Non-Stringy Adhesive Hydrophilic Gels

FIG. 1A shows a plot of the irradiation dose (Mrads) vs. PVP concentration (%) for adhesive highly stringy formulations, adhesive non-stringy formulations and those characterized as "dead."

FIG. 1B shows a plot of the irradiation dose (Mrads) vs. PEO concentration (%) for the various hydrogel formulations described in the disclosure including pituitous formulations, adhesive highly stringy formulations of prior art and the adhesive non-stringy formulations of the present invention. This plot shows that the regions defining each of the above-underscored surface properties are well-defined. The region above the upper boundary of the adhesive non-stringy formulations (i.e., those gels exposed to much higher doses of irradiation) comprises "dead" (non-adhesive) hydrogels.

FIG. 2 shows the Force-Displacement Profile (FDP) for a 4 weight (wt) % PEO (MW ca. 4.times.10.sup.6) formulation prepared according to the method of U.S. Pat. No. 3,419,006. It should be noted that this and all other FDP traces shown in the figures are not to vertical scale. However, all traces are plotted to the same horizontal scale.

FIG. 3A shows the FDP for a 9 wt % PEO (MW ca. 900,000) formulation, also containing 5 wt % potassium chloride and about 0.3 wt % biocides, prepared according to the method of U.S. Pat. Nos. 4,684,558, 4,706,680 and 4,777,954.

FIG. 3B shows the FDP for 10.5 wt % PEO (MW ca. 900,000) formulation, also containing 6.7 wt % magnesium acetate and about 0.3 wt % biocides, prepared in a fashion similar to that described in U.S. Pat. No. 4,777,954.

FIG. 3C shows the FDP for the gel contained in a Polyhesive.RTM. TENS electrode (transcutaneous electrical nerve stimulation) (APT-1060) manufactured by Valleylab, Inc. Boulder, Colo., USA.

FIG. 4A shows the FDP for a 7 wt % PEO (MW ca. 900,000) formulation, also containing 1 wt % of an aqueous frangrance-enhancing mixture and about 0.3 wt % biocides, prepared according to the methods of the present invention.

FIG. 4B shows the FDP for a 20 wt % PVP (MW 1.times.10.sup.6) formulation, also containing 1 wt % PEO (MW ca. 900,000), 5 wt % potassium chloride and about 0.3 wt % selected biocides, prepared according to the methods of the present invention.

FIG. 5 shows the FDP for a non-adhesive "dead" hydrogel prepared by prolonged irradiation of a PEO hydrogel prepared according to the method of U.S. Pat. No. 3,419,006.

FIGS. 6a-6j show the various stages experienced by a hydrogel material (non-stringy; highly stringy) during the test employed under the conditions described in the present disclosure.

The non-stringy hydrophilic gels employed in this invention are unique in that although they are electroconductive, they are substantially free of unbound water. This property is important for several reasons. First, it means that the gel does not "bleed" free water under the influence of pressure and/or elevated temperatures, which bleeding can adversely affect one or both of the gel's non-stringy adhesiveness and/or uniformity of conductivity. Second, it means the gel is not "broken" easily if subjected to temperatures near the freezing point of water. This characteristic is very important from a storage and shipping stability point of view. Finally, the gel's resistance against "bleeding" free water renders it more resistant to "drying out" after being removed from its sealed gas and moisture impermeable package.

Because sheets of non-stringy adhesive hydrogels need to be sterile, when used as bandages or as the skin contacting member of medical electrodes, the packaging of the sheet should be adaptable to ensure such sterility. Although this sterilization process cannot conveniently be achieved conventionally by autoclaving, because heating the electrode to extreme temperatures could adversely affect the polymer or alter the moisture content of the gel, sterility can readily be accomplished by other means, e.g., by treatment with ethylene oxide. Alternatively, the electrode may be packaged and subjected to the high energy radiation step which converts the starting viscous polymer mixture to a solid hydrogel. Such an irradiation process effectively and conveniently sterilizes the hydrogel and associated structural and packaging materials.

The non-stringy hydrogels employed in this invention are characterized by being semi-tacky non-stringy viscoelastic solids which, in the tack rolling ball method (TRBM) test described hereinafter, typically give a rolling ball distance of at least about 10 mm, when the ball employed has a diameter of 16.5 mm, and typically give an adhesion energy force in the Adhesion Energy Density (AED) Determination Test, described hereinafter, of at least about 5 g/cm and not exceeding about 50 g/cm. In the Force-Displacement Profile of these materials, the PF value is at least about 250 grams. Notably, these hydrogels also possess a swell ratio (SR) of at least about 2 and a value for the percent gel of at least about 80. Moreover, these sheets have greater cohesive strength than adhesive strength, whereby the sheet can be removed from a surface to which it is affixed without leaving a visible residue. Because the sheets of the present gels are integral single structures, much like films of thermoplastic polymers, they have excellent cohesive strength which prevents material from separating from the sheets when they are peeled off the subject's skin.

Unlike the conductive or non-conductive adhesive hydrogels of the prior art, however, the present hydrophilic gels are substantially non-stringy such that they may be applied and removed without the objectionable stringy sensation associated with the use of previous tacky gels. These previous materials are so tacky and sticky that tactile examination thereof leaves one with the strong impression that a residue is left on the skin after the gel is removed. Most people find this impression and the accompanying sticky, stringy sensation objectionable, even unacceptable. This extreme characteristic tackiness and stringiness is, therefore, undesirable. Quite surprisingly then, it has been discovered, that cohesive hydrophilic gels which are sufficiently tacky and adhesive and yet substantially non-stringy can be produced. The application and subsequent removal of the present non-stringy adhesive hydrogels are not accompanied by any discomfort or irritation, both physically and in matters of consumer distaste.

It has been discovered further that highly conductive hydrophilic gels may be produced which also embody the desirable characteristics of cohesiveness, adhesiveness, sufficient tackiness, non-aggressiveness, and non-stringiness mentioned above.

In a specific embodiment of the present invention, the hydrophilic gels are a homogeneous aqueous mixture of water and a crosslinked polyethylene oxide (PEO). Not only are they substantially or completely free of unbound water, the advantages of which are discussed above, they are substantially free of discrete uncrosslinked polymer which could settle, leach or bleed out or otherwise adversely affect the physical or chemical properties of the gels.

In another embodiment, the hydrophilic gels are a cohesive uniform mixture of water, an electrolyte, a crosslinked poly(vinyl pyrrolidone) (PVP), and viscosity-enhancing polymer. Not only are these gels substantially or completely free of unbound water, the advantages of which are discussed above, they are substantially free of discrete polymer particles which could settle out or otherwise adversely affect the physical, electrical or chemical properties of the gels. It should be noted that the hydrogel compositions described herein may exist as a multiphase system comprising the high molecular weight macromolecules which are present in the uniform mixture. The irradiative crosslinking process "freezes" in place these microphase regions to provide a stable highly useful material. In fact, the materials of the present invention remain substantially unchanged even after a storage period exceeding one year, under ambient conditions and with properly sealed packages. These materials even retain their desirable physicochemical and electrical properties for at least one month at an elevated temperature (e.g., at about 50.degree. C.).

The non-stringy hydrogels of the present invention are produced by exposing an aqueous mixture of least one water-soluble high molecular weight linear polymer to a dose of high energy ionizing radiation effective to form a gel-like material. A homogeneous aqueous mixture of PEO, present at a concentration of at least about 7 to about 35 wt%, preferably at least about 7 to about 20 wt%, may be used. Alternatively, an aqueous mixture of PVP and a viscosity-enhancing hydrophilic polymer may be employed. It has been found that irradiation of these extrudable viscous aqueous polymeric mixtures produce gels which are cohesive, adhesive, sufficiently tacky, and yet non-stringy.

For a conductive formulation, the homogeneous aqueous mixtures described above may be prepared with an effective amount of a water-soluble electrolyte present. Irradiation of these electrolyte-containing mixtures under the conditions described further below, gives conductive sheets having the desired non-stringy surface properties.

The PEO polymers useful in the present invention have molecular weights between about 200 kD to about 5,000 kD.

The PVP is typically a polymer of N-vinyl-2-pyrrolidone having a weight average molecular weight (M.sub.w) of about 200 kilodaltons (kD) to about 2,000 kD. An advantageous polymer is PVP having a M.sub.w of about 1,000,000. Homogeneous aqueous mixtures comprising about 5 to about 35 weight percent of PVP are suitable to achieve the objects of the present invention. Preferably, the concentration of the PVP in the aqueous mixtures are about 10 to about 35 weight percent, most preferably 15 to 25 wt%. The irradiation crosslinking of PVP mixtures are most recently described in U.S. Pat. No. 4,699,146 issued to Sieverding, the disclosure of which is incorporated herein by reference.

To reduce the transverse electrical resistance of the homogeneous aqueous mixtures described herein and consequently, the hydrogels which are produced therefrom, a variety of electrolytic substances may be added to the mixtures in amounts sufficient to produce conductive products. These electrolytes may be ionizable inorganic salts, organic compounds, or combinations of both. Examples of such salts include, but are not limited to, ammonium sulfate, monoethanolamine acetate, diethanolamine acetate, sodium lactate, sodium citrate, sodium chloride, magnesium sulfate, calcium sulfate, ammonium acetate, magnesium chloride, magnesium acetate, or combinations thereof. Preferably, the electrolyte used is stable and inert upon dissolving in the aqueous mixture and the subsequent radiation crosslinking step. Preferred salts are potassium chloride, sodium chloride, magnesium sulfate, or magnesium acetate. Potassium chloride is most preferred for EKG applications. Although virtually any amount of electrolyte may be present in the mixture, a breakdown in viscosity is observed as discussed further below, and it is preferable to have an amount of water-soluble electrolyte present at a concentration of about 0.1 to about 15 wt% of the mixture. However, the amount of electrolyte present must be effective to reduce the transverse electrical resistance of the mixture, and the resulting hydrogel, to an impedance at 10 Hz-5 MHz of less than about 1,000 ohms. Typically, about 5 wt% of an electrolyte such as potassium chloride, is sufficient to reduce the impedance at 60 Hz to much less than about 100 ohms.

It has been observed that the addition of certain electrolytes, particularly the inorganic salts, to aqueous PVP mixtures results in a breakdown of the viscosity of the initial electrolyte-free PVP mixtures. In general, the initially viscous mixture becomes less viscous to a point that it pours and spreads quite easily. Such a nonviscous mixture is difficult and taxing to work with because films of such materials do not retain their shape until the films are irradiated sufficiently. Specially modified conveyor systems have to be devised to keep such a material from running off any surface on which such a material is held. The configuration, shape, and thickness of the liquid films are thus difficult, if not impossible, to control reproducibly. Significantly, such free-flowing mixtures cannot be extruded successfully with conventional equipment, if at all. Furthermore, a production line, in which such nonviscous mixtures are to be treated, could not conveniently be interrupted even for very short periods of time. Such circumstances may adversely affect the electrical properties of an electrode assembly, as well.

It has thus been discovered that the introduction of a hydrophilic polymer having a weight average molecular weight in excess of about 100 kilodaltons, in as little as a few percent by weight of the total mixture, can enhance the viscosity of the conductive polymeric mixture such that the final viscosity is restored to a degree providing coatable, extrudable viscous aqueous polymeric mixture. Furthermore, when exposed to radiant energy at an effective dose, a film of the extrudable aqueous mixture is transformed into a cohesive gel-like solid having the desirable highly conductive tacky yet non-stringy adhesive properties characteristic of the hydrogels of the present invention.

As stated above, the viscosity-enhancing hydrophilic polymer should have a sufficiently high weight average molecular weight, M.sub.w. In general, such a polymer should have a M.sub.w in excess of about 100,000 or 100 kilodaltons (kD). The viscosity-enhancing hydrophilic polymer may have a M.sub.w as high as 10 or 15 million. Such a polymer may be derived from natural, synthetic, or semisynthetic sources; it may be linear, branched, crosslinked, noncrosslinked, water-soluble, or water-insoluble, so long as it is hydrophilic in nature.

Example: of suitable synthetic materials useful as viscosity-enhancers include, but are not limited to, polyacrylamide, poly(vinyl alcohol), a polyacrylate salt, poly(ethylene oxide), poly(ethylene imine), polyacrylamide sulfonic acid or their salts, polyacrylonitrile, hydrophilic derivatives, mixtures, blends, or copolymers thereof. A preferred polymer is poly(ethylene oxide) having a M.sub.w of about 500 to about 10,000 kD, preferably about 900 kD.

Some very useful semisynthetic polymers are the derivatives of cellulose. For example, methylcellulose, ethylcellulose, carboxymethylcellulose, hydroxyethylcellulose, or the like may be used to good advantage. A particularly useful cellulose derivative is a carboxymethycellulose (CMC) having a weight average molecular weight of about 700,000, such as CMC-7HF available commercially from Aqualon Company (Wilmington, Del.).

The addition of such viscosity-enhancers to the aqueous electrolyte PVP mixtures in as little as 1 to 2 wt% of the mixture increases the viscosity to at least about 8,000 cps, preferably 10,000-20,000 cps.

Other suitable macromolecules derived from natural sources include, but are not limited to, starch, agar, dextran, dextrin, carrageenan, xanthan, guar, their derivatives, or mixtures thereof.

Other components may also be present in the highly conductive non-stringy adhesive hydrogels of this invention, if so desired. It is important to keep in mind, however, that one of the advantages of the instant hydrogels is that they can be prepared with all the attendant properties and surface characteristics described herein without the need for extraneous chemical crosslinking agents, monomers, and the like. One should therefore try to minimize the presence of any additive which may be present so that the full benefits of the invention may be realized. In addition, the presence of these additional components may necessitate an adjustment in the dosage of radiant energy applied to the resultant extrudable viscous mixtures to arrive at the non-stringy hydrogels of choice. This adjustment generally requires further exposure of the multicomponent mixtures to high energy radiation. For instance, additives may be uniformly dispersed in the instant aqueous mixtures (and, consequently, the resulting hydrogels), which additives comprise preservatives, stabilizers, fire retardants, pigments, refractive particles, antifungal agents, bacteriacides, antibiotics (e.g., neomycin or silver sulfadiazine), cosmetics (e.g., glycerine, urea, allantoin, sulfur, anthraquinone, hydroquinones), moisturizers, pharmaceuticals, anesthetics (e.g., benzocaine), anti-microbials (e.g., mercurochrome, silver sulfadiazine, povidine iodine, iodine), healing agents (e.g., collagen), and the like. These additives may be present in individual or total amounts of about 0.001 to about 6 weight percent of the total mixture, preferably not exceeding about 3 wt % in the final product.

Specific examples of preservatives or "biocides" include, but are not limited to, Dowicil-200.RTM., methyl paraben, ethyl paraben, propyl paraben, butyl paraben, paraben salts, Cosmicil.RTM., glydent, germall, or combinations thereof. Other formulations for use in topical applications may further comprise boric acid, Burrows solution, and the like.

A hydrogel conductive sheet suitable for use in a medical electrode of this invention can be produced by mixing the water soluble poly(vinyl pyrrolidone) with the selected electrolyte and water to form an aqueous mixture. The viscosity-enhancing hydrophilic polymer may then be added to give the extrudable viscous feed. Alternatively, particularly with CMC as the viscosity-enhancer, one slowly blends the dry polymer into an aqueous mixture of the electrolyte, viscosity-enhancer, and additive, either at ambient or elevated temperatures. Preferably, the viscosity-enhancing hydrophilic polymer is added to a sufficient quantity of water to provide a viscous solution. To this solution is added sequentially the major matrix polymer followed by the electrolyte. Alternatively, a hot solution of the polymer can be prepared and a concentrated solution or mixture of the selected salt viscosity-enhancer and additive slowly blended therewith to achieve the desired or final concentration of desired components. The viscous liquid feed is then extruded, preferably onto a flat surface to form a liquid film thereon, e.g., a film of PVP-solution or a PVP-solution coated sheet of polyethylene. To contribute to the strength of the hydrogel both in tension and flexure a low area-weight scrim can be incorporated during fabrication before crosslinking. The scrim which is in intimate contact with the hydrogel can be of mesh type geometry, either woven or non-woven, e.g., non-woven monofilaments heat sealed together at their interstices or a sheet of thermoplastic polymer with holes in a geometric pattern heat-stamped therein, provided the scrim in is of substantial open area and low area weight, e.g., from about 0.1 to 5 mil in thickness and an area weight of about 0.002 to 0.2, preferably about 0.003 to 0.1 g/inch.sup.2. Preferably, the scrim and the hydrogel material are present in a range of thickness of about 0.25 to about 2.5 mm. The scrim is preferably fabricated from a natural or synthetic hydrophobic polymer, e.g., a polyethylene, polypropylene, polyester, polyamide homopolymer. These materials are preferably non-plasticized water-insoluble polymers so that they cannot leak impurities into the hydrogel.

The resulting liquid film is then subjected to a dose of high energy radiation sufficient to convert said film into a non-stringy adhesive solid gel. To facilitate production, the liquid film is preferably backed on one or both sides with a thin peelable hydrophobic sheet, e.g., polyethylene or plastic coated release paper, before it is irradiated. Either or both plastic sheets are then peelably removable after formation of the hydrogel sheet, either before packaging or before use. The hydrogel sheet, which is now a viscoelastic solid, can be cut to desired size and shape for use as the conductive element that contacts the skin in a fabricated electrode device. Depending upon the application, different types of backing sheets can be used on one or both sides of the hydrogel sheet, e.g., a non-peelable sheet can be used on one side only or a peelable sheet on one side and a non-peelable sheet on the other.

The poly(vinyl pyrrolidone) formulations useful in these applications include those incorporating and binding high concentrations of water while maintaining adequate surface tack (adhesiveness), sufficient strength (cohesiveness), and substantial non-stringiness. The polymer/salt/viscosity-enhancer/water mixture should be viscous enough to be extrudable and to form into a sheet-like configuration, e.g., a liquid film of about 0.1 to 2 mm thickness, before crosslinking. Preferably, the viscosity of the aqueous mixtures exceeds about 8,000 cps. If a scrim is incorporated into the body of the mixture, the mixture should project beyond both faces of the scrim and all surfaces of the scrim should be wet with the solution. This casting technique is possible with conventional equipment and can be continuous, thereby forming an elongate continuous sheet or film, or discontinuous, i.e., applying individual segments of the mixture of a size and shape corresponding to single electrodes. Any quantity of the extrudable viscous aqueous mixture may be applied to a backing film to form a sheet of hydrophilic gel capable of yielding a plurality of individual interfacing means for individual electrodes, or a large single sheet which can be cut up to form a plurality of interfacing means. The sheets may also be cut into long strips and rolled into rolls as a tape. The thickness of the aqueous film mixture that is applied to the backing sheet generally is dictated by the viscosity of the solution and whether or not a scrim is incorporated therein.

After the viscous mixture is applied or cast to the desired thickness, it is then subjected to crosslinking high energy irradiation, such as a high energy electron flux as produced by an electron accelerator or Van De Graaf generator. In general, alpha particles, beta particles, gamma rays, X-rays, electron beams, or high energy ultraviolet radiation may be used effectively to initiate or precipitate the crosslinking of polymer chains. The major requirement is that the beam of electrons be of sufficient energy to completely penetrate the mixture, so that the mixture receives a radiation dose effective to crosslink the entire cross section of the sample. Proper dose/energy/thickness relationships are readily available to those skilled in the art of radiation processing and therefore need not be discussed in detail. To achieve the desired degree of uniform crosslinking, i.e., effective to convert the viscous polymer/viscosity-enhancer/salt/water mixture into a viscoelastic non-stringy adhesive gel-like solid, doses typically of about 0.5 Mrads to about 4.5 Mrads, and usually about 0.5 to about 2 Mrads are required, depending upon the selected polymer, its concentration, viscosity-enhancer and its concentration, the selected salt and its concentration and the presence or absence of selected functional, therapeutic agents, or other additives. Most preferably, these formulations are indicated at a dose of about 0.7 to about 1.8 Mrad.

As a further guide to the reader, the following relationships are provided to define more precisely the upper and lower dose ranges which give the desired non-stringy surface properties:

in which C is the concentration of the PVP expressed as a weight fraction of the total mixture. The region of the dose (Mrads) versus polymer concentration (wt%) curve encompassed by these limits is illustrated in FIG. 1A. The region of the plot below curve A(C) yields PVP gels having adhesive highly stringy surfaces. The region above the curve NS(C) provides PVP gels which may be characterized as "dead" (non-adhesive).

In one specific embodiment of the present invention, a conductive non-stringy adhesive hydrogel is produced from an aqueous mixture comprising 20 wt% PVP, 1 wt% PEO (as the viscosity enhancer), 5 wt% potassium chloride, 0.1 wt% Dowicil-200, 0.02 wt% propylparaben, 0.15 wt% methylparaben, 0.02 wt% ethylparaben, and 0.007 wt% butylparaben. The extrudable viscous aqueous mixture may be irradiated under a variety of dosage conditions (See, Examples Section). In yet another specific embodiment of the present invention an aqueous mixture comprising PVP (15 wt%), CMC (1.5 wt%), KCl (5 wt%), Dowicil-200 (0.1 wt%), methylparaben (0.15 wt%), and propylparaben (0.03 wt%), is also irradiated under several dosage conditions, as described in the Examples Section to provide useful hydrogels according to the present invention. The physical properties of the resulting hydrogels are disclosed in Table I including the AED and TRBM values, SR, and % gel. The corresponding electrical data on two hydrogels in particular are presented in Table III. Most preferably, the hydrogels of the instant invention have AED values of at least about 7 g-cm/cm.sup.2, TRBM values of at least about 15 mm, swell ratios of at least about 5, and percent gels of at least about 80. After the conductive hydrogel sheet is irradiated and converted into a viscoelastic solid, it can then be incorporated into an electrode. First it is cut to size, if it is not formed in its desired final shape. If both faces of the hydrogel are covered with backing material, one of its faces is freed from the backing material. The side freed from the backing material is then affixed to a non-porous support conductive member, e.g., a material which contains a conductive metal button, snap, or tab of conductive foil-polymer laminate which is capable of receiving an electrode lead wire and connector to an external electrical apparatus. The electrode is then ready to be packaged. The final package preferably is a gas, moisture and microorganism impermeable sealed pouch or envelope, e.g., formed by heat sealing a heat sealable aluminum foil polymer laminate.

When a packaged electrode is ready for use, it is removed from its package, the remaining backing material is released by peeling it from the gel interfacing sheet, and it is applied to the skin of the patient. The electrode lead wire is then attached to the electrode at the fastener conductive member. Alternatively, the lead wire can be attached to the electrode before the remaining backing material is removed, the backing material then removed and the electrode with the connecting wire attached applied to the skin. Alternatively, the packaged electrode can be provided with its own electrode lead wire already attached. The same sequence of backing material removal and application of the electrode to the skin would then apply without the necessity of attaching a lead wire to the electrode before or during application.

The hydrogel interfacing member of the electrodes of this invention have high adhesive strengths, which means that they can readily be affixed to the skin and will adhere thereto with little risk of accidentally dropping off through loss of adhesion. At the same time, the hydrogel interfacing member is substantially non-stringy and is, therefore, more comfortable and more readily acceptable to the user. Because the interfacing member is water based, it is relatively immune to the effects of moisture on the skin and will not slide off as a result of perspiration forming under the electrode while affixed to the skin. They also have high cohesive strengths, which means that they can be removed from the skin after use without leaving any visible residue. Interestingly, although the gels have a high adhesive strength, it is not high enough to pull hairs from the skin or otherwise damage the skin when the gel is removed therefrom. Furthermore, the use of the present gels is not associated with any objectionable sensation.

The medical electrodes of this invention containing a sheet of a PVP/viscosity-enhancer/electrolyte hydrophilic solid gel, as disclosed herein as a skin interfacing member, can assume a wide variety of shapes and construction, which are within the knowledge and skill of the practitioner in the art.

Because the hydrogels will lose water eventually under ambient conditions, they are preferably stored in a water and gas impermeable container, e.g., a polyfoil packet formed from the laminated plastic conventionally used to store measured amounts of freeze-dried or ground coffee. Sealed envelopes are conventionally produced by heat sealing a pair of sheets of thin plastic around the hydrogel sheet-backing laminate, or medical electrode in which a hydrogel sheet is mounted, or by heat sealing the open end of an otherwise sealed packet or envelope formed from a single sheet of the laminate.

If the film or sheet of instant PVP hydrogel is to be stored separate from the components of the medical electrode with which it is to be used, both faces thereof are preferably covered with a sheet of peelable release liner, e.g., polyethylene. If the sheet of hydrogel is to be stored mounted in the medical electrode with which it is to be used, its exposed face, i.e., the face to be applied to the skin, is covered with such a release liner. If both faces are covered with a release liner, optionally different liners can be employed, one of which is more readily removable therefrom than the other, e.g., a sheet of polyethylene covering one face and a sheet of "Mylar" plastic covering the other, thereby ensuring that a predetermined face of the film or sheet is exposed first. In some end use applications, one of the faces of the film or sheet is covered with a conductive liner which is not removable and is used as a conductive member in the final electrode assembly. Other variations should be evident to the skilled practitioner.

The present hydrogel sheet or film can be packaged singly or in multiples between the release liner or liners. In TENS end uses, it is desirable to mount a plurality of spaced apart circles, squares or rectangles of the film or sheet of the hydrogel on a plastic sheet, e.g., a 2 mil film of "Mylar" plastic and cover their exposed face with a different release liner, e.g., a 2 mil film of polyethylene or a sheet of polyethylene coated paper release liner. Either or both of the facing films can be appropriately scored to facilitate removal of the units of PVP hydrogel sequentially. If desired, one face of a plurality of units of the hydrogel can be covered with a large backing sheet, one facing film which is unscored and the other face covered with a release liner of the same dimensions as the units of the hydrogel so that a unit of the hydrogel and the latter release liner can be peeled off together, one at a time from the large backing sheet.

In another embodiment, a large sheet of a laminate formed from the PVP hydrogel and films of plastic covering its faces, e.g., a film of polyethylene on one face and a film of Mylar on the other, is scored at spaced intervals in both directions thereby producing a plurality of severable square or rectangular units of the laminate, each for use individually in conjunction with a medical electrode by tearing the laminate along a pair of perpendicularly positioned lines, thereby releasing a unit of the laminate from the sheet.

When the sheet of conductive PVP hydrogel is of the same dimension as a release liner covering an exposed face thereof, removal of the latter is facilitated if the latter is slit into pieces, thus providing an edge which can be easily raised with a fingernail or tool.

If desired, a plurality of circles, squares or rectangles of the hydrogel with a release liner covering one face can be "stacked" one upon the other so that a column of such units of the hydrogel sheet with both faces covered with a release liner is formed. Desirably, in such an arrangement, one side of the release liner has a higher adhesive value than the other, so that only one unit of the hydrogel is removed at a time from the column. Such columns can be conveniently stored in glass jars or aluminum lined paper tube with a moisture impervious cap which form a gas and moisture impervious sealed container.

A hydrogel sheet suitable for use as a medical adhesive can be produced by mixing the water soluble linear polyethylene oxide and water to form a viscous feed. A convenient procedure is to blend gradually the dry polymer into the appropriate amount of water, either at ambient or elevated temperatures. The viscous liquid feed is then applied to a flat surface to form a liquid film thereon, e.g., a film of polyethylene or a polyethylene coated sheet of paper. To contribute to the strength of the hydrogel, both in tension and flexure, a low area-weight scrim can be incorporated into the film during fabrication before crosslinking. The scrim can be of mesh type geometry, either woven or non-woven, e.g., non-woven monofilaments heat sealed together at their interstices or a sheet of thermoplastic polymer with holes in a geometric pattern heat-stamped therein, provided the scrim is of substantial open area and low area weight, e.g., from about 0.1 to 5 mil in thickness and an area weight of about 0.002 to 0.2, preferably about 0.003 to 0.1 g/inch.sup.2. The scrim is preferably fabricated from a natural or synthetic hydrophobic polymer, e.g., a polyethylene, polypropylene, polyester, or polyamide homopolymer. These polymeric materials are preferably nonplasticized so that they cannot leak impurities into the hydrogel.

The resulting liquid film is then subjected to high energy radiation, such as an electron beam, where it is converted into a solid crosslinked viscoelastic gel. To facilitate production, the liquid film is preferably backed on one or both sides with a thin peelable hydrophilic sheet, e.g., polyethylene or plastic coated release paper, before it is crosslinked. Either or both plastic sheets are then peelably removable after formation of the hydrogel sheet, either before packaging or before use.

The hydrogel sheet, which is now a viscoelastic solid, can be cut to the desired size and shape for use in applications that contact the skin. Depending upon the application, different types of backing sheets can be used on one or both sides of the hydrogel sheet, e.g., a non-peelable sheet can be used on one side only or a peelable sheet on one side and a less readily or non-peelable sheet on the other.

The polyethylene oxide formulations useful in these applications include those incorporating and binding high concentrations of water while maintaining adequate surface tack (adhesiveness), to avoid leaving a residue. The starting water soluble linear polyethylene oxide must have a molecular weight high enough to form a viscous solution for processing and readily crosslink. Generally, polymers with weight average molecular weights of about 0.2.times.10.sup.6 -10.times.10.sup.6 and, preferably about 0.5.times.10.sup.6 -5.times.10.sup.6. Daltons, are employed. The concentration of polmer therein typically is from about 7 to 35 wt%, preferably about 7 to 20 wt%, of the overall mixture, depending upon its molecular weight. The polymer water solution should be viscous enough to form into a sheet-like configuration, e.g., a liquid film of about 0.2 to 4 mm thickness, before crosslinking. Illustrative viscosities range from about 2,000 to 2,000,000 cps. The polymer solution is formed into a liquid sheet or film by coating onto a backing film or sheet. If a scrim is incorporated into the body of the solution, the solution should project beyond both faces of the scrim and all surfaces of the scrim should be wet with the solution. This casting technique can be continuous, thereby forming an elongate continuous sheet or film, or discontinuous, i.e., applying individual pools of the solution of a size and shape corresponding to single units. Any quantity of the viscous solution may be applied to a backing film to form a continuous sheet of hydrophilic gel about 10 to 150 mils (0.254-3.81 mm) capable of yielding a plurality of adhesive pads or the sheet can be cut into long strips and rolled as a tape. The thickness of the aqueous polymer solution that is applied to the backing sheet generally is dictated by the viscosity of the solution and whether or not a scrim is incorporated therein.

After the viscous solution is applied or cast to the desired thickness, it is then subjected to crosslinking high energy irradiation, such as a high energy electron flux as produced by an electron accelerator. If conditions are selected which exclude atmospheric oxygen, gamma radiation may be used. The major requirement is that the beam of electrons be of sufficient energy to penetrate completely the solution, so that the solution receives a radiation dose effective to crosslink the entire cross section of the sample. Proper dose/energy/thickness relationships are readily available to those skilled in the art of radiation processing and therefore need not be discussed in detail. To achieve the desired degree of uniform crosslinking, i.e., effective to convert the viscous polymer solution into a viscoelastic solid gel, doses typically of about 0.20 to 5.0 Mrads and usually about 0.75-2.0 Mrads are required, depending upon the selected polymer molecular weight, and its concentration. If selected functional or therapeutic additives are included in the viscous polymer solution, the radiation dose may be further shifted within this range. Generally speaking, higher polymer concentrations require high irradiation doses to produce an acceptable viscoelastic solid gel than lower polymer concentrations.

As a further guide to the reader, the following relationships are provided to define more precisely the upper and lower dose ranges which give the desired non-stringy surface properties:

in which C is the concentration of the PEO expressed as a weight fraction of the total mixture. The region of the dose (Mrads) versus polymer concentration (wt%) curve encompassed by these limits is illustrated in FIG. 1B. It should be pointed out that this non-stringy region lies above the highly stringy region previously described in U.S. Pat. No. 4,684,558).

The relationships which define each of the regions shown in FIG. 1 are derived from the same basic equation:

in which C is the concentration of the PEO in the formulation. The values of M, A and B for the pituitous materials, P(C), and the adhesive highly stringy material, A(C), have been defined previously in U.S. Pat. No. 4,684,558. These values, together with the values corresponding to the upper boundary of the present adhesive non-stringy hydrogels, NS(C), are given below.

If a gel is desired which is electroconductive and/or which has a physiological salinity, an electrolyte can be incorporated into the starting viscous solution of the linear polethylene oxide. Typically an aqueous solution of about 0.1 to 15 wt%, preferably about 0.7 to 10 wt% of a water soluble salt, preferably a dermatologically acceptable metal salt, more preferably in alkali metal salt or alkaline earth metal salt, e.g., sodium chloride, potassium chloride, or a magnesium salt is employed, the specific concentration depending on the condutivity desired in the hydrogel produced therefrom, generally having a transverse electrical resistance to an impedance at 60 Hz of less than 1,000 ohms and preferably less than 100 ohms are desired. Such a salt solution is combined with a water soluble linear polyethylene oxide by mixing to produce a homogeneous viscous solution.

As stated above, the hydrogels employed in this invention are characterized by high conductivity, surface adhesiveness, sufficient cohesiveness to maintain structural integrity when being removed from the skin, while being substantially non-stringy.

The manner in which hydrogel film of this invention adheres to the skin is an important aspect of this invention. The hydrogel adheres sufficiently to both dry, damp, clean, or soiled skin. It is tolerant to perspiration which forms from the skin under the hydrogel after the electrode is applied to the skin, because the hydrogel can adsorb a substantial amount of water before it loses its surface tack. Conversely, because it is 65%+ water, it does not create chemical bonds with the skin and hair which results in pain and/or skin damage when an electrode employing a conventional adhesive-based skin interfacing member is removed after use, and, because it is substantially non-stringy, the present hydrogel is much more comfortable in its use and is less objectionable, less sticky to the touch.

To test for skin adhesiveness, samples of the hydrogel with backing removed from one side can be applied to the skin and left on. This step is done both with the scrim-containing hydrogel films alone and with a scrim-containing hydrogel film attached to a support backing bearing a metal conductive snap electrical terminal. How well the hydrogel adhered to the skin is then observed and how easily the electrode material can be separated from the skin is noted, along with whether or not any residue is left on the skin.

The adhesiveness and tackiness of the conductive hydrogel sheet or films can be quantified by the "Tack Rolling Ball Method" (TRBM) as specified by the Pressure Sensitive Tape Council. This test method for adhesive materials is detailed in The American Society for Testing Materials, Designation D3121-73 (Re-approved 1979) which test method is under the jurisdiction of ASTM Committee D-14 on Adhesives. The test utilizes an inclined trough which can be obtained through the Pressure Sensitive Tape Council, 1201 Waakegan Road, Glenview, Ill. 60025, that is equipped with a release lever at the top through which a 16.5 mm diameter, 21.7 g steel ball is released onto the trough. The ball gains momentum as it descends the incline and rolls onto the adhesive surface whose adhesiveness is being measured, the shorter distance the ball travels thereon, the higher the adhesion value. In some cases, an 11 mm diameter, 5.6 g ball is used also.

The test is performed as follows: Remove the backing materials from both sides of a hydrogel sample cut one inch wide and at least three inches long. The test is run in a controlled environment (72.degree. F..+-.5.degree. F. and 50% +10% relative humidity). A hard, horizontal surface of sufficient size to conduct the test is selected. Both metal and glass plates have proved satisfactory. Before testing each adhesive sheet, clean the inclined trough thoroughly with isopropanol.

The specimen to be tested is placed flat, adhesive side up, in line with the inclined trough. The end of the specimen opposite the incline is held to the table. Only one test is run on each specimen. Each time before the ball is rolled onto the hydrogel, it is thoroughly cleaned with distilled water, isopropanol, or another appropriate solvent, which removes any residue that might otherwise remain from a previous test, and then wiped with a lint-free, bleached, absorbent material to remove any remaining residue. After cleaning the ball or raceway is not touched. Use clean, dry tongs to place the ball on the upper side of the release. Release the ball and it will roll to a stop on the adhesive material. Measure the distance from the point where the ball initially contacts the adhesive to where the ball stops. The average of the stopping distance measurements of five or more tests is recorded. Pertinent additional comments based on visual inspection such as noticeable residue on ball, lift of adhesive from substrate, etc., are noted.

In this test, the hydrophilic gels employed in the electrodes of this invention have tack rolling ball distances, with the 16.5 mm ball, of at least about 10 mm, preferably at least about 15 mm. The preferred gels have distances of less than about 60 mm.

Another test that quantitatively measures the extent of crosslinking in a polymeric mixture involves an extraction test. This test provides % gel values and is carried out substantially as described below. A two inch by two inch piece of PVP gel and weighing about 2.5 grams is extracted with 200 mL of distilled water for 72 hours at ambient temperature. The excess water is then removed from the swollen sheet which is then weighed (See, the swell ratio, infra). The swollen sheet is then baked in a 50.C oven for 24 hours. The resulting desiccated gel is then weighed. The ratio of the "dried" gel weight over the original weight of the polymer in the sample is the gel fraction or % gel. Preferred hydrogels of the present invention have % gel values of at least about 80 percent.

Another important feature for an adhesive sheet especially one that is intended for utilization in wound management applications is its absorptive capacity. This property is important because an adhesive on the skin can readily lose its adhesive bond due to a layer of perspiration accumulating at the interface. Moreover, if an adhesive material is utilized as a wound dressing it must be capable of absorbing the exudate from the wound, as this is one of its primary functions. If the gel cannot do so, it will also lose its adhesive bond and move from the site where it was intended to function. For these reasons it is very important for the adhesive sheet to have good equilibrium or absorption capacity for aqueous liquids. A test method that quantitatively measures the absorption capacity of a crosslinked polymer system is the swelling test.

The test method proceeds in exactly the same manner as the extraction test previously mentioned, up to the point of extraction. The weight of the extracted sheet, with unbound excess water removed from the surface, divided by the weight of the original sheet is the swell ratio (SR). In the hydrogels of the present invention, it has been discovered that the preferred embodiments which are highly conductive and adhesive and yet substantially non-stringy are those which have an absorptive capacity, as measured by the swell ratio (SR), of at least about 2.

Another test to measure relative strength and stickiness of an adhesive bond is the Adhesion Energy Density Determination test. This test measures how well a hydrogel sheet adheres to a flat surface. The adhesion energy which is measured is the combined strength of the surface bond of hydrogel sheet to the flat surface and the strength of the hydrogel sheet itself (i.e., a combined cohesiveness/adhesiveness test.

A sample of the hydrogel sheet to be tested is placed unbacked on a clean flat stainless steel block. The block in turn is placed on a block of flexible foam which in turn is placed on a test stand. With the setup in place a steel ring is placed on top of the test sample and aligned with the test probe to be used so that the latter will descend therethrough without touching the ring. A cylindrical (1 inch diameter) polymethylmethacrylate test probe then descends into the sample at a constant rate to a constant depth. (In the hydrogel films tested, the descent rate is set at 0.5 mm/sec. and the penetration is set at 1.0 mm.) Before the test probe is made to descend it is cleaned with isopropanol or distilled water and dried with a lint-free cloth, to make certain no residual adhesive material is on the face of the probe before the test is begun. All tests are run at 72.degree. F..+-.5.degree. F. and at a relative humidity of 50%.+-.10% and each test sample is stored at these conditions for at least one hour before the test. When the test probe has achieved 5 grams force, it then descends 1 mm into the hydrogel sheet and begins its return (at a rate of ascent of 0.344 cm/sec), the adhesive sample being tested has adhered to the face of the test probe. From the start of the return of the probe to complete separation of the test sample from the face of the probe, the force on the probe and the corresponding displacement is recorded using a Voland Stevens LFRA Texture Analyzer and Recorder (Voland Corporation, Hawthorne, N.Y.). The area under the force-displacement curve is the adhesion energy. For the 1.0 inch diameter probe used, it is the adhesion energy per 5.07 cm.sup.2, which is the adhesion energy density (AED). For the work reported herein, the force was measured in grams and the displacement measured in centimeters so that all adhesion energy densities are reported in g-cm/cm.sup.2.

In this test, the hydrophilic gels of this invention display adhesion energy densities of about 5 to about 50 g-cm/cm.sup.2. The preferred gels give values of at least about 7 g/cm to about 40 g/cm in this test.

Because the PVP and/or viscosity-enhancer is crosslinked by high energy radiation, the hydrogels of the present invention are free of both residual monomers and chemical crosslinking agents, a very important consideration for devices which are to be affixed to the skin. If desired, and as mentioned previously, the gels optionally can contain preservatives, antifungal agents, a bacteriostat and the like, bearing in mind that unless special steps are taken to incorporate any such agents into the gel after it is formed, e.g., by application of a film of an aqueous solution thereof to one or both faces of the sheet of hydrophilic gel, the materials selected must be able to withstand the irradiation employed to produce the hydrophilic gel. Furthermore, the presence of these additives can change the radiation doses required to give a product with enhanced adhesion, yet non-aggressive, sufficient strength, but yet non-stringy.

Such additives may be included in formulations at levels of about 6% or less. The addition of these extra components usually requires a shift, upward in the radiation dose to reach the same level of desired crosslinking. However, shifts to lower levels are not necessarily precluded.

The physical properties of the hydrogels of Examples 1 through 4 (Section 5), according to their Adhesion Energies, Tack Rolling Ball Distances, Swell Ratios, and % Gels, are listed in Table I, below.

The electrode assemblies according to this invention are suitable for application to skin in connection with both electrical signal sensing medical electrical apparatus and electrical energy transmitting medical electrical apparatus, i.e., they can be used both as sensing electrodes and as working electrodes. Examples of "sensing" electrodes are those used in electrocardiogram (ECG), electrooculogram (EOG), electrogastrogram (EGG), surface electromyogram (EMG), electrodermal responses (EDR), electroensephalograms (EEG), visual evoked potential (VEP), and auditory evoked responses (AER). Moreover, because the hydrogels employed therein are biologically inert, the assemblies according to this invention are suited to the detection of signals requiring application to or implanted within sensitive areas of the body, such as the cornea in the electroretinograms (ERG), or in body cavities where the materials of conventional assemblies may prove unsatisfactory, such as in the summated electro-cochleograms (ECOG) electro-olfactorograms (EOGs) and measuring electrovaginal potentials (EVP).

Examples of "working" electrodes for which the electrode assemblies of this invention can be used are those adapted structurally for Transcutaneous Electrical Nerve Stimulation (TENS), use as a Electro-Surgical Unit (ESU), External Cardiac Pacing (ECP) and for Defibrillation (DEFIB).

The physical, electrical and chemical characteristics of these two general types of electrodes, plus three sub-catagories of the latter type, are set forth in Table II, below.

For a more extensive discussion of the preceding test methods please refer to U.S. Pat. Nos. 4,684,558 and 4,706,680 the complete disclosures of which are incorporated by reference herein.

Force-displacement profiles (FDPs), are generated as part of the adhesion energy density test previously described. The FDP traces are sensed by the Voland Stevens Texture Analyzer, and the signals processed, analyzed and then plotted by a Spectra-Physics SP4200/4270 computing integrator. The system is suitably calibrated at frequent intervals. The different FDP traces on various hydrogel sheets help provide a characteristic signature of the type of adhesive surface properties, or lack thereof, for each of these hydrogels.

The FDP traces coupled with their AED values help distinguish and differentiate the different classes of surface characteristics (i.e., pituitous, highly stringy, non-stringy or dead) for the various hydrogel sheets described in the present discussion.

The original PEO hydrogel sheet described in U.S. Pat. No. 3,419,006 gives a trace as depicted in FIG. 2 for a 4% PEO formulation cured at an irradiation dose of about 0.5 Mrad. If this formulation is irradiated to a higher value, the FDP becomes very small which describes "dead" or non-adhesive surface properties. This "dead" trace is depicted in FIG. 5. The surface properties claimed in U.S. Pat. Nos. 4,684,588, 4,706,680 and 4,777,954 are classified as highly adhesive, highly tacky and highly stringy. Typical traces of this kind of surface are shown in FIGS. 3A-3C. Such traces are characterized either by multiple plate features or broadened profiles and relatively high AED values. On the other hand, the distinguishing features of the non-stringy adhesive hydrogels that are the subject of this invention are depicted in FIGS. 4A and 4B. The figures show a very sharp single substantially featureless spike which gives an AED value of greater than about 5 g/cm but less than about 50 g/cm. The height (which is measured by peak-force, PF, in grams) of the spike of the non-stringy adhesive material has a PF value of at least about 180, preferably at least about 250 grams. Thus, by employing the testing method described in this section, the present adhesive non-stringy hydrogels can be characterized fully and readily distinguished from previously available adhesive materials or less desirable non-adhesive formulations. To appreciate more keenly the behavior of these various formulations under the FDP testing conditions, the reader is referred to FIG. 6 which shows, frame-by-frame, what takes place after the probe has come into contact with the gel surface and is withdrawn gradually.

The following is a summary of the properties of the hydrophilic gels of this invention.

The hydrophilic gel is inert and is not metabolized. It has a normal pH of about 7, which is allowed to "float" between 6 and 8. They have a zero irritation index. Because it is produced by irradiation, the gel has a very low bioburden.

The hydrogel contains no extraneous or other objectional ingredients. It does not contain extraneous chemicals such as monomers and cross-linking agents, which are present in chemically linked cross-linked gels, or solvents, etc., which are an integral part of formulated adhesives. All ingredients have a proven bioacceptability on contact with the skin. Normal exudants flow into the matrix of the gel away from the user's skin. Its hydrophilic properties eliminate the common requirement for abrasive treatment and/or other skin preparation.

The biocompatibility of the instant hydrogels are expected to be quite favorable because generally all the ingredients used to prepare the hydrogels are, themselves, highly biocompatible.

Experience has shown that specific ion control with even distribution within the conductive matrix is of paramount importance in electrode performance. The precise ion level and dispersion in the process employed to produce the hydrogel lends itself perfectly to the production of a unique family of controlled conductive-adhesive transmission components. Although the polymer matrix theoretically could hamper ion mobility, the volume resistivity of the hydrogel remains low.

The hydrogel contains no free water. The water in the hydrogel is an integral part of the gel structure and therefore cannot be separated therefrom by physical means such as pressure. Thus, the crosslinked matrix remains homogeneous under gravity and even at temperatures approaching freezing water. Its imbibing property enables the hydrogel to cleanse the body surface of water soluble exudates and secretions by drawing them up into the gel by osmosis, thus lowering the skin irritation factors commonly associated with other organic polymers. The gel pad has a distinct advantage of conforming itself to the irregularities of human skin, producing a substantially uniform contact. This characteristic is important because poor skin contact can cause electrical noise or current loss, which can change the accuracy of a biopotential recording or the efficacy of an electrical energy treatment. The high water content also precludes the necessity of preparatory skin shavings which many commercial electrodes require.

The hydrogels' non-stringy adhesive characteristics are manifested in its ability to conform to minute irregularities on the surface on which it is placed, yet sparing the user the objectionable sensation associated with handling an extremely sticky, stringy composition akin to freshly masticated chewing gum. While having these non-stringy properties, the present gels retain their cohesive properties. These characteristic meet the criteria of a non-stringy adhesive, without the necessity of additional chemicals. The degree of adhesion to a given surface is a function of the degree of irregularity or porosity of the surface. The hydrogels retain their adhesive quality even while absorbing normal perspiration. The viscoelastic properties of the hydrogel within the gel structure allows it to flow into the tiny interstices of the surface to which it is placed, thereby allowing intimate uniform contact between itself and that surface. This type of adhesiveness allows it to adhere to skin without employing additional chemical bonding agents, which permit the hydrogel to be removed from the skin without pain, skin damage or hair pulling and without leaving any residual components of the gel on the skin itself, as the components are permanently bound within the gel structure.

This non-stringy adhesive property has been achieved in a hydrogel sheet derived from an aqueous mixture of a water-soluble high molecular weight linear polymer. In particular, homogeneous mixtures of water and poly(ethylene oxide) or water, poly(vinyl pyrrolidone) and a viscosity-enhancing hydrophilic polymer may be exposed to a suitable does of radiation to provide solid sheets with the desired properties.

It has been surprisingly discovered, however, that hydrogels having the desirable electrical properties, discussed further below, having the adhesive properties described above, yet having the non-stringy properties also described herein, may be produced with the addition of viscosity-enhancing hydrophilic polymers of a sufficiently high weight average molecular weight. These benefits are achieved with very little amounts of viscosity enhancers, as little as about half to about one percent of the total mixture, and by careful exposure of the viscous mixture to the requisite amount of high energy radiation.

The starting materials used to produce the hydrogel can be formulated with a wide range of amounts and types of ionic materials to produce hydrogels having highly desirable electrical characteristics. The uniform distribution of selected ions results in correspondingly reproduceable electrical properties throughout the hydrogel, thereby lending itself to a wide variety of applications based on its conductive and capacitive properties. Furthermore, the predictable volume resistivity of the hydrogel lends itself to many critical medical applications.

Electrolytes that can be used in the hydrogel include most cations, e.g., ammonium, sodium, potassium, lithium, magnesium, calcium, etc., and both simple and complex anions, e.g., chloride, sulfate, carbonates, nitrates, and anions of organic acids, e.g., acetic, citric, adipic, tartaric, lactic, propionic, glutaric and maleic acids, the latter being preferred in electrodes where corrosion of the metallic connector may be a problem. Magnesium acetate is especially suitable in this respect. The volume resistivity remains constant throughout the gels intended use, allowing virtually zero decay in the conductance of the skin in medical applications, while allowing an upward even flow of skin excretions through the matrix away from the user. This change is uniform throughout the cross sectional area of the gel because of its balanced osmotic hydrophilic properties.

It is also important to note that the hydrogels of the present invention have impedance values at 60 Hz of less than about 1,000 ohms, indeed, as low as about 15 ohms, at 0.1 mAmp of current measured peak to peak, when said impedance is measured for a pair of 4 cm.times.4 cm square gel sheets in face to face intimate contact with each other and in which the exposed face of each sheet is electrically coupled to a 1 cm diameter silver/silver chloride disc centered on the exposed surface. Any variations in electrical properties between sheets of hydrogels will be small on an absolute basis for a given standard deviation of impedance values. Such uniformity is very important because one would want the electrical properties of an electrode to be substantially the same as other electrodes which may also be in use on the same subject.

The electrical properties of particular embodiments of the present invention are listed in Table III. these tests are enumerated in "Standard for Pregelled ECG-Disposable Electrodes," Association for the Advancement of Medical Instrumentation (AAMI), Arlington, Va. (1984). These impedance measurements can be measured at any suitable frequency, e.g., 10 Hz to 5 MHz, using the configurations described in the AAMI reference.

The basic sheet form of the hydrogel has both structural integrity along with resilient memory which permits it to return to and retain its original form when pressure is applied to the X-Y or Z axis. The product will withstand loss of water with a force of about 20 psi on a single surface, unlike other types of gels which exude water under the influence of gravity. Its high specific heat is another useful property. The hydrogel sheet is structurally unchanged and functional over a wide range of temperatures beyond its use range. The amount of energy required to raise the temperature of the sheet adds a safety margin in many medical applications. It can also be useful in some combination therapy applications involving heat/cold and electrical stimulation.

Because the hydrogel sheet or film is produced with high energy radiation, such as that produced by an electron accelerator, it can be sterile at a sufficient dosage.

Particular advantages realized with electrodes employing the hydrogel are its stable electrical properties, its excellent adhesion to the skin, and its substantially non-stringy texture. A superior medical electrode should not store electrical charge, should have a low solution potential with the skin, and should be of low impedance. The hydrogels employed in the electrodes of this invention have all of these characteristics. The electrodes also adhere firmly to the skin, ordinarily without the necessity of external adhesive support, depending upon the duration of the application. Also, the surfaces of the hydrogel which are exposed to air during use slowly form a dry crust over a period of time, thereby preventing the bulk of the hydrogel film from drying out and acquiring altered electrical conductivity properties. This property is particularly useful for long term applications.

The electrodes of this invention also exhibit further superior properties upon removal after use. Although the electrodes readily adhere to the skin, they can very easily be removed therefrom in a painless manner without damaging the skin, as do conventional commercial adhesive products. Moreover, upon removal, the electrode leaves no visible residue on the skin, as do many liquid gel-based electrodes. In fact, liquid gel electrode materials must be wiped off the skin in a relatively painstaking manner, frequently by application of soap and water. Because these hydrogels are substantially non-stringy, they are particulary more comfortable to use and are more acceptable to the patient. Also, during application, the hydrogel of the electrodes of this invention does not stain or stick to clothing. All of these advantages are accomplished employing ingredients which have an excellent history of biocompatibility so there is little likelihood of skin eruption or irritation.

Both sensing (detecting electrical signals on the skin) and working (transmitting electrical energy to the skin) electrodes according to this invention have numerous advantages over the prior art versions presently available commercially. Some of these are listed in Table IV below.

The following is a description of specific end use applications of the highly conductive hydrophilic non-stringy surfaced viscoelastic solid gels employed in the medical electrodes of this invention and the advantages associated therewith.

The TENS (Transcutaneous Electrical Nerve Stimulation) electrode coupling media is produced from low to medium ionic concentration, e.g., about 4 to 5 wt% of sodium chloride, hydrogel sheets. It is used as a disposable interface between a "standard" reuseable carbon electrode and the skin. The substance can also be used as an electrolyte in contact with its own carbon electrode material. The inert ingredients preclude skin irritation and the osmotic properties permits exudant to be carried away. The uniform ion control allows uniform current distribution and the hydrophilic properties prevents any air-gaps that can cause alternating current rectification. The excellent adhesive characteristics prevent accidental electrode detachment and the consistent electrical properties assures continuous effective treatment. The cohesive properties allows the hydrogel sheet to be cut to size and easily removed from the skin and electrode, offering true ease of use. This also holds true of the totally disposable product where ease of use and no clean-up are controlling factors. Finally the high specific heat and intimate contact becomes a deterrent to "hot spots" and any thermal burn potentials.

The ESU (Electro-Surgical Unit) electrode is produced from lower ionic hydrogel sheet, e.g., 6.7 wt% magnesium acetate. The dispersive radio frequency (grounding pad) return electrode application is a perfect conductive/adhesive application. The adhesive safety factor which prevents electrode removal and subsequent RF burns is of paramount importance. The precise ionic distribution and control prevents current pooling and small area thermal burns. The hydrophilic properties lessen interference from surgical fluids and assures close physical contact, thereby preventing muscle stimulation from rectified current. The high specific heat provides another safety factor in diminishing edge effect heating and electrolyte drying. In addition, the instant hydrogel is characterized as having an inherently uniform internal composition. As a result, the hydrogel is thermodynamically homogeneous and resists uneven gel or salt distribution during storage. Thus, electrodes manufactured from these hydrophilic gels do not suffer from gel or ingredient separation or gel migration, ensuring the presence of an adequate and uniform surface area for proper current dispersion from the body. The biological inertness of the hydrogel assures that local skin reactions, which could be confused with possible RF burn, will not be produced. The hydrogel's chemical inertness assures no ingredient breakdown via electrolysis and the hydrogel's excellent response to elevated temperatures also assures performance under adverse use conditions.

The PVP hydrogel-based EKG (electrocardiogram) electrodes have the widest variety of specific use applications, made possible by the ability to produce hydrogels of specific ionic strength. The ion concentration is chosen from a high, e.g., 7-8 wt% potassium chloride, percentage for high performance exercise use to low, e.g., 5-6 wt% potassium chloride, concentrations for long term applications. The ability to use ions that have previously been hard to control allows the production of a near perfect electrode on a consistent basis. The unique ability of the hydrogel to be compressed without any associated signal drift makes it ideal for clinical situations. The bound PVP matrix provides a stable signal sensing electrolyte for consistent recording, regardless of changing skin or temperature conditions. The excellent adhesive properties of the hydrogel provides added safeguards against "lead-loss" alarm conditions and the cohesive component provides the sought after ease of use quality. The excellent skin friendliness makes it a perfect choice for long term contact. The hydrophilic characteristics allows good conduction without the patient discomfort of skin abrasives or shaving. The ability of the gel to be reapplied to a different site during surgery is another advantage. Finally, the excellent response to extreme temperatures makes EKG electrodes based on the PVP hydrogels of this invention a good choice for emergency field applications.

The defibrillator pad is produced from a sheet of PVP/PEO/KCl hydrogel. The pad is usually used as a conductive media for the application of large amounts of electricity (voltage & current) and also used as a sensing electrolyte for EKG monitoring thru the same electrodes. The excellent electrical properties allows efficient delivery of the therapeutic charge of electricity without a loss of monitoring capability due to its low DC offset. The bound polymer matrix prevents the product from pooling during storage and the unique thermal properties of the gel makes it the perfect choice for field use of these devices. The adhesive component assures proper paddle contact without the fear of electrode solution running, which allows repeated repositioning or re-application of the paddles while maintaining effective skin contact. The hydrophilic properties of the gel sheet assure uniform skin contact without "pitting" and also eliminates the necessity of any skin preparation. The structural stability of the gel sheet allows greater user pressure upon paddle application without fear of pushing the gel away from the contact area. Finally, the clear glass-like property of the gel sheet allows full view of any trauma related injuries. The gel sheet's thermal sink properties and uniformity also minimizes skin burns associated with the defibrillation procedure.

The Bio-Feedback electrode is produced from a high concentration ionic gel sheet, e.g., 7-8 wt% KCl. Advantageous characteristics of the hydrogel sheet are its ability to firmly adhere to the patient's skin because of it adhesiveness and its ability to be re-positioned because of the cohesiveness. Its specific even ionic concentration allows it to be used with a wide variety of home and clinical electrodes, and permits immediate signal reception. The hydrophilic properties of the gel sheet allow many possible placement sites and repositioning without the need for any skin preparation. The bio-compatibility and skin friendliness makes long term use possible. The qualities of this product also find identical applications in the EEG, EMG, ENG and Evoked Potential fields. Specific electrical qualities necessary in all the above uses involve low noise potential and small DC offsets because of the low level signals involved. The gels bioinertness is especially important since these applications are frequently proximate to the eyes and mouth.

The variable electrolyte content of the present hydrogels makes them suitable conductive dressings for wounds. In particular, these conductive materials may be used in conjunction with electrical wound healing therapy in which beneficial effects have been observed from the application of electrical impulses to sores or wounds.

Two representative references by Alvarez et al. which describe the treatment of wounds through the application of external currents and the use of polymeric wound dressings, in general, are: J. Invest. Dermatol. 1983, 81(2), 144-148 and J. Am. Acad. Dermatol. 1985, 12 (Part 2), 409-419, respectively. The complete disclosures of these two references are incorporated herein by reference.

A liquid film (ca. 50 mil) of a mixture of 20 wt% poly(vinyl pyrrolidone) (approximate weight average molecular weight 1.times.10.sup.6), 1% poly(ethylene oxide) (M.sub.w 900,000), 5 wt% potassium chloride and about 0.3 wt% of selected biocides in water is cast (coated or extruded) onto a 1 mil film of polyethylene backing material. A polyethylene non-woven scrim (0.016 grams/inch.sup.2 area weight) is immersed into the viscous solution near its center. The scrim-containing solution is covered with a second sheet of 1 mil polyethylene film backing material, producing a sandwich 52 mil thick. This sandwich, held on a movable conventional conveyor belt, is then passed across the beam of a Van De Graaf generator, where it receives 1.34 Mrads of irradiation. The Van De Graaf generator is operated at a voltage of 1.5 MeV. The extrudable viscous aqueous mixture is thus converted to a sheet of a solid viscoelastic hydrogel. A one inch square sheet is cut from the sandwich and the backing materials on both sides of the sheet are removed. The sheet of scrim-containing solid hydrogel is affixed to the back side of a conductive silver/silver chloride snap, the front of which is embedded in a sheet of adhesive polyurethane foam with the top of the snap protruding therefrom. This configuration of conductive hydrogel, silver/silver chloride button and polyurethane foam, constitutes a test electrode unit. Two identical such electrode units are then joined together hydrogel back to hydrogel back to form an electrode pair. This electrode pair is then tested to determine its electrical responses for use as a medical electrode according to the standards for pregelled ECG disposable electrodes by The Association for the Advancement of Medical Instrumentation (Standard For Pregelled ECG Disposable Electrodes, Association for the Advancement of Medical Instrumentation, February 1984 Revision). The guideline values specified by The Association for such electrode pairs in the following electrical measurements are:

The values obtained for the electrode pair of Example 1 are listed in Table III.

The hydrogel of this example is similar to that of Example 1, except that it is exposed to a different dose of radiant energy (0.76 Mrad). Subsequent samples are irradiated at 1.04, 1.09, 1.54, 1.80, and 2.10 Mrad respectively. The physical properties are described in Table I, above.

The hydrogel of this example is similar to Example 1, except that the aqueous mixture is comprised of PVP (15 wt%), CMC (1.5 wt %), KCl (5 wt%), and biocides (<0.3 wt%). The extruded film is irradiated at a dose of 1.31 Mrad. It's physical and electrical properties are listed in Tables I and III, respectively.

The hydrogel of this example is similar to Example 3 except that the level of exposure to radiant energy is 1.0 Mrad. Subsequent samples are irradiated at 1.2 and 1.5 Mrad, respectively (See, Tables I and III).

The hydrogel of this example is similar to that of Example 1, except that 7% poly(ethylene oxide) of weight average molecular wt. 900,000 is used in place of the PVP and the 1% PEO, and it is exposed to an irradiation dose of 1.2 Mrads. The physical properties are described in Table 1 above.

Additional PEO formulations are prepared and exposed to a dose of radiation as enumerated in Table I. Thus, homogeneous mixtures of water and PEO in which the concentration of the linear polymer is 6, 9, 10.5 and 15 percent by weight of the total mixture, respectively, are irradiated as described above. Table I summarizes the physical properties of the respective formulations. The force-displacement profile of the formulation with a PEO concentration of 7 wt% is shown in FIG. 4.

Also, a typical breakdown of the biocide components may be as follows (in wt%): methylparaben (0.15), ethylparaben (0.05), propylparaben (0.02), butylparaben (0.05) and ucarcide (0.2).

The preceding examples can be repeated with similar success by substituting the generically or specifically described reactants and/or operating conditions of this invention for those used in the preceding examples.

From the foregoing description, one skilled in the art can easily ascertain the essential characteristics of this invention, and without departing from the spirit and scope thereof, can make various changes and modifications of the invention to adapt it to various usages and conditions.