might otherwise destabilize the reagent layer. When the film format is used, the additional layers are needed to allow the incorporation, of these components into the test device. 6.1 Light Scattering Centers When instrumental reading by reflectance is used, it is advantageous to incorporate light scattering centers with reagent layer. The- us ' such centers effectively increases the precision the assay by reducing the effect of variations in dry film thickness. Light scattering centers can be produced by incorporating insoluble, inorganic particles such as titanium dioxide particles or equivalents such as barium sulfate, calcium car-. bonate, magnesium oxide, aluminum oxide, zinc oxide, lead oxide, microcrystalline cellulose or talc. A working range for incorporation of titanium dioxide particles is up to about 40% weight percent of a coating emulsion; a preferred range is from about 0.5 to about 15 weight percent of coating emulsion for the reagent layer. A particle size of less than one micron is preferred. 6.2 Sodium Chloride Addition to Decrease Hematocrit Dependence If a hydrophilic carrier incorporated with hydrophobic globules is used as the reagent layer of a multilayer test means for a whole blood electrolyte determination, sodium chloride can be incorporated with the hydrophilic carrier. The addition of approximately 0.1 to 0.2 M sodium chloride has been found to be sufficient to obviate the hematocrit dependence otherwise seen with whole blood potassium tests. The addition of salt is particularly advantageous in the multi layer format preferred for whole blood determinations and will be discussed more fully later in the specification. 6.3 Interferant Removal Substance Body fluids normally contain many cations, such as sodium ion (Na+), potassium ion calcium ion (cm ) and magnesium ion (Mg Although the ionophore will usually be chosen for its selectivity for the desired analyte-ion, in some cases the presence of other cations could interfere with the coaction of the ionophore with the desired analyte-ion and decrease the accuracy of the test. For example, Sodium Ionophore I will bind sodium ion in preference to calcium ion in a ratio of approximately 4 to 1. In samples where the ratio of sodium ion to calcium ion is less than 4 to 1, it may be necessary to prevent the interaction of calcium ion with the ionophore to ensure the proper relationship between sodium ion concentration and the detectable response. An interferant removal substance can be provided to obviate this problem. An interferant removal substance can be incorporated into the hydrophilic matrix or into the hydrophobic globules. In a preferred embodiment, the removal substance is designed to interact with an interfering cation so as to keep it in the aqueous phase formed by contact with the aqueous fluid sample, or otherwise prevent cation interaction with the ionophore in the hydrophobic globule. For example, ethylenediamine tetraacetic acid (EDTA) and ethyleneglycol bis(aminoethyl)- tetraacetic acid (EGTA) are water soluble compounds which form complexes with divalent cations, such as calcium ion. If EDTA is incorporated with the hydrophilic carrier matrix of the emulsion reagent layer for the determination of sodium ion, EDTA will preferentially bind calcium ion in an aqueous sample containing sodium and calcium ions. The bound calcium ion will not substantially interfere with the formation of the ionophore/sodium ion complex in the hydrophobic globule. In addition, ionophores can be used to remove interfering cations if they are specific for the interfering ion and are water soluble or are modified chemically to increase their water solubility without decreasing their ability to interact with the interferant. For example, Sodium Ionophore III (chemical name given in abbreviation list, structure can be found in published EP patent application 85 101 412.6) can be modified by the addition of solubilizing groups, such as (-SO3 H) groups, to the benzene rings to increase its water solubility without decreasing its ability to interact with sodium ion. Other compounds such as tran-1.2- diaminocyclohexane-N,N,N' ,N'-tetraacetic acid can also be used advantageously. 6.4 Buffer A buffer or combination of buffers can be incorporated with the hydrophilic carrier matrix of the emulsion reagent layer. Upon contact with an aqueous fluid sample, the buffer redissolves into the aqueous phase thus created, raising or lowering the pH to the desired level for the generation of the detectable response to proceed. With preferred reporters capable of losing a dissociable proton upon interaction with the ionophore/ion complex, the buffer mains a suitable pH for the reaction to proceed. Suitable buffers include, but are not limited to, bis [2-hydroxyethyl] imino-tris [hydroxymethyll - methane; 1,3-bis[tris(hydroxymethyl)methylamino]- propane, N,N-bis-(2-hydroxyethyl)glycine, tris(hydroxymethyl)amino-methane, N-[2-acetamidol- 2-iminodiacetic acid; N-2-hydroxyethylpiperazine-N' 3-propanesulfonic acid; 3 [N-tris (hydroxymethyl) - methylamino-2-hydroxypropanesulfonic acid; tetramethylammonium borate; 3-(cyclohexylamino)propane sulfonic acid and tetramethylammonium phosphate. The preferred pH range depends on the reporter substance. Therefore, the choice of the buffer is determined by the reporter substance used and to some extent by the desired detectable response. For example, when 7-decyl MEDPIN is used as the reporter, the preferred pH range is from 6 to 8.5. However, when a reporter substance having a higher pKa for the dissociable proton is used, a higher pH range will be preferred. Similarly when a reporter having a lower pKa for the dissociable proton is used, a lower pH range will be preferred. When the detectable response is a color change, the buffer can influence the degree of such detectable response, and a particular buffer can be chosen for color intensity optimization. For example, the useful pH range for the reporter, 7-decyl MEDPIN, occurs from about pH 6 to 8.5 where the color change is from orange to blue. A higher pH, pH 8.5 to 10, gives shades of dark blue which are difficult to distinguish visually, and a lower pH, pH 5 to 6, gives shades of pale yellow, also difficult to distinguish visually. Both pH extremes could be used with instrumental analysis, although the best instrumental precision occurs at the pH range of from about 6 to 8.5. Determination of a suitable pH is a routine laboratory experiment. 7. MULTILAYER TEST MEANS A multilayer test means for the determination of an ion in an aqueous fluid sample can be prepared by the addition of a reflecting layer and optionally an opacifying layer on top of the reagent layer. The reflecting layer contains a material or mixture of materials in the form of insoluble inorganic particles which provide a background to aid the user in determining the detectable response in the reagent layer of the device. In a preferred embodiment for whole blood determinations, the purpose of the reflecting layer is to screen the color of the red blood cells in the sample being tested from the color change to be observed by the user. A preferred substance for "screening purposes" is titanium dioxide. However, other materials can be used, for example, barium sulfate, calcium carbonate, aluminum oxide, magnesium oxide, zinc oxide, lead oxide, talc and microcrystalline cellulose. Such material is contained in the reflecting layer in an amount of from about 5 to 40 weight percent, preferably 15 to 40 weight percent, based on the total weight of the reflecting layer. Such materials generally have a particle size of less than one micron. The materials generally have a dry coating weight of 2.5 to 75 g/mê, (grams per square meters), preferably 10 to 25 g/mê. In addition to the inorganic substances, the reflecting layer can contain a hydrophilic substance such as gelatin. The hydrophilic substance is contained in an amount of 2 to 8 weight percent, preferably 2.5 to 5.5 weight percent, based on the total weight of the reflecting layer. Suitable hydrophilic substances include gelatin, agarose, poly(vinyl alcohol), poly(propyleneimine), copolymers of acrylic acid, carrageenan and alginic acid. Commonly, the remainder of the coating solution for the reflecting layer is water. Additionally, the reflecting layer may contain one or more wetting agents (surfactants) and/or one or more suspending agents. A nonlimiting example of a wetting agent which can be employed in the reflecting layer is Triton X-100, a polyoxyethylene surfactant available from Sigma Chemical Co. For example, in a test involving the determination of potassium, 0 to 0.5 weight percent Tritone X-100 can be utilized. Nonlimiting examples of suspending agents for use in the reflecting layer include gelatin, alginate and hydrophilic urethanes. The reflecting layer has a dry coating weight 2 in the range of 2.5 to 75 gm/m (grams per square meters), preferably 10 to 25 gm/mê. To prepare a multilayer test means, the reflecting layer is coated on the dried reagent layer and dried at about 400C for about 10 minutes. In a preferred embodiment, an opacifying layer is coated on top of the reflecting layer, i.e., the opacifying layer is optional. The opacifying layer has a wet layer thickness (thickness when applied) of 10 to 50 microns preferably 15 to 35 microns. The opacifying layer contains substantially inert particles for imparting an opaque appearance to the layer suspended in a hydrophilic substance. Hydrophilic substance and suspending agents used can be those as described in the reflecting layer. Such particles can be, for example, carbon black particles. The additional layers in the multilayer device can optionally include a buffer, an interferant removal substance and/or sodium chloride as described previously for the reagent layer. Prebuffering allows the test means or multi layer device to be used with unbuffered and undiluted sera or whole blood. Although buffer can be added to the hydrophilic matrix with the emulsion reagent layer, the presence of additional layers provides a vehicle for more buffer capacity which might otherwise have an adverse affect on the emulsion if incorporated directly into the reagent layer. A multi layer device including an opacifying layer is prepared by coating the opacifying layer on top of the reflecting layer and drying the whole device again at about 400C for about 10 minutes. In using the multilayer device, a sample is applied on top of the uppermost layer, i.e., the reflecting layer if no opacifying layer is employed, or the opacifying layer; and the detectable response, usually color, of the reagent layer after a certain timed delay is read from below. The multilayer format can be coated on or affixed to a transparent support. Useful transparent supports include polystyrene, polyester, polycarbonate, cellulose acetate and polyethyleneterephthalate. Polyethyleneterephthalate or cellulose acetate subbed to accept gelatin are preferred. A multilayered device 12 in accordance with a preferred embodiment of the present invention is depicted in Figures la and lb. As shown in Figure 1b the multilayered device 12 is composed of a transparent support layer 14 on top of which is coated a reagent layer 16. A reflecting layer 18 is coated on top of the reagent layer 16. As shown in Figure la an opacifying layer 20 can optionally be disposed on top of reflecting layer 18. A sample, 22, is placed on top of opacifying layer 20. Color development can be read from the bottom of layer 14 by the human eye or using a instrument such as a SERALYZER reflectance photometer (Ames Division, Miles Laboratories, Inc.) which has been adapted for ion determinations. The presence of the added reflecting layer or reflecting and opacifying layers effectively seal the reagent layer from the outside environment. Accordingly, the multilayer device protects the reagents in that without the added reflecting layer or added reflecting and opacifying layers the reagents would be exposed and, therefore, susceptible to damage due to mechanical contact. The presence of the added reflecting layer or added reflecting and opacifying layer also serve to prolong the stability of generated color. The use of the reflecting layer, or reflecting and opacifying layers, also provides a blocking mechanism to cells, proteins and other macromole cules, thus permitting the use of whole blood without washing or wiping the test device. In addition, due to the filtration capabilities of these layers, a multilayer test device for calcium measures ultrafilterable calcium, as bound calcium should not reach the reagent layer. Single layer and multilayer calcium test devices could be used to provide information on total calcium versus ultrafilterable calcium in a test sample. The working and preferred concentration ranges for a multilayer test means responsive to potassium ion are given below. Preferred ranges are given for the determination of serum potassium by reflectance on an Ames SERALYZER reflectance photometer. These concentrations can be used as a starting point for the determination of useful concentration ranges for the determination of other ions with other ionophores and reporters. The concentrations of ionophore and reporter refer to concentration in the volume of organic solvent used, other concentrations are defined as grams per 100 grams of solution. The reagent layer thickness for the multilayer test device can be from about 25 microns to about 500 microns, with a preferred wet thickness being from about 150 microns to about 200 microns. working preferred I. Reagent Layer Film thickness 25-500 150-200 microns microns Ionophore 10-500 mM 80-160 mM Reporter 10-120 mM 30-60 mM Light Scattering centers (optional) 0-40% 0.5-15% If the reagent layer is a hydrophilic carrier containing hydrophobic globules: Hydrophobic 5-15% 7-12% Vehicle Hydrophilic Carrier 5-15% 7-12% Buffer 0-0.5 M 0.2-0.5 M (optional) Interferant removal substance (optional) 0-30 gm/L 10-20 gm/L Wetting substance (optional) 0-3 gm/L 1-2 gm/L Sodium chloride (optional) 0-0.6 M 0.5-0.15 M If the reagent layer is a nonporous, nonpolar carrier matrix polymer 5-25% w/w 5-25% w/w hydrophobic vehicle 8-50% w/w 8-50% w/w II. Optional Multilayers 1. Reflecting layer titanium dioxide 5-40% 15-40% gelatin 1-6% 2-6% sodium chloride (optional) 0-0.6 M 0.05-0.5 M dry coating 2 2 weight 2.5-75 gm/M 10-25 gm/M 2. Opacifying Layer Carbon black 3-30% 7-15% gelatin 1.0-12% 1.5-68 sodium chloride 0-1 M 0-0.6 M film thickness 10-50 15-35 (wet) microns microns 8. EXAMPLES Abbreviations used in the examples are as follows: Square brackets, [), are used to designate ion concentration in millimoles per liter (mM) in the linear regression equations. All percent concentrations are given in weight per deciliter unless otherwise indicated. - Temperature: OC degrees Centigrade Length: cm centimeters Thickness: mil 1 mil is equal to 25.4 microns Weight: gm gram mg milligram Volume: dL deciliter mL milliliter pL microliter L liter Concentration: mM millimolar (millimoles per liter) M Molar (moles per liter) % w/v percent weight per deciliter % v/v percent volume per deciliter Ions: Na sodium ion K potassium ion Li lithium'ion Ca calcium ion ++ Mg magnesium ion Abbreviations for chemical components used are given below. The ionophore designations were assigned by the present inventors for convenience only. The name is usually based on the principal ion the ionophore was used to determined. However the ionophores commonly respond, to varying lessen degrees, to other ions. Structures of the ionophores named can be found in published European patent application 85 101 412.6. Ionophores Sodium Ionophore I 1,1,1-tris-[1'-(2t- oxa-4'-oxo-5'-aza 5'-methyl)-do decanyl]propane Sodium Ionophore II N,N'-dibenzyl-N,N' diphenyl-1,2-phenyl enedioxydiacetamide Sodium Ionophore III 6,7,9,10,18,19-hexa hydro-17-n-butyl-di benzo[b,k] ,[1,4,7,10,13] pentaoxacyclohexadecane 18-yl-oxyacetic acid Potassium Ionophore I 2,3-naphthol-1,4,7,10,13 pentaoxacyclopentadeca 2-ene Calcium Ionophore I diethyl-N,N'-[ (4R,5R)- 4,5-dimethyl-1,8-dioxo 3,6-dioxaocta methylene]bis(l2-methyl- aminododecanoate) Hydrophobic Vehicle NPOE 2-nitrophenyl octyl ether NPBE 2-nitrophenyl butyl ether Reporter Substance 7-decyl MEDPIN 7-(n-decyl)-2-methyl 4-(3',5'-dichlorophen 4'-one)-indonaphthol Miscellaneous EDTA ethylenediamine tetraacetic acid TRIS-C1 Tris(hydroxymethyl) aminomethane hydro chloride EGTA ethyleneglycol his (aminoethyl) - tetraacetic acid (G. Fredrick Smith Chemical Co., Columbus, Ohio) Triton X-100 polyethyleneglycol-p- isooctylphenyl ether (Sigma Chemical Co., St. Louis, MO.) NaDDBS Sodium dodecyl benzene sulfonate This invention will now be illustrated, but is not intended to be l-imited by the following examples. 8.1 Multilayer Potassium - Correlation of Serum and Whole Blood Measurements with the Reference Method The potassium ion concentration determined from a two layer test device was compared t th determination of potassium with a flame photometer reference method. Blood from fifteen normal subjects was drawn and the potassium concentration determined with the device, using the reflectance measured from 155-180 seconds. Serum was prepared by centrifugation and assayed with the device in the same way. Aliquots were also assayed by the flame photometer reference method. The reagent layer was prepared by emulsifying the hydrophobic vehicle, NPBE, containing 120 mM Potassium Ionophore I and 30 mM 7-decyl MEDPIN with a hydrophilic carrier and with the aid of butananedioic acid, dodecyl-4,4'-[ (1-methylethylidene)di- 4,1-cyclohexanediyl] ester referred to herein as an oil former. The emulsion was coated and dried before the reflective layer was applied. Reagent Layer: hydrophobic vehicle 8.3% gelatin 8.3% oil former 0.0428 polystyrene sulphonate 0.02% Tris-Cl 0.2M (pH 7.5) Wet Thickness: 375 microns Reflective Layer: gelatin 2.75% titanium dioxide 19% Wet Thickness: 82 microns Percentages given are gm per 100 ml of the coating solution. Test devices were prepared with a transparent support and the reflectance measured through the support with a SERALYZER . The data are shown below. The apparent potassium ion concentration (mM) for each data point is shown in parentheses. These apparent concentrations were calculated using the correlation equations for blood and serum. Reference [K ] Response from Device, K/S Sample* Concen. mM Blood Serum 1 4.40 1.484 (3.91) 2.043 (4.00) 2 3.80 1.399 (3.59) 1.977 (3.71) 3 3.85 1.536 (4.12) 2.190 (4.65) 4 3.80 1.525 (4.07) 2.046 (4.02) 5 3.65 1.444 (3.76) 1.992 (3.78) 6 3.55 1.380 (3.51) 2.020 (3.90) 7 3.55 1.451 (3.71) 1.854 (3.17) 8 3.85 1.585 (4.31) 2.004 (3.83) 9 3.90 1.433 (3.72) 1.964 (3.65) 10 3.85 1.303 (3.21) 1.949 (3.59) 11 4.25 1.456 (3.81) 2.079 (4.16) 12 4.00 1.391 (3.55) 1.944 (3.57) 13 4.35 1.731 (4.87) 2.162 (4.53) 14 4.65 1.734 (4.88) 2.270 (5.01) 15 4.25 1.679 (4.67) 2.074 (4.14) For blood, the correlation equation is: EMI30.1 regression coefficient = 0.653 standard error = 0.10 K/S For Serum: : EMI30.2 regression coefficient = 0.713 standard error = 0.076 K/S The results show good correlation between the concentration of potassium ion in both blood and serum measured with the test device and that measured by flame photometry over the critical concentration range of 3 to 5 mM potassium. 8.2 Addition of Sodium Chloride to Obviate Hematocrit Dependence of a Whole Blood Potassium Test The volume fraction of blood volume occupied by red blood cells, the hematocrit, is normally 40 to 42%. Inside the red blood cell the normal concentration of potassium ion is approximately 120 mM, whereas that in the serum is approximately 4 mM. Hence a potassium determination on whole blood is sensitive to a very small degree of red blood cell destruction (hemolysis). While the hematocrit is usually 40 to 42%, it can range from 30 to 70% in pathological states. It was found that the response of a single layer potassium test device was sensitive to the value of the hematocrit. This could lead to erroneous measured values of potassium ion concentration. A series of devices were prepared having a substantially common formula, but varying in the amount of sodium chloride (NaCl) added to the reagent or the reflective layers. An emulsion of an oil phase dispersed in a continuous aqueous phase containing gelatin was prepared using a high shear emulsifier. The oil former used was the same as that used in Example 8.1. The composition of the oil phase was Potassium Ionophore I 120 mM 7-decyl MEDPIN 30 mM oil former 0.68 NPBE remainder The final composition of the emulsion was Oil phase 8.31% Gelatin 8.31% Polystyrene sulfonic acid 0.02078 Tris-Cl buffer X pH 7.5 NaCl (shown on table) Percentages given are weight per volume ofithe phase referred to. The concentration of Tris Chloride used as the buffer, X, in device 1 was 0.2 M; the remaining devices were prepared with 0.166 M Tris-Cl buffer. The reagent layer was cast to a wet thickness of 175 microns on a polyester backing. The reflective layer contained titanium dioxide 19% gelatin 2.75% Tris-Cl buffer X pH 7.5 Triton X-100 0.03% NaCl (shown on table) The concentration of Tris-Cl buffer, X, used in device 1 was 0.1 M; the remaining devices were prepared with 0.062 M Tris-Ci buffer. The reflective layer was then spread on the dried reagent layer to a wet thickness of 82 microns. Concentration NaCl (M) [Reagent) [Reflective] Formulation Layer Layer Overall* 1 0 0 0 2 0.05 0.05 0.05 3 0.15 0.05 0.12 4 0.05 .5 0.19 5 0.15 .5 0.26 *The overall concentration of sodium chloride was -calculated by adding the salt concentration in each layer from the equation: EMI34.1 <tb> Overall <SEP> = <SEP> - <SEP> [reagent] <SEP> + <SEP> freflective] <tb> <SEP> (reagent <SEP> + <SEP> reflective <SEP> layer) <SEP> thickness <tb> wherein concentration in the reagent layer is. found by multiplying the reagent layer thickness by the sodium chloride concentration in that layer and concentration in the reflective layer is found by multiplying the reflective layer thickness by the sodium chloride concentration in the reflecting layer. Test devices were prepared and the potassium ion response measured as described previously. Samples of varying hematocrit were prepared. A high hematocrit sample (about 60%) was generated by gentle centrifugation and removal of some serum. A range of samples having the same potassium ion concentration but varying hematocrit was prepared by adding back different amounts of the autologous serum. Assay of the samples with the five device formulations showed that with less than about 0.1M sodium chloride, the potassium ion response decreases with increasing hematocrit, with too much sodium chloride the response increases. The addition of from about 0.1 to about 0.2 M overall sodium chloride provides a test device essentially independent of hematocrit. These results are shown in Figure 3. The overall molar concentration of sodium chloride in the test device formulation is marked for each response curve. 8.3 Multilayer Calcium Test Device A multilayer test device for the determination of ultrafilterable calcium ion can be formed with three layers: a reagent layer, a reflective layer and a opacifying layer. The composition of the layers would be as follows: Reagent layer: Oil 1.25 gm Gelatin 1 gm Tris buffer 8 gm (100 mM, pH 8) Triton X-100 0.05 mL NaDDBS 0.05 mL Reflective layer: gelatin 60 mL (10% w/v in Tris buffer) Titanium dioxide 36 gm Sodium hexa metaphosphate 0.1 gm Triton X-100 1 mL NaDDBS 0.25 mL Opacifying layer: Carbon Black 15 gm gelatin 60 mL (10% w/v in Tris buffer) NaDDBS 0.5 mL distilled water 30 mL The oil used in the reagent layer is composed of 0.1 gm Calcium Ionophore I, 0.05 gm 7-decyl MEDPIN and 5 mL NPOE. The carbon black used is available from Degussa Corp., Teterboro, N.J. under the trademark DERUSSOL Z35. The oil and the rest of the reagent layer is spread on a transparent plastic support with a Meyer's Rod to a wet thickness of 6.75 mil. (171.45 microns) and allowed to dry. The reflective layer is prepared by blending the ingredients above and spreading the mixture on the dried reagent layer to a wet thickness of 3.60 mil (91.44 microns). The two layered test means thus formed is again dried. The test means could be used at this point for a serum calcium ion determination. The opacifying layer is then applied by blending the above ingredients and spreading on to the reflective layer of the dried two-layer device to a wet thickness of 1.25 mil (32 microns). For convenience the multilayered test means is mounted on a rigid support member such as a transparent polystyrene which permits either visual or instrumental determination from the side of the device opposite the sample application. The supported test means is sometimes called a "test device". In use, one drop (approximately 50 microliters) of sample, (either whole blood or serum) is applied to the opacifying layer. Color development can be viewed through the transparent support and compared with a suitable color chart or preferably is read by reflectance at 640 nm (nanometers) by the Ames SERALYZER reflectance photometer. 8.4 Magnesium Test Device A reagent layer for the determination of magnesium ion can be prepared as follows. A solution is prepared containing 2.5 gm of magnesium ionophore (N,N'-diheptyl-N,N'-dimethyl-1,4-butane- diamide, available from Fluka Chemical Co., 0.050 gm of 7-decyl MEDPIN and 2.5 gm of NPOE. An emulsion of 1.25 gm of this solution in a hydrophilic carrier is prepared. The hydrophilic carrier is composed of: gelatin 1.00 gm Tris buffer 8.00 gm (100 mM, pH 8.5) Triton X-100 0.05 mL NaDDBS 0.05 mL The emulsion is spread on a plastic support such as a polyester to a thickness of 0.25.mil (6.35 microns) and dried. Reagent layers thus formed are expected to produce good response to magnesium ion. If calcium ion interference is possible, an appropriate level @@ EGTA can be incorporated with the hydrophilic --ierito selectively bind any calcium ion in the example. For clinical serum samples, 2 to 3 mM EGTA *,eold be appropriate. A reflectance layer and optionally a opacify ,-.g layer could be added as shown in Example 8.3 to ovide a multilayer device responsive to magnesium 8.5 Ultrafilterable Calcium Test Means Using a Multilayer Film A film stock solution is prepared using 8.55 gm 5% vinylidene chloride/95% vinylchloride copolymer (VdC/VC), 21.45 gm diethylphthalate and 70 gm cyclohexanone. The film is prepared containing: Film Stock Solution 1 gm 7-decyl MedPIN 10 mg Calcium Ionophore I 4 mg Tritone X-100 0.05 mL (18 in acetone) The film is spread with a doctor blade to a wet film thickness of about 10 mil (0.0254 cm) and dried. A titanium dioxide/gelatin mixture is prepared using 60 mL of 10% gelatin in TAPSO buffer (100 mM, pH 7.4), 18 gm Tits, 0.13 g sodium hexametaphosphate, 0.25 mL sodium dodecylbenzenesulfonate (NaDDBS), 0.4 mL Tritone X-100 and 0.1 mL Makon 6. The mixture is homogenized in a Waring Blender and spread on top of the dried VdC/VC film with a wet thickness of 3.6 mil (0.00915 cm) to form the reflecting layer. Optionally a carbon black layer may be spread on top of the TiO2/gelatin layer. This layer is made from a homogenized mixture consisting of15 gm Derussol Z35, 58 mL gelatin (10% in water), 0.86 mL NaDDBS and 32 mL water. Wet thickness was about 1.26 mil. With this formulation the free calcium concentration either serum or whole blood, may be determined. A drop of sample is placed on the carbon black side of the film. Protein bound calcium cannot pass through the gelatin layer and only ultrafilterable calcium can do so to cause the color development. Obviously many other modifications and variations can be made without departing from the spirit and scope of the invention.

Claims: WHAT IS CLAIMED IS: 1. A test means for determining the presence of an ion in an aqueous test sample, the test means comprising: (a) a reagent layer chosen from a group consisting of (i) a substantially nonpolar, nonporous carrier matrix incorporated with an ionophore capable of forming a complex with a specific ion to be determined and a neutral reporter substance having a dissociable proton, which proton is capable of dissociating upon interaction of the reporter with the complex of the ionophore and the cation to produce a detectable response; and (ii) a hydrophilic carrier matrix incorporated with finely divided globules of a hydrophobic vehicle, the globules containing an ionophore capable of forming a complex with a specific ion to be determined and a neutral reporter substance having a dissociable proton which proton is capable of dissociating upon interaction of the reporter with the complex of the ionophore and the cation to produce a detectable response; and (b) a reflecting layer disposed on top of the reagent layer and in laminar relationship thereto, the reflecting layer including one or more materials which act as a background in order to facilitate the determination of a detectable response in the reagent layer; and optionally, (c) an opacifying layer in laminar relationship to the reflecting layer and disposed on top of the reflecting layer, the opacifying layer containing particles for imparting an opaque appearance to the layer. 2. The use of the multilayer test device of claim 1 for the determination of potassium ion. 3. The multilayer test device of claim 1 in which the reagent layer is a hydrophilic carrier matrix incorporated with finely divided globules of a hydrophobic vehicle and an interferant removal substance, capable of interacting with interfering ions, is incorporated with the hydrophilic carrier. 4. The multilayer test device of claim .1 in which the reagent layer is a nonpolar, nonporous carrier matrix which matrix is incorporated with light scattering particles. 5. The multilayer test device of claim 3 or 4, additionally comprising a hydrophilic polymer in either the reflecting layer, the opacifying layer or both. 6. The test device of claim 5 additionally comprising a buffer in any or all of the layers. 7. The multilayer test device of claim 6 in which the sample is whole blood, additionally comprising sodium chloride incorporated in any or all of the layers including a hydrophilic polymer, to impart hematocrit independence to the ion determination. 8. The multilayer test device of claim 7 in which the total concentration of sodium chloride added is between 0.1 and 0.2 molar. 9. The use of the multilayer test device of claim 8 for the determination of potassium ion. 10. The use of the multilayer test device of claim 5 for the determination of ultrafiltrable calcium ion.

Inventors: CHARLTON, STEVEN C., FLEMING, ROGER L., HEMMES, PAUL, LAU, ARTHUR L.Y.
Applicants: MILES INC.
Application year: 1986
Main classification: G01N33
IPC codes: G01N33