SILVER-CONTAINING COMPOSITIONS, DEVICES AND METHODS FOR MAKING

Abstract: The present invention comprises methods and compositions for making a silver-containing antimicrobial hydrophilic material. More particularly, the present invention comprises methods and compositions for stabilized silver antimicrobial devices comprising a matrix comprising a polymer network and a non-gellable polysaccharide, and an active agent. The matrix may be formed into any desired shape for its desired uses.

Description: SILVER-CONTAINING COMPOSITIONS, DEVICES AND METHODS FOR MAKING Cross Reference to Related Applications This application claims the priority of U.S. Provisional Patent Application No. 60/157,000, filed October 1, 1999, U.S. Provisional Patent Application No. 60/212,455, filed June 19, 2000, and is a continuation-in-part of U.S. Patent Application No. 09/191,223 filed November 13, 1998, which is a continuation-in-part of U.S. Patent No. 5,928,174. Field of the Invention The present invention relates generally to antimicrobial devices and methods for making and using such devices and particularly to compositions and methods for delivering active agents to wounds. More particularly, the present invention relates to methods of making antimicrobial matrices for uses in many areas, including treatment of wounds. Background of the Invention The outer layer of skin surrounding the body performs an important protective function as a barrier against infection, and serves as a means of regulating the exchange of heat, fluid and gas between the body and external environment. When skin is removed or damaged by being abraded, bumed or lacerated, this protective function is diminished. Areas of damaged skin are conventionally protected by the application of a wound dressing which facilitates wound healing by acting as a skin substitute. Wounds to skin and the underlying tissues of humans and animals may be caused by external insult such as friction, abrasion, laceration, burning or chemical irritation. Damage to such tissues may also result from internal metabolic or physical dysfunction, including but not limited to bone protrudence, diabetes, circulatory insufficiencies, or inflammatory processes. Normally tissue damage initiates physiological processes of regeneration and repair In broad terms, this process is referred to as the wound healing process The wound healing process usually progresses through distinct stages leading to the eventual closure, and restoration of the natural function of the tissues Injury to the skin initiates an immediate vascular response characteπzed by a transient peπod of vasoconstπction, followed by a more prolonged peπod of vasodilation. Blood components infiltrate the wound site, endothehal cells are released, exposing fibπllar collagen, and platelets attach to exposed sites As platelets become activated, components are released which initiate events of the intπnsic coagulation pathway At the same time, a complex seπes of events tπgger the inflammatory pathways generating soluble mediators to direct subsequent stages of the healing process Normally, the wound healing process is uneventful and may occur regardless of any intervention, even in the case of acute or traumatic wounds However, where an underlying metabolic condition or perpetual insult such as pressure or infection are contπbuting factors, the natural wound healing process may be retarded or completely arrested, resulting in a chronic wound. Trends m modem medical practices have shown that the wound healing of both acute and chronic wounds may be significantly improved by clinical intervention using methods and mateπals that optimize wound conditions to support the physiological processes of the progressive stages of wound healing Key factors in providing the optimal conditions are the prevention of scab formation, prevention or control of microbial activity, and the maintenance of an optimal level of moisture in the wound bed It is also helpful to manage wound exudate fluid A common problem in the management of both acute and chronic wounds is the maintenance of an optimal level of moisture over the wound bed duπng heavy exudate drainage This is usually, but not always, an early stage of healing Most moist wound dressing technologies such as thin films, hydrocolloid dressings and hydrogels are typically overwhelmed by the accumulated exudate moisture duπng this heavy drainage phase Management of moisture duπng heavy exudate drainage often necessitates the use of gauze or sponge packings that wick away excess moisture from the wound bed, thin film coveπngs that trap exudate fluid over the wound bed, or calcium algmate dressings that chemically bind exudate moisture due to the hydroscopic properties of the seaweed extract Examples of wound dressings that have been developed include collagen dressings, a natural polymer. Soluble collagen has been used as a subcutaneous implant for repaiπng dermatological defects such as acne scars, glabellar furrows, excision scars and other soft tissue defects Collagen has also been used in many forms as wound dressings such as collagen sponges Several inventions have attempted to solve the problem of maintenance of an optimal level of moisture in the wound environment. Collagen is used as the matπx mateπal in Artandi. U S. Patent No. 3,157,524 and Berg et al, U.S Patent No 4,320,201. However, most of these dressings are not satisfactory for the vaπous types of full thickness wounds Collagen films and sponges do not readily conform to vaπed wound shapes. Furthermore, some collagen wound dressings have poor fluid absorption properties and undesirably enhance the pooling of wound fluids Generally, most wound dressing mateπals do not provide for the control or elimination of microbial bioburden in the wounds. Another example of wound dressings that have been developed for control of moisture levels in wounds are the hydrocolloid dressings United Kingdom Patent Number 1,471,013 and Catania et al, U.S. Patent No 3,969,498 descπbe hydrocolloid dressings that are plasma soluble, form an artificial eschar with the moist elements at the wound site, and gradually dissolve to release medicaments These dressings compπse a hydrophilic foam of dextran polymer that can be applied without therapeutic agents or ointments, are non-irπtating to the lesion and can be easily removed Known hydrocolloid dressings in general, and the Catania et al. dressings in particular, are subject to a number of drawbacks The major disadvantages of these dressings include the potential to disintegrate in the presence of excess fluid at the wound site, and minimal, virtually negligible, control over water loss from the wound This latter disadvantage is particularly important, as excess water loss from a wound will cause an increase m heat loss from the body as a whole, potentially leading to hypermetabohsm In addition, hydrocolloid dressings require frequent dressing changes. This is especially true of the Catania et al. dressing due to the dissolution of the dextran polymer at the wound site caused by the fluid loss through the wound in the exudative stage Although currently available dressing mateπals possess features that contπbute to the control of heavy exudate drainage, most also possess significant limitations that retard the overall healing process For example, thin film dressings such as those descπbed in U.S. Patent No. 3,645,835, maintain excessive moisture over the wound bed, contπbutmg to the overhydraUon or maceration of surrounding skin. Although sponges and gauze support ϋssue, they require frequent changing, and cause irritation to the wound bed duπng body movement and dressing removal. These dressings may be permeable to moisture but not to microorganisms Although these devices and others administer some control over wound exudate moisture and may additionally provide a barπer to microbial contamination, they do not actively participate in controlling the growth of microorganisms or in the elimination of microbial bioburden from the wound dressing Calcium alginates turn into a gelatinous mass duπng mteracuon with moisture, are difficult to remove completely, and often dehydrate the wound bed due to the hydroscopic nature of the matπx Importantly, none of the presently available devices significantly contπbute to or support the autolytic debndement phase, which is the natural removal process of necrotic tissue and debπs from the wound Autolytic debndement is a key early stage event that precedes repair phases of healing When wound conditions are not optimal for supporting autolytic debndement, then clinical procedures such as surgical removal, lrπgation, scrubbing, and enzymatic or chemical methods must be used to remove the necrotic tissue and escar that can inhibit wound healing Temporary or permanent wound dressings that are designed to enhance wound healing are needed to cover large open wounds on patients with extensive burns, lacerations and skm damage Furthermore the ability to produce wound dressings in a vaπety of shapes to accommodate multiple sizes and forms of injuπes is important in the manufacture of useful medical products In addition, there continues to be a need for a wound dressing that possesses high moisture absorption capacity, a high rate of absorption, as well as a capacity to regulate moisture at the wound bed-dressing interface Desirably, such a wound dressing device should stimulate the autolytic debndement process, especially duπng the heavy exudating phase of wound care management Another desirable aspect of a wound dressing would be the ability to deliver active agents to the site of injury to accelerate wound healing and in particular to control the growth and damage caused by microbial contaminants of the wound. Active agents for use in wound treatment may be administered to an individual in a vaπety of ways For example, active agents may be administered topically, subingually, orally, or by injection (subcutaneous, intramuscular or intravenous) Nevertheless, there are drawbacks to many of these methods, and an inexpensive, reliable, localized and relatively pain-free method of administeπng an active agent has not been provided in the pπor art One common method employed for the treatment of wounds is the topical application of a salve or ointment. Yet many times, topical application to a wound can be painful and short-lived. Addiuonally, m the case of a deeply cavitated wound m particular, an excess of active agent may be required because the agent must diffuse through layers of necrotic tissue and newly forming '/ epidermal tissues This difficulty in dehveπng the agent may require the application of an excessive amount of the agent and preclude an accurate determination of the effective amount of active agent to be added The oral and subhngual administrations of active agents used in wound treatment also have their drawbacks Most importantly, the administration site, the mouth, is normally far removed from the actual location of the wound Ingestion of an active agent at a site distant from the wound may result in the agent having negative system-wide effects and possibly knocking out the normal flora, or normal microbial environment, whose presence benefits an individual Successful absorption of the agent into the bloodstream also depends on several factors such as the agent's stability in gastrointestinal fluids, the pH of the gastrointestinal tract, solubility of solid agents, intestinal motihty, and gastiic emptying Injection of an active agent, a normally painful method of administration, may have the same negative system-wide effects as that of an oral or subhngual administration if injection is at a site distant from the wound Yet more importantly, a danger inherent in the injection of an active agent is that rapid removal of the agent is impossible once it is administered. There is also a πsk of transmission of infections and the possibility of vascular injury due to the use of needles One active agent, silver, has long been recognized for its broad spectrum anti-microbial activity and compatibility with mammalian tissues Although silver has been used m a large range of medical devices, its incorporation, as a prophylactic anti-infective agent, in pπmary wound contact products has been restπcted due to silver's adverse properties These properties include a short half-life, the rapid inactivation of silver by protein, and light-mediated discoloration of the product containing silver and any body parts touching the product, such as sk Recently, manufacturers have tπed methods to overcome some of the limitations to broaden the utility of silver m wound care The cunently available silver-containing wound care dressing matenals have been unsuccessful in adequately overcoming the problems inherent in using silver. Medical devices that are implanted or those that are attached to epitheka may create an environment conducive to the multiplication and growth of microorganisms This microbial growth may lead to complications such as local or systemic infection Dermal wounds are at particular πsk since microbial contaminants are commonly present, and the wound produces optimal nutπents and other environmental conditions for microbial growth Medical practices have demanded the use of steπle or low bioburden devices and the adoption of procedures and adjuncts such as frequent dressing changes, use of topical antimicrobial compounds, and systemic antibiotics to control growth of microorganisms on and around the device duπng use. An alternative approach is the production of devices that possess broad spectrum antimicrobial activity. A vaπety of approaches have been taken to endow devices with antimicrobial properties including soaking of indwelling catheters and other devices in antibiotics such as penicillin or fluconazole, or in antiseptic solutions such as chlorhexidme or sulfadiazme Although these approaches render some antimicrobial activity to the devices, they are of limited utility due to toxicity, stability and effectiveness. Such limitations include short half-lives m tissue or on the devices, the agents' spectrums of activity are too narrow for the range of organisms that may be encountered near the device, or the agents may be destructive to tissues at their effective concentrations. Heavy metals may provide an optimal alternative as antimicrobial agents for rendeπng medical devices with antimicrobial properties. Heavy metals may exist as salts, complexes with earners, as base metals or other forms. This versatility contributes to the vanety of ways in which the forms can be coupled with the devices. In addition, it is known that heavy metals such as gold, platinum, silver, zinc and copper exert antimicrobial activity at very low concentrations against a broad spectrum of organisms including bacteπa, protozoa, fungi and viruses (N. Gπer, "Silver and its compounds" In Disinfection, Steπ zation, and Preservation, (3 rd edition S. S Block, ed., Lea & Febiger, Philadelphia, Ch. 20, (1983).) Silver is oligodynamic, meaning that it has antimicrobial activity at very low concentrations against a wide range of bactena, fungi and viruses Measurements of ionic silver as low as 10 6 to 10 9 M have been shown to be antimicrobial (A.D. Russel and W.B. Hugo, "Antimicrobial Activity and Action of Silver", Prog, in Med. Chem. 31:351- 370, 1994.) Moreover silver is well tolerated by mammalian cells and tissues. One active heavy metal, in particular silver, has long been recognized for its broad spectrum anti-microbial activity and compatibility with mammalian tissues. Although silver has been used m a large range of medical devices, its incorporation, as a prophylactic anti-infective agent, m pnmary wound contact products has been restricted due to silver's adverse properties. These properties include a short half-life, the rapid inactivation of silver by protein, and light-mediated discoloration of the product containing silver and any body parts touching the product, such as sk . Recently, manufacturers have tned methods to overcome some of the limitations to broaden the utility of silver in wound care. The currently available silver-containing wound care dressing mateπals have been unsuccessful in adequately overcoming the problems inherent in usms silver. The mode of action of silver is due to the reactivity of the ionic form with a vanety of electron donating functional groups that contain reactive entities such as oxygen, sulfur or nitrogen Electron donating functional groups in biological systems are many and vaπed, including groups such as phosphates, hydroxyl, carboxylates, thiol, lmidizoles, amines, and mdoles Microbial macromolecules are πchly endowed with these functional groups that, when bound by silver ion, may become inactivated and disfunctional resulting m the death of the microorganism Ionic silver is known to disrupt microbial cell wall, cell membrane, electron transport, metabolic and anabolic enzymes, and nucleic acid function (A D Russel, W B Hugo, "Antimicrobial activity and action of silver" In Progress in Medicinal Chemistry Vol 3, G P Ellis & D K Luscombe, ed , Elsevier Science B V , (1994)) Ohgodynamic silver has been incorporated into medical inventions for the purpose of imparting an antimicrobial effect The use of metallic silver was reported in UK patent application No 2134791 A which descπbes the vapor deposition of metallic silver or silver/carbon on Sphagnum moss for the purpose of making an antimicrobial surgical dressing US Patent No 5,753,251 descπbes the production of a wound contact product by sputter coating silver on to substrates such as plastic films to impart antimicrobial activity to the device A descπption of a metallized bandaging matenal, prepared by vapor coating metallic silver onto a fiber fleece was descnbed in US Patent No 2,934,066 US Patent No 4,483,688 descπbes the combining of finely ground metallic silver with a binding agent for coating indwelling catheters Alternative means of incorporating silver or silver salts into or on devices have also been descπbed The incorporation of antimicrobial silver into the adhesive of an adhesive coated, moisture impermeable thin film polymer for use for secuπng medical devices or as a wound dressing was descπbed in US Patent No 4,340,043 The use of silver oxide, finely ground into small particles, dispersed in latex batching has been descπbed in US Patent No 4,902,503 for use in making indwelling medical devices where antimicrobial activity would increase effectiveness Although these devices have provided certain solutions to combining antimicrobial activity with medical devices, these inventions have identified a number of limitations associated with silver and silver salts The highly reactive nature of silver ions contnbutes to the relatively short half-hfe of the antimicrobial effect in the presence of certain functional groups Moreover its antimicrobial form, ionic silver, is unstable in light and is rapidly converted to a black inactive precipitate by photo-reduction Attempts at overcoming the limitations of silver addition included applying silver or silver salts onto dry substrates where little or no lonization of silver could occur or the use of substrates containing few reactive functional groups that would react with ionic silver However, this is impractical for applications where moisture abounds such as in moist devices such as soft contact lenses, hydrated plastic implants, or m moist wound dressing cover such as a hydrogels, hydrocolloids, or biologies, or in medical devices that contain reactive functional groups such as in a collagen matπx To overcome these problems, inventions descnbmg stabilization of silver have been descnbed U.S. Patent No. 5,863,548 descπbes the process of forming a complex between silver and allantom which in turn is encapsulated in allantom to form a light stable antimicrobial coating for medical devices US Patent No. 5,709,870 descπbes a process for producing a light and heat stable silver complex with carboxymethyl cellulose for use in coating fibers Similarly US Patent No. 5,744,151 descπbes a process for rendeπng silver photo- stable and antimicrobial for use as an adjunct to pharmaceuticals by forming an acyclic polyether polymer stabilized by ratios of cation and anions in the process The stabilization of the antimicrobial effect of silver in a device that is exposed to light or is m contact with functionally reactive groups may also be accomplished by retarding the release of the silver ion into the environment around the device after application In other words by using mechanisms that continuously release a small steady supply of ionic silver into the device An invention descπbed in US Patent No. 5,470,585 incorporates silver into a form of glass that slowly dissolves m the presence of moisture The slow dissolution of the matπx thereby releases ionic silver about the device Sputter coated nanocrystallme silver coatings on devices such as plastics for wound care initially are similarly slowly released from the device duπng contact with moisture of tissues to liberate ionic silver around the device duπng use as is descπbed in US Patent No. 5,753,251. These inventions have provided some solutions to the problems of stability, and half-life for silver for several silver antimicrobial applications. However they are cumbersome, may contain toxic accessory agents that support function, or are prohibitively expensive for application to commodity medical devι_ a such as wound dressings. Moreover, these approaches are not solutions to the incorporation of antimicrobial silver into devices that contain solvents where lonization of the silver would normally occur in wound dressings such as hydrogels, moist contact lenses, oral prosthetics and other devices containing water. In addition, these inventions make only marginal contπbution to the sustained continuous release of ionic silver from devices treated by the processes 2 descπbed What is needed are compositions and methods for providing antimicrobial activity in medical devices, and particularly for silver incorporation into medical devices such as moisture-containing wound dressings, skin contact devices, such as monitor leads, wound dressings and hydrated plastic implants. Summary of the Invention The present invention compπses compositions and methods for producing mateπals that contain stabilized antimicrobial metals, preferably silver, for many uses, including medical products. In particular, the present invention provides methods and compositions for administenng active agents, such as antimicrobial silver, to the site of a wound via wound dressings The present invention also allows for localized delivery of active agents and prevents the negative effects of system-wide administration. The present invention compπses wound healing devices that have specialized structures that aid in treatment of wounds A preferred embodiment of the present invention compπses a hydratable matnx matenal that has an antimicrobial agent, such as a heavy metal, most preferably, silver, incorporated into the matπx The matπx preferably also compπses components that stabilize and control the release of the active agent into the surrounding environment when used. In a prefeπed embodiment of the present invention, active agents are incorporated directly, or may be incorporated by sequentially adding components or precursors of the active agent to the matπx of the devices, and having the precursors form the active form of the active agent in or on the matπx The agents may be incorporated by absorption or adsorption of agents or precursors by the matπx, and preferably by incorporation duπng the polymeπzation of the matπx It is theoπzed that the release of the active agents may be controlled via manipulation of concentration parameters, movement of water through the matπx and the degree of cross-lmking m the matπx. In another preferred embodiment, the wound dressings compπse a stranded configuration, wherein the strands extend from at least one common region and the strands themselves compnse a polymer matnx. The wound dressing devices of the present invention may be used to simultaneously deliver a number of active agents to a wound site. Wound healing agents such as antimicrobial agents, antifungal agents, antiviral agents, growth factors, angiogemc factors, anaesthetics, mucopolysacchaπdes and other wound healing proteins may be incorporated into the wound dressings for controlled release Adjuvants and other agents, such as those that boost the immune system, may also be incorporated into the wound dressings devices of the present invention. A surpπsing and novel aspect of a prefened embodiment having agents directly incorporated into micro-cavities of the matπx is that the activities of the wound healing agents are not altered by incorporation into the devices and that the agents are effective upon their release In a preferred embodiment of the present invention, the wound dressing devices of the present invention compπse a novel stranded structure made from a matπx suitable for application to broken skm and underlying tissues. The individual strands of the preferred embodiment may or may not have free floating ends, however, the unique anangement of the device allows it to both absorb excess wound exudate, and simultaneously conform closely to the walls of the wound bed, in order to accelerate overall wound healing. A stranded configuration of the wound dressings of the present invention is particularly desirable because the novel design provides a high surface area to volume ratio to maximize interchange between the matπx and wound moisture and wound debπs. The multiple strands of the preferred configuration provide maximal mter-strand space to serve as a reservoir for moisture, necrotic mateπals, or agents scheduled for delivery to the wound bed. The supeπor moisture absorption and regulation capacity of the preferred embodiment equip the wound dressing devices for use on heavily to moderately draining wounds. In addition to increased moisture absorption and the ability to deliver active agents, the individual strands of the preferred configuration may participate in mechanical debndement thereby accelerating the wound healing process. The individual strands of the preferred wound dressings increase the inherent flexibility of the device, and enhance conformability to the lrregulaπties of the contours in the wound cavity, allowing the preferred devices to be used in deeply cavitated wounds where debndement is essential. In order to simplify the overall wound dressing procedure, the preferred devices may have a single unit construction that is applied and removed as a complete unit, leaving no remnants. Additionally, the preferred devices may be left m place for prolonged peπods between changes Other forms of the matπces of the present invention, such as molded articles, are also contemplated by the present invention. Other forms also include films, sheets, fibers and amorphous gels. The matnces of the present invention can be dipped or applied m methods known to those skilled m the art to articles or devices. A preferred embodiment of the present invention compπses methods and devices that incorporate antimicrobial agents, more preferably, the agents are heavy metals, and most preferably, the agents are silver compositions. The silver-containing devices have antimicrobial activity, are resistant to light degradation, possess sustained release characteπ sties, and provide improved wound healing ability Methods of the present invention compπse methods for making the antimicrobial devices, such as wound dressings, and methods of use of such devices Another preferred embodiment of the present invention compπses devices and methods for making and using such devices that compnse mateπals that allow for the application and stabilization of antimicrobial metals such as silver Preferred embodiments compnse devices made with or associated with hydrophilic pre-formed fibrous mateπals A prefened use is for use in medical and non-medical devices and mateπals for the purpose of imparting sustained, light stable antimicrobial activity to the device In particular, the present invention relates to compositions and methods for the incorporation and stabilization of silver onto and within the hydrophilic fibers of cross-linked and non-cross-hnked celluloses such as carboxymethy cellulose and hydroxymethyl cellulose, cotton, rayon, and of fibers made from polyacrylates and other synthetic and natural polymers, and fibers of calcium algmates that may be used as a pnmary contact sustained-release silver antimicrobial mateπals Additionally, the methods of incorporating stabilized heavy metals, particularly silver, into matenals can be used for a wide vaπety of products For examples, such methods include adding antimicrobial characteπstics to cosmetic products, such as dressings, topical lotions, or compresses for acne and blemishes, scar reduction, tattoo removal, and laser resurfacing, any body- or skin- contacting medical devices, such as, catheter coatings, guidewire coatings, ostomy appliances, respiratory and feeding appliances, contact lenses, and heanng aids, and personal and skin care products, such as skin conditioners, barπer creams, lubncating preparations, and super absorbents for addition to diapers, adult incontinence products, and feminine hygiene products Accordingly, it is an object of the present invention to provide compositions and methods for the treatment of wounds Another object of the present invention is to provide compositions and methods that facilitate and accelerate the wound healing process Yet another object of the present invention is to provide a wound dressing device wherein active agents are incorporated It is another object of the present invention to provide wound dressing devices that absorb excess moisture at a wound site It is another object of the present invention to provide wound dressing devices that promote autolytic debndement // Yet another object of the present invention is to provide a wound dressing device that absorbs wound exudate by allowing for optimal contact between the device and the wound area. A further object of the present invention is to provide wound dressing devices for external and internal wounds Another object of the present invention is to prevent infection by providing wound dressing devices that clean wound sites by removing debπs and contaminating matenal. It is another object of the present invention to provide wound dressing devices that easily conform to the shape of a wound It is yet another object of the present invention to provide wound dressing devices that are easily manufactured. Still another object of the present invention is to provide wound dressing devices that may be easily removed from wounds and replaced. Yet another object of the present invention is to provide wound dressing devices that are compatible with injured tissue and do not induce imtation or inflammation. It is yet another object of the present invention to provide wound dressing devices that function to both absorb wound exudate and promote autolytic debndement. Another object of the present invention is to provide methods and compositions for making single unit construction wound dressing devices having multiple strands. It is another object of the present invention to provide methods and compositions for treating wounds using wound dressing devices that function to both absorb wound exudate and deliver wound healing agents. An object of the present invention to provide methods and compositions for treating wounds using wound dressing devices having active agents incorporated therein. Still another object of the present invention is to provide methods and compositions for dehvenng active agents to wound sites and damaged tissue An object of the present invention compπses methods and compositions for providing devices with antimicrobial activity. Another object of the present invention compnses methods and compositions for providing moisture-containing devices with antimicrobial activity. Still a further object of the present invention compπses methods and compositions for providing devices that are essentially dry with antimicrobial activity. -. These and other objects, features and advantages of the present invention will become apparent after a review of the following detailed descπption of the disclosed embodiments and the appended claims Brief Description of the Figures Figure 1 is a three dimensional view of one embodiment of a wound dressing device of the present invention wherein the multi-stranded device may have free floating strand ends Figure 2 presents a cross-section of a strand of the multi-strand device Figure 3 is an illustration of a pattern of a die used for cutting a device from an appropπate matπx mateπal Figures 4-7 illustrate additional embodiments of a wound dressing device Figure 8 shows a graph of the sustained release activity of a silver- containing matπx wound dressing Figure 9 shows a graph of the results of tests for cytotoxicity Figure 10 shows graphs of the absorbency and moisture-donating ability of a preferred embodiment of the present invention Figure 11 shows the effect of a silver-containing device on the viability of an E coli culture Figure 12 is a graph showing the effect on the bioburden when using a silver-containing device Detailed Description The present invention compπses compositions and methods for making and using mateπals compns g antimicrobial activity Such mateπals may be hydrophilhc moist mateπals or dry mateπals In particular, the present invention compπses compositions and methods for making and using such mateπals, for example for treating wounds using wound dressing devices with active agents incorporated therein A preferred active agent is silver that is incorporated into the matenals and is stabilized until released by application or placement in the site of use In a preferred embodiment, the active agents may be directly incorporated into the scaffolding matπx of the devices for controlled release at the site of the wound In a further prefened embodiment, the matπx compπses a biocompatible, scaffolding polymer network, such as a polyacrylate hydrophilhc polymer, with a non-gellable polysacchaπde dispersed evenly throughout said network Most preferably, the matπx has antimicrobial activity associated with it The matπces of this preferred embodiment provide a reliable a and efficient means for dehvenng active agents to the site while at the same time may also provide a supenor moisture regulation capacity which is important for promoting wound healing The wound dressing devices of the present invention are preferably in the form of a continuous sheet form, similar to wound dressings known in the art However the invention may also take other particular conformations For example, a preferred embodiment of the present invention compnses a stranded configuration wherein the individual strands extend from at least one common region and may have free-floating ends This particular conformation is particularly suitable for use m deeply cavitated wounds since the multiple matπx strands enable the dressing to conform to individual and uniquely shaped wound areas Furthermore, the devices accelerate wound healing by displacing and allowing for the removal of excess cellular exudate and debπs, thereby improving the rate of tissue repair and regeneration The terms 'a", "an" and "the" as used herein are defined to mean one or more and include the plural unless the context is mappropπate Active agents The active agents incorporated into the matπces and devices of the present invention may be used for a vaπety of applications where there is a need for the presence of the active agent A particularly preferred use is in the treatment of wounds or m sk healing The active agents may participate in, and improve, the wound healing process, and may include antimicrobial agents, including but not limited to antifungal agents, antibactenal agents, anti-viral agents and antiparasitic agents, growth factors, angiogenic factors, anaesthetics, mucopolysacchaπdes, metals and other wound healing agents Examples of antimicrobial agents that can be used m the present invention include, but are not limited to, isoniazid, ethambutol, pyrazinamide, streptomycin, clofazimine, nfabutin, fluoroquinolones, ofloxacm, sparfloxacin, nfampm, azithromycin, claπthromycin, dapsone, tetracychne, erythromycm, ciprofloxacin, doxycychne, ampicillin, amphoteπcm B, ketoconazole, fluconazole, pynmethamine. sulfadiazine, chndamycin, lincomycm, pentarmdine, atovaquone, paromomycin, diclazaπl, acyclovir, tπfluoroundine, foscarnet, penicillin, gentamic , ganciclovir, latroconazole, miconazole, Zn-pynthione, heavy metals including, but not limited to, gold, platinum, silver, zinc and copper, and their combined forms including, salts, such as chlonde, bromide, iodide and peπodate, and complexes with earners, and other forms Growth factor agents that may be incorporated into the wound dressing devices of the present invention include, but are not limited to, basic fibroblast growth factor (bFGF), acidic fibroblast growth factor (aFGF), nerve *1 growth factor (NGF), epidermal growth factor (EGF), insulin-like growth factors 1 and 2, (IGF-1 and IGF-2), platelet denved growth factor (PDGF), tumor angiogenesis factor (TAF), vascular endothe al growth factor (NEGF), corticotrop releasing factor (CRF), transforming growth factors cc and β (TGF-α and TGF-β), ιnterleukm-8 (IL-8), granulocyte-macrophage colony stimulating factor (GM-CSF); the interleukins, and the interferons. Other agents that may be incorporated into the wound dressing devices of the present invention are acid mucopolysacchaπdes including, but are not limited to, hepaπn, hepaπn sulfate, hepannoids, dermatan sulfate, pentosan polysulfate, chondroitin sulfate, hyaluromc acid, cellulose, agarose, chitin, dextran, carrageenin, hnoleic acid, and allantom. Proteins that may be especially useful in the treatment of wounds include, but are not limited to, collagen, cross-linked collagen, fibronectin, laminm, elastin, and cross-linked elastin or combinations and fragments thereof Adjuvants, or compositions that boost an immune response, may also be used in conjunction with the wound dressing devices of the present invention. Antibodies or antibody fragments are also included. It is to be understood that in a prefened embodiment of the present invention, the active agent, more preferably heavy meatls, most preferably silver, is incorporated into the matπces or devices so that the agent is released directly from the devices and delivered to the contact substrate such as the wound site or application site. The incorporated agents may be released over a peπod of time, and in this way, the devices retain their ability to kill or inhibit microorganisms over an extended peπod of time. As used herein, the term silver includes all silver salts or silver compounds, including, but not limited to, silver chloπde. silver phosphate, silver sulfate, silver iodide or silver bromide. The active form of the silver salt is the silver ion, as is the case for the active forms of the heavy metals. Administenng active agent for the prevention or control of local infection using the wound dressing itself overcomes several of the problems of the pπor art. First, the present invention avoids the painful re-application of salves and ointments to the wound. The present invention also allows silver to be delivered directly into the site of the wound to prevent the negative impact of system wide delivery of the agents as encountered after oral or intravenous administration. In the case of deeply cavitated wounds, m contrast to the topical application of active agents, the wound dressing and silver therein may be located directly within the wound, providing a more effective delivery of the agents. Finally, in contrast to an injection of active agents, the present invention provides methods of administenng active agents wherein the agents may be removed immediately from the wound and the administration terminated. Matπces The devices of the present invention compπse a hydrophilic matnx mateπal, preferably, one that is flexible and elastic, and is of a semi-solid scaffold that is permeable to substances such as inorganic salts, aqueous fluids and dissolved gaseous agents including oxygen The substances permeate the matnx through movement via intermolecular spaces among the cross-lmked polymer The matnx may be moist or dry Preferably, the hydrophilic matnx mateπal is constructed from a natural or synthetic polymer and a non-gellable polysacchaπde Natural hydrophilic polymers that may be used for the construction of the wound device include, but are not limited to collagen, animal hide, hyaluronic acid, dextran and alginate Additionally included are hydrophilic fibers of cross-linked and non-cross- hnked celluloses such as carboxymethy cellulose and hydroxymethyl cellulose. cotton, rayon, and of fibers made from polyacrylates, and fibers of calcium algmates that may be used as a pnmary contact sustained release silver antimicrobial mateπal Synthetic polymers that may be used include, but are not limited to polyacrylamide, polyv yl s (PVP, and PVC), polyacrylate, polybuterate, polyurethane foam, si cone elastomer, rubber, nylon, vinyl or cross linked dextran If cross-lmked dextran is used, it is preferred that the molecular weight of the dextran polymer is between 50,000 and 500,000 The most preferable non-gellable polysacchaπde is a non-gellable galactomannan macromolecule such a guar gum A range of guar gum between approximately 001 kg to 100 kg, preferably between approximately 0 1 kg to 10 kg, and most preferably between approximately 0 5 kg to 2 kg is generally sufficient Other non-gellable polysacchaπdes may include lucerne, fenugreek, honey locust bean gum, white clover bean gum and carob locust bean gum To decrease the permeability of wound dressing devices compπsing a cross-linked polymer and non-gellable polysacchaπde matnx, water loss control agents may be applied to the surface of the device Application of water loss control agents is prefened since a decrease in the permeability of the device controls the loss of fluids from the wound The preferred water loss control agent is petrolatum, however, other water loss control agents such as glycohpids, ceramides, free fatty acids, cholesterol, tnglyceπdes, sterylesters, cholesteryl sulfate, knoleic ethyl ester and sihcone oil may also be used If desired, a plasticizer may also be added to the matπx matenal A preferred plasticizer is glycerol and water, however, propylene glycol and butanol may also be used If glycerol is used, a range of between approximately 0 5 kg to 50 kg, preferably between 1 kg and 30 kg, and most preferably between approximately 5 kg to 15 kg is generally sufficient. The plasticizer may be added in the initial mixture of polymer and cross-linking agent. If desired, a hydration control agent may be incorporated into the matrix. The prefened hydration control agent is an isopropyl alcohol, however, ethanol, glycerol, butanol, and propylene glycol may also be used A range of isopropyl alcohol of between approximately 0.1 kg to 10 kg, preferably between approximately 0.2 kg to 5 kg and most preferably between approximately 0.5 kg to 2 kg is generally sufficient. The matnx of the preferred embodiment preferably compπses polymeπzed chains of acrylamide monomer, wherein the acrylamide monomers are cross-linked with a cross-linking agent, a non-gellable polysacchaπde, and an active agent or pharmaceutical directly encapsulated into micro-cavities therein. A range of acrylamide between approximately 1 kg to 100 kg, preferably between approximately 2 to 50 kg, and most preferably between approximately 5 kg to 20 kg is generally sufficient A preferred matπx compnses a cross-lmked polyacrylamide scaffolding that enmeshes guar gum as disclosed in U.S. Patent No. 5,196,160 to Nangia. The most preferable cross-linking agent is NNNN'- methylenebisacrylamide, however other appropπate cross-linking agents such as bisacrylylycystam e and diallyltartar diamide may also be used. If NNNN'- methylenebisacrylamide is used, a range of between approximately 0 01 kg to 1 kg, preferably between approximately 0.02 kg to 0.5 kg, and most preferably between approximately 0 05 kg to 0.3 kg is generally sufficient. As noted above, the most preferable non-gellable polysacchaπde is a non-gellable galactomannan macromolecule such a guar gum, but other non-gellable polysacchaπdes may include lucerne, fenugreek, honey locust bean gum, white clover bean gum and carob locust bean gum. Ammonium persulfate and TEMED may also be added to the matnx. A range of ammonium persulfate between approximately 0.01 kg to 1 kg, preferably between approximately 0.02 kg to 0.5 kg, and most preferably between approximately 0.05 kg to 0.2 kg is generally sufficient. Additionally, a range of TEMED between approximately 0.01 kg to 1 kg, preferably between approximately 0.02 kg and 0.5 kg, and most preferably between approximately 0.05 kg to 0.3 kg is generally sufficient. Incorporation of active agents One embodiment of the matπces of the present invention can be found in U.S. Patent No. 5,196,190 to Nangia et al, which is hereby incorporated in its entirety. Nangia et al. teach a matπx composed of a natural or synthetic polymer, a non-gellable polysacchaπde, and a phospholipid-based drug delivery < ■ } system. In particular, Nangia et al. teach a matπx capable of drug delivery, wherein hpid vesicle hposomes containing a desired drug are incorporated into the matπx. One problem with the pπor art methods, however, is the difficulty of incorporating active agents into the hposomes since some agents may be incompatible with hposome chemistry. Incorporation using hposomes is time consuming, expensive and sometimes unreliable because dispersion of the hposomes in the matnx is difficult to achieve and once achieved, the hposomes may prematurely release costly agents due the hposomes' inherent instability. Another problem is that the pnor art fails to teach a method of incorporating active agents into a wound dressing wherein the release of the agent over time can be controlled through the manipulation of concentration parameters, movement of water through the matπx and the degree of cross linking in the matπx Preferred embodiments of the present invention however, address the need for a less expensive, quicker, and more rebable method for incorporating a wider range of desired agents into matπces and devices Prefened embodiments also provide a means to control the release of the desired agents over time via manipulation of concentration parameters, movement of water through the matnx and the degree of cross-linking the matnx In a prefened embodiment, the desired agents may be directly incorporated into the matπx by adding the agents into the initial formulation for the matnx pπor to cross-linking. This method of incorporation is inexpensive, rapid and reliable, and most surpnsmgly, the incorporated agents are not affected by the process of polymeπzation and retain their biological activities. Another preferred method of incorporation is the adsorption or absorption of solutions containing the active agents or precursors of the active agent to an already formed matπx. Using preferred embodiments of the present invention, delivery of the desired agents may be controlled by the use of movement of liquid through the matπx. Though not wishing to be bound by any theory, it is theonzed that the liquid m a matπx of polymer and non-gellable polysacchande is either bound to the non-gellable polysacchaπde or it is unbound in the polymer mass. Thus, it is theonzed that the present invention uses the free liquid portion of the matnx as a general solvent and as a means to debver desired agents Soluble drugs are easily dissolved in the free liquid portion, however sbghtly soluble drugs are ground to a fine powder and may require the use of a wetting agent such as glycerol or isopropyl alcohol or a surfactant such as polysorbate, tnton-X or sodium lauryl sulfate. t 8 Once the desired active agent or agents are dispersed throughout the matπx, a portion of the agent resides in the non-gellable polysacchaπde, while another portion of the agent is dissolved in the free liquid phase and moves freely through the matπx The ability of the agent to move freely throughout the matπx in the free liquid phase is important in the agent delivery system of the present invention Because the agent is dissolved in the free liquid phase, a concentration gradient of the active agent is created between the matπx of a wound dressing device and the moisture of the wound itself Therefore, when the matπx is placed onto a moist surface such as an open wound, the soluble agent will move through the free liquid phase toward the agent-free wound moisture, resulting m the delivery of the agent to the wound This movement of soluble agent further upsets the equihbπum between soluble and insoluble agents, and causes more agent to dissolve into the free liquid phase, thus causing more agent to be delivered to the wound Because the present invention incorporates the desired agent directly into the matπx rather than incorporating the drug into other debvery vehicles, such as hposomes, the agent may be dissolved in the free liquid phase and reliably delivered to the wound through the process descπbed above Delivery of the desired agents may also be controlled by the degree of cross-linking in the matnx. As descnbed above, the desired agents ma> be added to the other ingredients forming the matπx pnor to the addition of the cross-lmking agent Subsequent addition of the cross linking agent and concomitant polymeπzation results in both chain elongation of monomeπc chemicals and cross-lmking between chains of monomers The combination of chains cross-linked together creates micro-cavities wherein the desired agents are encapsulated By controlling the amount of cross-linking agent and the length of chains of monomer, it is possible to regulate the size of the micro-cavities in the polymer Larger micro-cavities, produced by a lower degree of cross-linking, allow for freer migration and quicker debvery of the desired agent, whereas smaller micro-cavities increase the delivery time Although the bposome based delivery system may also make use of the degree of cross-linking, the hposome itself acts as an additional barπer to delivery, making delivery less controlled and less reliable The present invention compnses compositions that are useful for stabilization of heavy metals, particularly silver, for devices that have sustained release charactenstics, are light stable, and possess antimicrobial activity In particular, this invention relates to the incorporation and stabibzation of silver salts into a hydrated polyacrylate matnx that may be used as a primary contact sustained release silver antimicrobial matenal for use in wound dressings and other devices and mateπals The polyacrylate matπx as taught in the Nangia patent, U.S. Patent No. 5,196,190, has little or no antimicrobial properties when applied to wounds A preferred embodiment of the present invention compnses the incorporation of antimicrobial silver into the matπx to increase its effectiveness and utibty for application such as in wound care where microbial growth may inhibit or complicate the wound healing process. The preferred polyacrylate matπx, like many hvdrated medical devices, contains a sigmficant amount of aqueous moisture. This moisture serves as a solvent in which many of the undesirable characteπstics of silver are exhibited. These include the formation of ionic silver which is highly reactive to functional groups that exist on orgamc mateπal that may be part of the device, the formation of the photo-reactive form (Ag+) of silver that may lead to discolonzation; a solvent phase that contributes to the instability of silver to certain levels of heat; as weU as the transfer of antimicrobial silver to adjoining packaging matenals through migration of silver through the solvent phase. Preferred methods and devices of the present invention compπse addition of compositions compπsmg metals, preferably silver, that are added to hydratable medical devices such as hydrogels to provide stable sustained release antimicrobial activity. The present invention contemplates devices compπsmg metals and a prefened metal is silver Though silver is taught as a preferred embodiment, the present invention compπses use of any metal that imparts antimicrobial activity to a matnx or device. It has been found that silver salts such as silver chloπde are generally stable in the salt form. Moreover, many silver salts such as silver phosphate and silver sulfate are only weakly soluble in aqueous solvent. Methods of the present invention compπse prepaπng a salt of silver dunng the preparation of the matπx, and preferably the matπx is a hydratable polyacrylate polymer. The formation of the weakly soluble salt, silver chloπde, is fully dispersed throughout the matπx and provide the precursor for the formation of the sustained release silver. The deposition of collodial silver chloπde or other weakly soluble salt throughout the matnx is accomplished by any one of several methods of the present invention. In one method, the pre -formed salt, such as silver chloπde, may be incorporated along with other components duπng the compounding of the matπx formulation pπor to polymeπzation. Another method compnses sequentially adsorbing or absorbing solutions compnsing the precursor components, such as weakly soluble salts into a matπx. For example, a solution containing chlonde ions is added to a polymenzed hydrophilic matπx, 0 where the solution is adsorbed or absorbed by the matπx A second solution, containing silver ions, is added to the matπx to form a colloid of silver chlonde in the matπx Another method, and a preferred method, is the sequential addition of anions and cations duπng the compounding of the mateπal mixture, causing the formation and dispersion of the colloid in the mixture pnor to polymeπzation Prefened chlonde ions compπse any dissociable salt, including, but not bmited to, sodium chloπde, potassium chloπde, copper chloπde, feme chlonde, zinc chlonde calcium chloπde and hydrochloπc acid Such chloπde ions may be added in solution or dry form An ionic silver solution compπses compositions such as those prepared by dissolving a salt of silver, including but not limited to silver nitrate, silver acetate, silver citrate, and silver sulphate, into water The silver ions may also be added in a dry form When the polymer is catalyzed to gel, the finely dispersed silver chlonde is immobilized within the polymer where it undergoes disassociation (as an example according to the formula) AgCl → Ag + + Cl Since AgCl is only weakly soluble in aqueous solutions the re-association to AgCl is strongly favored However the ionic form is unstable and may react to hght to form insoluble elemental silver (Ag° ) This form has minimal antimicrobial activity and moreover is a black precipitate that strongly discolors the matπx when it is formed In addition the ionic form (Ag + ) is highly reactive with functional electron donating groups which may reduce its antimicrobial effect Therefore it is desirable to stabilize the silver m hydrated polymers such as the prefened embodiment, by providing an excess of chlonde ions in the matπx to favor association rather than disassociation Although excess chloπde ions in the matπx provide conditions that favor the formation of the stable silver chloπde salt form of silver, an amount of free ionic silver exists in the matnx The ionic form (Ag + ) may react with electron donors leading to a steady conversion of ionic silver into non- antimicrobial forms and left to continue would significantly deplete the matπx of a source of antimicrobial silver The reaction of ionic silver with strong electron donating groups such as light, can be inhibited by the incorporation of a competing electron acceptor that has a higher electrochemical potential than silver in the matπx In the preferred embodiment, either ionic copper or ionic iron are both strong electron acceptors that may be incorporated into the matπx to stabilize ionic silver in the matπx until it is applied to a moist environment such as a wound The electron acceptors are added to the matπx solution in a Λ I stabilizing solution A stabilizing solution is a solution that provides components, including but not bmited to the electron acceptors, that aid in the prevention of the reaction of the active agent. For example, in a preferred embodiment, a stabilizing solution compπses a solution of electron acceptors such as a copper chloπde or feme chloπde solution, for addition to a silver- containing matπx mixture to aid in the prevention of the reaction of ionic silver. Altematively, a stabilizing solution also compπses the addition of electron acceptors, such as copper chloπde or feme chloπde, in a dry form, not in a liquid solution Additionally, a stabilizing solution compπses one or more electron acceptors for prevention of reaction of the active agent. Other electron acceptors that can be used m the present invention include, but are not limited to, gold, platinum and cesium Other strong organic oxidizers may be used to prevent the reduction of ions, such as the reduction of silver by light energy A preferred embodiment of the present invention compπses a wound healing device compπsing a polyacrylate hydratable matnx produced according to US Patent No. 5,196,190 with antimicrobial properties provided by incorporating heavy metals, preferably silver Other preferred embodiments compnses devices that are coated with matπces, preferably a biocompatible polymeπc matnx compπsing a scaffolding polymer network with antimicrobial activity. A non-gellable polysacchaπde may or may not be included with the matπx A silver contaimng polyacrylate matnx generally compπses mixing approximately 100-250 g acrylamide and approximately 0 5 to 5.0 g bisacrylamide into 2800 to 3950 g of water containing between 6 to 54 g of sodium chloπde. To this mixture, add 21 g of guar gum and 188 g of glycerol. After mixing to homogeneity, slowly add an aqueous solution containing approximately 0.01-3.1 g silver nitrate to the mixing batch. Alternatively, molar equivalents of silver acetate, silver citrate or silver sulfate may be substituted for silver nitrate. After formation of the finely dispersed silver complex, dissolve either from about 0.1 to 2.8 g copper chloπde (CuCl 2 ) or about 0.3 to 3.3 g feme chloπde FeCl 3 . Alternatively, molar equivalents of potassium chloπde, magnesium chloπde, zinc chloπde, calcium chloπde, hydrochloπc acid or other soluble chlonde salt may substituted for the feme or copper chlonde. The polymeπzation of the mixture into a polymer is accomplished by blending approximately 0.7 to 3.6 ml TEMED and about 0.2 to 4.6 g ammonium persulphate into the mixture. The mixture is poured into the appropπate molds with the desired shape before polymeπzation in a dark place. The gelled polymer is typically removed from the mold, dehydrated by mild heat <2 λ in a darkened drier and then rehydrated by humidification to a desired moisture content, approximately 15 to 50% w/w. The matrix may cut into a desired size or shape, packaged and then is sterilized by irradiation with an electron beam or gamma irradiation. The present invention also comprises compositions and devices comprising preformed hydrophilhc fibers and methods for making and using such materials with antimicrobial activity. Pre-formed cross-linked hydrophilic fibers have been shown to have utibty in wound care due to their absorbency of wound fluid and their compatibility with exposed tissues. Many hydrophilic fibrous materials are readily available through commercial channels for on- processing, packaging and sterilization for use in wound and other medical applications. However none of these materials are available with silver impregnation due to the instability of silver and due to the lack of effective known methods for the incoφoration of stabilized silver into the substrates of these materials prior to fiber formation. Furthermore these materials have little or no inherent antimicrobial activity. Therefore the most practical method for rendering these materials antimicrobial would be the application of silver in a stabilized form to the pre-formed fibers. U.S. Provisional Patent Application No. 60/157,000, herein incoφorated in its entirety, describes a method of incoφoration of antimicrobial silver into materials, preferably polyacrylate materials, by the formation of a silver chloride colloidal precipitate during the compounding of the matrix material. The silver complex was stabilized by a combination of excess copper and chloride ions. The incoφoration of a stabilized form of silver colloid into pre-formed hydrophilic fibrous materials is impractical. Therefore this invention also comprises methods for the incoφoration of silver into fibrous materials by an impregnation method that causes the in situ formation of a stabilized silver colloid complex within and around the fibrous material. One method of making materials with antimicrobial activity is to disperse a chloride salt of sodium or copper or iron in water at a concentration that remains in solution when the water is combined with an alcohol solvent, including, but not limited to, isopropyl alcohol and ethanol. The fibrous matrix materials for impregnation are then immersed in a bath of the chloride ions so that the material is completely immersed. After a suitable time the material is then removed and blotted of excess chloride-containing solvent. Then the material is immersed in a similar aqueous/alcohol bath that contains silver and copper or iron ions. After a suitable time, the material is removed, blotted of excess reagent and air dried. It is desirable that the ratio of water to alcohol in mixtures that contain the ionic elements not exceed a concentration that would A 3 cause hydrophilic mateπals to begin to gel. A preferred range compπses 5-15% aqueous, it is highly prefeπed that the aqueous portion not be greater than 50%. Reversal of the immersion sequence is inconsequential to the success of impregnation of the fibrous mateπals An alternative method for the impregnation of the silver compound is to combine the silver ion and chloπde ion into an aqueous component of an alcoholic solvent bath along with copper or feme ions before immersion and soaking of the fibrous mateπals Thereafter the fibrous mateπals should be removed, blotted and air dned to form a stable antimicrobial mateπal for application to wounds and other compromised tissues It has been found that silver salts such as silver chlonde are generally stable the salt form. Moreover many silver salts such as silver chloπde, silver bromide, and silver iodide as examples, are only weakly soluble m an aqueous environment. Therefore the present invention compπses methods of prepaπng a weakly soluble salt of silver on and within the filaments of the hydrophilic mateπal duπng the process and is specifically one object of the invention. The formation of the weakly soluble salt, such as silver chloπde is done by sequentially localizing the ions of the salt within the hydrophilic matenal This is accomplished by using the aqueous portion of the aqueous-alcohol solvent bath as the delivery vehicle which is selectively absorbed by the mateπal due to its hydrophilic properties It is possible that some delivery of ionic species is accomplished also by the permeation of the alcohol carrying ions into the matπx as well The coincident location of the silver and chloπde ions in the preferred embodiment result m nucleation of a colloidal-like structure within the matπx. The use of a bath that is predominately composed of an organic solvent such as alcohol or any other solvent that does not cause gelling or swelling of the fibrous mateπals is desirable This is important in that it prevents the need for substantial dehydration of the fibrous mateπals following immersions as well as for allowing recovery, and re-use of the baths for treating other mateπals. The nucleated silver salt within the matπx is immobihzed and stabilized by the presence of excess chloπde containing salts as well as copper or feme ions, similar to the mateπals descπbed above, to render the silver treated matenals resistance to discoloration by light and radiation energy. The distnbution of the nucleated silver salt is such that when the matenal becomes in contact with aqueous substrates such as wound fluid, there will be some solubihzation of the silver salt thereby releasing silver ions which are antimicrobial. The rate of release is controlled by the inherent solubility of the silver salt, the amount of silver and the available moisture which are taken into n consideration to provide sustained release of antimicrobial activity from the treated mateπals A prefened embodiment of the present invention compπses compositions of hydrophilic fibrous mateπals such as cross-lmked carboxymethyl cellulose, calcium algmates and textiles such as cotton that have been impregnated by the methods of the present invention to form mateπals that possess antimicrobial activity which is released in a sustained manner over time and is stable to discoloration by light energy. The antimicrobial matπces taught by the present invention can be formed into a vaπety of devices, especially preferred are those that polymenzed polymers or plastics Such matnces may also be coated onto devices to provide antimicrobial activity to the surfaces of such devices The many uses of the compositions and devices of the present invention are not limited to the examples given here, but include polymeπc matnces and their uses known to those skilled in the art. For example, the present invention contemplates using the matnces for adding antimicrobial charactenstics to cosmetic products such as dressings, topical lotions, or compresses for acne and blemishes, scar reduction, tattoo removal, and laser resurfacing; to body contact medical devιces(such as catheter and guidewire coatings, ostomy appliances, respiratory and feeding appliances, contact lenses, and heanng aids; and to personal and sk n care products such as skin conditioners, banner creams, lubncating preparations, and super absorbents for addition to diapers, adult incontinence products, and feminine hygiene products Stranded structure The devices of the present invention may take many physical forms, however, some preferred embodiments are constructed of thin strands of matπx suitable for placement into the wound bed or cavity. The preferred devices may be constructed from one or multiple strands of matπx. When multiple strands are used in the construction, the strands are secured together by wrap, tie, glue, or altematively by a continuous bπdge of matπx between adjacent strands. Multiple strands are secured together to minimize accidental loss duπng removal of the dressing from the wound bed. Typically, the strands of particular embodiments are bound or secured in the mid-region so that the ends of the device may float free. The advantage of free floating strands is to enable the individual strands to access a maximum volume of the wound and thereby absorb the excess fluid, exudate and debπs. The mechanical action of the free floating strands contributes to the trapping and removal of cellular and wound debπs Concurrently the free floating strands also conform optimally with the contours of the wound surface to maximize contact between the device and the wound bed. Referπng now to the drawings, one preferred conformation of the wound dressing devices of the present invention is now descnbed This preferred conformation is useful for the control of exudate moisture accumulation, for stimulation of mechanical and autolytic debndement. and for delivery of active agents Figure 1 is a three dimensional view of a preferred embodiment of the wound dressing device 10 with a strand 20 of the multi-strand device with free floating strand ends 40 The strands are secured together by a bπdge 30 created duπng the cutting stage and composed of the matπx mateπal used to construct the device. Figure 2 represents a cross-section 22 of a strand 20 of the multi- strand device 10. It is intended that the cross-section 22 illustrate the sum of the linear dimensions of the sides Preferably the sum of the linear dimensions of the sides is at least twice the numeπcal value of the surface area of the cross- section to provide an adequate surface area to volume ratio of the strands. More preferably, the sum of the linear dimensions of the sides is four or more times the numeπcal value of the surface area of the cross section Figure 3 is an illustration of the pattern of a die 45 used for cutting a preferred embodiment of the wound dressing device 10 from an appropπate matπx matenal Cutting blades 55, around the peπmeter of the die, release the cut-out from the stock sheet of matπx duπng the cutting phase of production. Within the peπmeter, a seπes of cutting blades 57 are situated lying parallel to one another extending from the ends of the pattern toward the center but not continuing through the center so as to leave a region 50 of uncut matenal in the center. The pattern of blades may vary according to the puφose of the wound dressing device. For example, the patterns may vary in terms of numbers of strands 20, numbers of regions of uncut region 50 for bπdging strands, and the positioning of the single or multiple bndges 50 relative to the ends of the strands. The cross section 22 of the strands may be any suitable dimension that allows the appropπate interaction between strands and wound environment. The matπx may be any non-dissolvmg mateπal that is suitable for contacting the broken skm, and underlying tissues including non-absorbent natural or synthetic mateπals, or absorbent natural or synthetic mateπals. Figure 4 illustrates a pattern that is an alternative embodiment. It is a circular pattern for making an embodiment 80 whereby the strands 90 radiate away from a central region of uncut matπx that joins the adjacent strands in the unit. Figure 5 illustrates a pattern for making an embodiment whereby the bndge 95 of matπx is offset to one end of the pattern enabling the strands 100 to radiate away from the bπdge in a single direction Figure 6 illustrates a pattern for making an embodiment whereby the strands 120 are irregular m shape over their length from the matπx bπdge 100 Figure 7 illustrates a pattern for making an embodiment whereby the strands are conjoined at several bπdges along the length of the device and at the ends of the device It is to be understood that the pattern can be any vanation of these embodiments and is still within the scope of the present invention The unique stranded embodiment is particularly desirable because it enables the device to maintain its mtegπty and also maximize the surface area to volume ratio of its matπx This is important since the matπx may be an absorbent mateπal where a high surface area to volume ratio increases the rate of absoφtion, without increasing the overall absoφtion capacity of the device In a preferred embodiment, the wound dressing is pπncipally constructed of a ' stranded" matπx, which allows for optimal contact between the strands and the wound area In addition, the stranded matπx construction maximizes the overall flexibility and pliability of the dressing In embodiments of the device where multiple strands are employed, the overall flexibility and conformational characteπstics of the device are maintained by binding strands in only limited and restricted areas Minimal binding of the strands prevents the formation of πgid areas and allows for the effective and optimal utilization of numerous strands in a single device without adversely diminishing contact with the surface of the wound bed Prefened embodiments of the present invention compnse stranded matπces with antimicrobial activity Preferably, the embodiments compnse antimicrobial activity provided by the methods of silver incoφoration into the matnx Another advantage of the stranded matπx construction is the "semi- porous" quality of the wound dressing that allows for the removal of extraneous cellular matter resulting duπng the wound healing process The air in the mter- strands area of the device serve as a reservoir of space that may be displaced allowing for the removal of excess matenals such as exudate fluid, debndement product and cellular exudate from the wound bed As this region fills, the device may swell to provide "support" to the wound bed and surrounding tissues. A wound constitutes damaged or "missing" tissue, and when tissue is missing, the surrounding tissue may "collapse" or sag into the void "Support" in this context therefore, means the temporary filling of the void to hold the surrounding tissue in place where it should reside Removal of debndement product and cellular exudate is further facibtated by unbound, loose strands of the wound dressing devices When ^ placed upon a wound, the loose strands of the devices randomly oπent in the wound bed where the thin filamentous strands and free floating ends contπbute to mechanical debndement of necrotic slough. Since the strands are secured and bound in at least one region, a mechanical union is formed, ensuπng that all strands and necrotic tissue accumulation m the inter-strand spaces are removed from the wound when the device is changed By contnbuting to the removal of extraneous wound products and cellular debπs, the wound dressing device permits cleaning of the wound which in turn prevents and decreases the possibility of infection and contamination. In one embodiment, the wound dressing device is constructed from a matnx composed of an absorbent synthetic polyacrylate matenal. The rate of absoφtion of polyacrylate is significantly increased by cutting the mateπal into strands, which increases the surface area to volume ratio. Polyacrylate mateπal is particularly suitable for the wound dressings of the present invention because it retains its integπty dunng interaction with wound exudate moisture, as well as with necrotic tissue and wound debns. The wound dressing device of the present invention does not dissolve, gel or otherwise disintegrate dunng application to the wound. The preferred matnx swells slightly duπng the absoφtion of moisture, causing the device to conform closely to the walls of the wound bed. In a preferred embodiment, the polyacrylate matnx is cut into free- floating strands bound together through a matπx-bndge in the mid-region. This pattern of construction imparts a significantly high surface area to volume ratio for rapid moisture movement within the absorbent matπx. Wound dressing devices of the present invention may be produced by cutting a desired design pattern from stock sheets of matπx mateπal For example, the matenal may be die-cut from stock sheets of an absorbent polyacrylate wound dressing mateπal. The stranded cut-out may then be coated with an agent to prevent aggregation and tangling of the free floating strands. Coating agents that may be used include, but are not limited to, petrolatum, talcum, polyglycols, glycerol, propylene, glycol, vegetable oil, and animal oil Following the steps of cutting and coating, the mateπal may be steπhzed using stenbzation techniques known m the art such as gamma radiation, steam and heat steπbzation, electron beam or chemical stenbzation (such as by use of ethylene oxide). A preferred composition of the present invention compπses a matπx compπsing a scaffolding polymer, a non-gellable polysacchaπde, and one or more active agents incoφorated therein. A more preferred matπx compnses an acrylamide polymer, guar gum, and one or more active agents incoφorated 3 ? therein. A most preferred matπx compπses an acrylamide polymer, guar gum, has one or more active agents incoφorated therein, and is formed into a stranded structure wherein the strands are secured by at least one common region. The wound dressing devices of the present invention may be used on injured tissue and for bodily fluid drainages where control and management of fluid and secretions is desired. The term "bodily fluid," as used herein, includes, but is not limited to, sabva, gmgival secretions, cerebrospmal fluid, gastrointestinal fluid, mucous, urogenital secretions, synovial fluid, blood, serum, plasma, unne, cystic fluid, lymph fluid, ascites, pleural effusion, interstitial fluid, intracellular fluid, ocular fluids, seminal fluid, mammary secretions, vitreal fluid, and nasal secretions. In particular, the wound dressing devices of the preferred embodiments are especially appbcable for usage on heavily exudating acute and chronic wounds for controlling accumulating exudate moisture, support of the wound bed and surrounding tissues. Importantly, the wound dressings are particularly effective for stimulating and supporting autolytic debndement, and therefore accelerating the wound healing process. In use, the wound dressing devices of the present invention are the pnmary dressing placed in direct contact with the wound bed, or as near as practical against the wound bed The devices may serve as a packing mateπal and, if required, may be secured into position with any suitable secondary wound dressing such as a wrap, tape, gauze, or pad The dressings are temporary, however, and are not intended for permanent incoφoration into the healed tissues. When necessary, the wound dressing devices are changed by first removing any over-dressing matenal and then removing the device, whereby any accumulated necrotic tissue and exudate is lifted away The wound dressing devices of the present invention may be replaced by a fresh device or other suitable wound coveπng. The devices may be placed m their entirety into a wound, placed m combination with additional bundles of the same design into the wound, or cut through the bπdge between strands to reduce the size or number of strands present in the wound. The devices of the present invention may be cut, shaped and modified to accommodate numerous uses and applications. For example, the devices may be used as a gastric retnevable device, wherein a retrieval cord is attached to the device that is then swallowed. After absoφtion has taken place, the devices may be retneved and analyzed for content. The devices may undergo a swelling action as they absorbs exudate moisture, however, they will not dissolve or disintegrate. The swelling action Λ °l displaces necrotic mateπal from the wound surface and forces the mateπal into the ter-strands regions of the device The laden moisture content and the retention of moisture near the wound bed by the invention contnbutes to stimulation of the autolytic debndement process whereby the body's own enzymes break-up necrotic tissue and cellular debns Complete removal of the device occurs due to the conjoined nature of the device The foregoing descnption includes the best presently contemplated mode of carrying out the invention This descnption is made for the puφose of illustrating the general pπnciples of the inventions and should not be taken in a limiting sense This invention is further illustrated by the following examples, which are not to be construed in any way as imposing limitations upon the scope thereof On the contrary, it is to be clearly understood that resort may be had to vaπous other embodiments, modifications, and equivalents thereof, which, after reading the descnption herein, may suggest themselves to those skilled in the art without departing from the spiπt of the present invention EXAMPLE 1 Formation of a Matrix Including A mixing tank was charged with 161 4 kg of water and 9 1894 kg of acrylamide. 0 10347 kg of NNNTN'-methylenebisacrylam de, and 9 3046 kg of glycerol were added and mixed Then 1 0213 kg of guar gum non-gellable polysacchaπde was dispersed in a mixture containing 0 9770 kg of isopropyl alcohol and 2 kg of water The solution of guar gum was then added and dispersed into the acrylamide mixture After suitable mixing, 0 1042 kg of TEMED was added and polymeπzation was catalyzed with 0 0999 kg ammonium persulphate While the batch was still liquid, it was poured into molds to form sheets After gelling had occurred, sheets were transferred to a dessicator and dehydrated to form a stable intermediate stock sheet Pnor to cutting to size, the stock mateπal was re-hydrated in a humid atmosphere After cutting, the matenal was coated with petrolatum The resulting wound dressing device was then sealed into appropnate packaging and irradiated to steπhze it EXAMPLE 2 Absorption Capacity of Polyacrylamide Matrix It was determined that a prefened matπx mateπal composed of cross- linked polyacrylamide and embedded natural vegetable gum absorbed approximately seven times its weight m water Saturation of a flat sheet of matπx mateπal with a thickness of 0 9 mm was achieved m approximately 22 2, 0 hours of continuous exposure to excess water. A similarly sized piece of fiat matnx matenal was cut into thin strands with a calculated 200% increase in overall surface area. The total water absoφtion of this mateπal was also approximately seven times its weight However this mateπal achieved saturation in approximately five hours Similar compaπsons were made between an intact matπx and a matπx cut in such a way as to increase the surface area between 150% and 300% These studies revealed that the matπces retained their overall absoφtion capacity but there was an increased rate of absoφtion proportional to the increase in surface area. EXAMPLE 3 Matnx Absorption Capacities for Various Natural Substances Matπces, cut into strands, were tested for absoφtion capacities on a vaπety of natural aqueous based viscous fluids These fluids included water containing salt (0 15 M salinity), cow's whole milk, egg whites from chicken eggs, yogurt, and fetal bovine serum. The absoφtion of moisture by the test matπx strands ranged between 3.2 and 7.3 times the oπginal weight of the tested devices EXAMPLE 4 Absorption Capacity of Matrix in Heterogeneous Biological Fluid A polyacrylamide matnx of a preferred device was placed into a test tube containing fetal bovine serum, in an amount equal to five times the weight of the matπx The matnx absorbed the aqueous fluid from the serum, leaving a concentrate of serum proteins in approximately four hours at 4°C The concentrated serum proteins were predominately located between the strands of the device as a thick viscous coagulation When the device was removed from the tube, the concentrated proteins were also removed. This expeπment showed that the design would assist in the debndement of the wound. EXAMPLE 5 Construction of Stranded Matrices Initial prototypes of the stranded matπces were prepared by taking flat sheets of polyacrylamide matπx and cutting them into th strands using a shaφ instrument such as a box knife. Several methods were tested to determine a satisfactory method for commercial production of the device. The following tests were earned out with success: Test 5(a) Matnx mateπal was processed through a pasta cutter using a blade for noodles. _. . Test 5(b). A steel rule die was constructed such that parallel bands of steel rules, separated by spacers were locked into a die block. Matπx was cut by placing the die over the matπx and press-cutting with a hydraulic press Test 5(c). Matπx formula was compounded and catalyzed to initiate polymeπzation. The matπx was then placed into a 50 ml synnge and extruded as a thin strand onto a sheet. The thin strands were allowed to complete polymenzation and then were dned and cut to uniform lengths for use in the device. Test 5(d). A rotary die was constructed with a preferred pattern. The rotary die was placed into the rotary die assembly and matπx was fed through between the rotary die and the anvil for cutting. EXAMPLE 6 Optimization of Matrix Construction Utility Several prototypes were constructed to optimize the utibty of the device as follows: Test 6(a) Individual strands cut from a sheet of matπx were banded together using a sihcone elastomer πng. The πng, having an internal diameter of approximately 3 mm and a length of 1.5 mm, was stretched open so that between five to seven strands could be threaded through and secured by the band about the middle. When placed into fluid for absoφtion studies, it was found that the unit nature of the device was retained throughout the absoφtion penod and that the whole device was removed without leaving remnants in the absoφtion chamber. Test 6(b) Prototypes constructed by using one strand to tie other strands together performed satisfactory m absoφtion and retneval studies. Test 6(c) Prototypes constructed by maintaining a continuous bπdge of matrix between adjacent strands were tested and shown to perform satisfactory in absoφtion and retneval studies. EXAMPLE 7 Incorporation of Penicillin G into the Matrix The incoφoration of the antimicrobial agent, penicillin G, into the matπx was evaluated by dissolving 1 x 10 6 units of penicillin G powder into 50 milhbters of water. Acrylamide, methylenebisacrylamide, glycerol, and a guar gum/isopropyl alcohol mixture were added to a flask containing 900 ml water and mixed for two hours. The penicillin solution was then added to the flask along with TEMED dissolved m 25 ml water After thorough mixing, ammonium persulphate in 25 ml water was added and mixed thoroughly. The mixture was then poured into sheet molds and allowed to gel. The sheets of semi-solid gel material were stripped from the mold and dehydrated to approximately 7% their original water content for storage. Prior to testing, the sheets were placed in a humidified environment until the sheet weight had increased to approximately 118-122% the storage weight. Discs of 0.7 cm diameter were cut from the sheets. The discs were placed onto the surfaces of agar plates that had previously been seeded with various strains of microorganisms (Staph aureus; E. coli; Candida albicans; Ps aeruginosa). The plates were incubated and then examined for zones of inhibition around the discs containing antibiotic verses control discs. Zones of inhibition were measured around the penicillin containing matrix but not the control matrix on the Staph aureas, E coli, and Pseudomonas aeruginosa plates. No zone was measured on the Candida albicans plate. These results demonstrate the release of active penicillin G after its incoφoration into the matrix. EXAMPLE 8 Incorporation of Silver Chloride Precipitate into the Matrix Silver chloride is a weakly soluble salt that dissociates in water to release the silver ion that may have antimicrobial activity. Silver nitrate was dissolved into the batch mixture of pre -polymerized matrix at a concentration of 5 x 10 '3 M and then mixed well. The silver was precipitated by the addition of sodium chloride to produce a colloidal suspension of the weakly soluble salt. The batch was then polymerized by the addition of TEMED and ammonium persulphate and cast into sheets. The sheets were dehydrated to approximately 5% of the original moisture content and stored in the dark. Before testing, the sheet stock was hydrated to 118-122% its storage weight and then cut into 0.7 cm discs that were placed on the surface of pre-inoculated agar culture plates. The plates were incubated and then evaluated for growth around the discs. Zones of inhibition were measured around discs on plates inoculated with Staph aureus; E. coli; Candida albicans; Pseudomonas aeruginosa, indicating the release of active silver ions after incoφoration into the matrix. Hydrated sheets exposed to continuous light turned from an amber color to a uniform tan to brown color which illustrated uniform dispersion of the silver chloride precipitate. This also showed the susceptibility of the product to discoloration due to exposure to light when a stabilizing solution such as that of copper or ferric ions, was not added to the mixture. 3 EXAMPLE 9 Synergistic Action Between Therapeutic Agent and Adjuvant The antifungal agent Zn-pynthione is an active agent against a wide range of pathogenic fungi but it poorly penetrates heavily keratimzed tissues such as finger and toe nails. Matπx matenal containing Zn-pyπthione and the keratinolytic agents salicylic acid and urea were tested for increased efficacy of dehveπng agents to control fungal growth in nail tissue. To the pre- polymeπzed batch mateπal was added sufficient Zn-pynthione, salicylic acid and urea to give final concentrations of 0.01%, 5% and 5%, respectively. The batch was neutralized to pH 6.5 by the addition of sodium hydroxide After thorough mixing, the batch was poured into molds to cast into sheets. After gelbng, the sheets were dehydrated to 5% the oπginal moisture content and stored. Before testing, the sheet stock was hydrated to 118-122% its storage weight and then cut into 0 7 cm discs which were placed on the surface of bovine hoof matenal cut thinly to resemble finger nail. These were then transferred onto pre- moculated agar culture plates The plates were incubated and evaluated for growth around the discs. Zones of inhibition were measured around the discs on plates inoculated with Candida albicans. No zones were measured where Zn pyπthione or the keratinolytic agents were not included in the matπx. Smaller zones were measured where only urea and Zn-pyπthione were added. Zones of inhibition were however measured around sets that contained both the active agent and the keratinolytic agents combination These results demonstrate that therapeutic agents and adjuvants may be incoφorated into the matrix and later released in active form such that they work synergistically EXAMPLE 10 Bovine Protein Incorporation into and Delivery from the Matrix Bovine serum albumin (approximately 65,000 Daltons) and bovine gamma globulin (approximately 155,000 Daltons) were dissolved at a concentration of 0.1% w/w into a pre-polymeπzed matπx batch matenal and thoroughly mixed. The batch was polymenzed by the addition of TEMED and ammonium persulphate, poured into molds and gelled into sheets. The sheets were dehydrated to approximately 5% the ongmal moisture content and stored. Before testing, the sheet stock was hydrated to 118-122% its storage weight and then cut into 0.7 cm discs which were placed on the surface of saline agar plates. The plates were incubated for 24 hours at 4°C and then developed by the addition of 0.25 M HC1 solution which causes proteins to precipitate. Zones of 3 *1 protein precipitate were measured only around the discs that had protein incoφorated into the matπx. indicating the release of active protein after its incoφoration into the matπx. EXAMPLE 11 Interleukιn-2 Incorporation into and Delivery from the Matrix The growth factor mterleukιn-2 was incoφorated into polymenzed matπx mateπal by soaking re-hydrated plain stock sheet in fluid containing the growth factor. After 24 hours of soaking at 4°C, the matπx pieces were cut into one cm circles and placed into salme Samples of the elution fluid were taken at intervals and assayed by ELISA (Enzyme Linked Immunosorbent Assay) for ιnterleukm-2 to determine if mateπal entered the matπx and was then released The results showed that proportionately more IL-2 was eluted from the matπx over time EXAMPLE 12 Temporal Release ofAntifungal Agent Fluconazole was incoφorated by the addition of the active agent to a pre-polymeπzed batch of matπx. After polymeπzation, dehydration and rehydration, a disc containing the active agent was placed onto an agar plate for two hours at 4°C. Thereafter, every two hours for a total of 154 hours, the disc was removed and transferred to a new spot on the surface of the agar. After all transfers had been earned out, the plates were inoculated with Candida albicans and incubated at 35°C until confluent growth had occurred. The seπal transfer spots on the plates were then examined for zones of inhibition The results showed that the device delivered a high dose of fluconazole in the first eight hours and then a steady concentration thereafter until the 140th hour when the concentration, according to zone size, began to diminish. EXAMPLE 13 Delivery of a Biologically Functional Protein from the Matrix Human transfemn is an iron chelating protein of approximately 70,000 MW. Transfemn was incoφorated into the pre-polymeπzed batch mix at 0.05% w/w, mixed, and then encapsulated by polymeπzation with TEMED and ammonium persulphate. After dehydration, rehydration and cutting, discs of 0.7 cm were placed onto the surface of nutπent agar plates and incubated at 4°C for 24 hours. The discs were then removed and the plates were inoculated with Staph aureus and then incubated at 37°C overnight. The plates were examined for zones of inhibition where the transfemn removed the trace element iron from the nutπent Human transfemn retained its biological activity duπng incoφoration, processing and testing as measured by the zones of inhibition around the spots where transfernn-contaming discs had been placed. EXAMPLE 14 A wound healing device compnsing a polyacrylate hydratable matπx produced according to US Patent No. 5,196,190 and containing silver was made using the following steps. The silver containing polyacrylate matπx was made by mixing 185 g acrylamide and 2 g bisacrylamide into 3330 g of water containing between 33.3 g of sodium chloπde. To this mixture, was added 21 g of guar gum and 188 g of glycerol. After mixing to homogeneity, a solution containing 0.563 g silver nitrate was slowly added to the mixing batch. After formation of the finely dispersed silver complex, either from 0.16 g copper chloπde (CuCl 2 ) or 0.46 g feme chloπde FeCl 3 was dissolved into the mixture The polymeπzation of the mixture was accomplished by blending 1.8 ml TEMED and 2.6 g ammonium persulphate into the mixture. The mixture was poured into the appropπate molds before polymeπzation m a dark place. The gelled polymer was removed from the mold, dehydrated by mild heat in a darkened dner and then rehydrated by humidification to a desired moisture content, 22% w/w The matnx was then cut if necessary, packaged, and stenbzed by madiation of electron beam or gamma irradiation. EXAMPLE 15 This Example shows the antimicrobial activity of the silver- containing matπx wound dressings of Example 14 in a zone inhibition assay. Fresh overnight suspension cultures of each of vaπous medically important bacteπa and fungi were coated onto the surface of trypticase soy agar, for bacteπa, or Sabouraud's agar plates, for fungi. Circles 5 mm in diameter, were cut from the silver-containing dressings and from control dressings that do not contain silver. The circles were placed on the surface of the cultured plates which were then incubated for 24-48 hours. Zones of inhibition were measured at the completion of the incubation phase. The diameter of the zones were measured and are expressed m Table 1. l Table 1. Strain of organism Zone of Inhibition (mm) AcryDerm Silver Control mg Staph. aureus 19 <5 Staph. aureus (coagulase -) 28 <5 Staph. aureus (MRSA) 16 <5 Group A Streptococcus 23 <5 Bacillus subtilis (spore former) 15 <5 Listena monocytogenes 18 <5 Ps. Aeruginosa 21 <5 Proteus mirabihs 16 <5 Enterobacter faecalis 20 <5 Enterobacter cloacae 9 <5 Kleb. Pneumoniae 20 <5 Candida albicans 13 <5 Candida parapsύosis 20 <5 T. rubrum 15 <5 M. gypseum 9 <5 EXAMPLE 16 This example was directed to showing that the devices of the present invention, compns g a matπx with silver incoφorated, such as those made by the methods of Example 14, was stable to light This was done by prepaπng 1 inch circles of silver-containing matπx that were then stored in the dark. Each day for 7 days a 1 inch circle of matπx was transfeπed from dark to a lighted area so that at the end of the 7 th day a total of 8 circles had been exposed to light for between 0 time and 7 days. Dressing circles that contained silver chloπde without the photostabhzation chemistry were treated identically. The dressings that had no photostabibzation chemistry had reacted by the formation of a blackening in the matnx The blackening was proportional to the amount of time the matnx had been exposed to light. By contrast samples that were stabilized by either copper or iron did not show discolonazation. 2 7 EXAMPLE 17 The sustained release of silver was shown in this example using the dressing made in Example 14 This was demonstrated by seeding agar nutπent plates with a test strain of microorganisms daily for 6 days. The trypticase soy agar were inoculated with a fresh overnight inoculum of Staph. aureus The plates were then incubated for 24 h at 37° C. The zones of inhibition were then measured before transfemng the dressing circles to a freshly inoculated plate of TSA This process was repeated daily for 5 days to measure the release of antimicrobial activity into the culture plate To clanfy, on day 1, a piece (5 mm circle) of silver-containing dressing was placed on the first plate and incubated for 24 hours The circle was then transfeπed to the second plate for a further 24 hours and so on. Each plate was then incubated to determine the zone of inhibition around the area where the piece of matπx had been deposited. Figure 8 shows the data of the silver- containing dressing and a control dressing that did not contain silver. The results showed that silver was released over a penod of 6 days m a concentration sufficient to inhibit the growth of the indicator strain of bacteπa used in the test. EXAMPLE 18 Cytotoxicity of siher-containing wound dressings for mammalian cells Tissue cytoxicity was evaluated b> the in vitro method taught m the AAMI Guidelines for Biological Evaluation of Medical Devices. Samples of the silver-containing wound dressings of Example 14 were added to DMEM tissue culture medium and incubated. Fetal bovine serum was added before the samples were transferred to confluent monolayers of L-929 ftbroblasts The cultures were incubated at 37° C in 5% C0 2 for 24 h. Alamar Blue vital dye was added for the last 4 h of incubation. The culture supernatants were removed, assayed for OD difference at 570 and 600 nm wavelength along with the positive (fresh medium alone) and negative (3% w/v acetic acid in saline) controls. The viabibty of ftbroblasts was also evaluated by parallel cultures stained with the vital dye, trypan Blue (data not shown) The silver-containing dressing was indistinguishable from the positive growth control sample with greater than 99% of fibrobalsts over the culture peπod. The acetic acid solution caused a greater than 88% decrease in viability in the ftbroblasts culture. These findings are consistent with microscopic observation of cultures treated with trypan blue vital dye (data not shown). Figure 9 shows the results of the silver-containing dressing and the positive and negative controls. j S EXAMPLE 19 This Example shows the absorbency profile of the silver- contaming dressings of the present invention, such as that made by Example 14 Squares (2 5 cm) were cut from the matπx of Example 14 that does not contain silver, and the silver-containing dressing These were weighed and then placed into isotonic saline solution at room temperature At vaπous intervals each matπx was removed, damped of excess moisture and reweighed This procedure was repeated over the course of 24 h The hydrophilic base polymer alone increased by 720% in saline The addition of silver to the matnx only slightly reduced its absorbency (605% vs 720%) Figure 10 shows the absoφtion profile and the donation of moisture by the silver-containing dressing Donation of moisture testing was earned out by weighing the silver polyacrylate matenal onto dned pre-weighed filter paper and allowing it to stand for vanous intervals before re-weighing to detect moisture donation EXAMPLE 20 This Example was directed to showing the light stability and skin staining characteπstics of silver-containing wound care dressings Ionic silver (Ag+) is reduced to a black precipitate (Ag°) by light energy The silver- containing matnx of Example 14 suppressed the light reaction of silver This was demonstrated by exposing 2 5 cm circular samples of silver-containing matπx to light for vaπous numbers of days There was almost no darkening of the silver-containing dressing for up to 8 days of exposure to room light Bv contrast, silver nitrate impregnated filter papers showed significant darkening within 24 h exposure to light When placed on skin and exposed to light, similar results were seen The silver impregnated paper stained the skin whereas the silver- containing matπx did not EXAMPLE 21 RATE OF BACTERIAL KILLING The time between exposure to the antimicrobial and the bacteπcidal event is related to the rate of release of silver from the matπx The rate of killing of E coh by silver-containing matπx from Example 14 was determined by suspending a 1 gram sample of matπx in a bacteπal suspension After vanous time intervals samples were removed and plated counted to determine the number of surviving bacteπa Fig 11 is a plot of the number of surviving organisms at the vanous sample intervals following exposure to the silver-containing matπx i <7 EXAMPLE 22 SKIN BIOBURDEN Continued silver ion formation and release from the silver containing polyacrylate is dependent upon disruption of the equihbnum between colloid and free ions in the aqueous phase of the matnx. Theoretically even small amounts of aqueous fluid added to the matπx will cause additional release of silver Furthermore this released silver should be sufficient to be bacteπcidal to organisms in contact with the dressing. This was illustrated by placing either silver-containing matπx of Example 14 or non-silver containing matnx on sk for a set time interval and then sampling under each of the matπces for surviving bacteπa. Samples of matπx from example 14 along with plain non-silver containing matπx was placed on adjacent areas of the forearms of volunteers 24 h later the specimens were removed and the areas in a precise 30 mm circle were swabbed and plated and counted to determine the microbial bioburden The plain matnx served as the control for each of the five individuals. In all cases the presence of silver significantly decreased the bioburden compared to the plain matnx (see fig. 12). Each line is the test of one individual. EXAMPLE 23 BIOCOMPATABILITY TESTING Devices containing bioactive ingredients must be compatible with tissues to have utility in clinical applications. This is generally determined by testing the devices for their propensity to cause imtation or to induce sensitization Skin imtation testing was earned out by secuπng 30 mm diameter pieces of the matπx of Example 14 to the forearms of volunteers for 7 days. Plain matnx without silver (FlexiGel) served as the known non-irπtating control Latex served as a probable lrntating mateπal Specimens were secured by a polyurethane thin film adhesive dressing. At the conclusion of the induction phase the mateπals were removed and the areas were scored for erythema and induration consistent with imtation (see results m the table 2). Sensitization is the induction of an lmmunological response to agents or sensitizers in the mateπal This was measured by the local lymph node assay which is earned out by placing test mateπals on the ears of mice each day for 5 consecutive days On the fifth day the animals received a dose of radioactive thymidine for a pulse peπod of 4 hours. Thereafter the local draining lymph nodes were removed from the animals and measured for thymidine incoφoration. The higher the level of incoφoration the more sensitized the io animals. The findings laid out in table 2 showed that none of the animals were sensitized to the silver-containing matπx of Example 14 Table 2: Biocompatibibty Testing EXAMPLE 24 AgCl COLLOID NUCLEATION IN SOLVENT FOR AQUACEL Example 24 was directed to the development of methods for the nucleation of silver chloπde in Aquacel (carboxymethoylcellulose, CMC) using water in IPA (Isopropyl alcohol) or EtOH (ethanol) as the debvery and permeation vehicles One aspect of this Example was to establish solvent to water ratios for the precipitation of silver chloπde into pre-formed filamentous mateπals such as Aquacel (CMC) and alginates. Aquacel and alginates are hydrophilic mateπals that aggressively absorb aqueous solutions which often cause gelling of the matπx mateπals Gelled mateπals may be subsequently dehydrated, but seldom retain their oπginal properties after absoφtion of water. Therefore it is impractical to use a substantially aqueous vehicle for the delivery of ionic silver and chloπde into the matπx mateπal where nucleation in situ of colloid would be expected to occur. This excludes the method of precipitating AgCl in situ using water as solvent. Aquacel and alginates do not absorb alcohol, therefore a AgCl precipitation m a water;alcohol solution to partially hydrate fibers with reagents can be done. A. This expenment of the Example showed the use of either acetone, isopropyl alcohol or ethanol as the solvent phase of an aqueous: alcohol bath for impregnation of silver into cross-lmked carboxymethyl cellulose. The following combinations of reagents were produced and tested for efficacy in allowing nucleation of AgCl m the solvent phase. 1) Add 0.177 g NaCl to 3.333 mL ELO. 2) Add 90 g Acetone, EPA, or EtOH. Add 6.666 mL AgN0 3 sol (0.11325g/50ml H 2 0) Observe precipitate formations It was concluded that the ethanol was the preferred alcohol for the debvery vehicle. B. This expeπment was earned out to determine if separate aqueous:alcohol solutions could be pre-made and then combined before the immersion of hydrophilic mateπals as an appropnate single bath method for impregnating hydrophilic polymers. Separate reagents were prepared according to the formula below and then combined together 1 ) Add 0.221 g AgNO 3 to 200μL H 2 O to 25 g EtOH 2) Add 0.5 g NaCl to 2 mL water to 25 g EtOH Combine solutions Results: Immediately following combining of the reagents a heavy rapidly forming precipitate developed m the mixture. It was not appropπate to pre-mix separate solutions that are later combine to form the bath for the immersion of hydrophilic matπx mateπal for impregnating with silver C. The puφose of this expeπment was to determine if sodium thiosulfate dissolution of silver chlonde would aid in the deposition of the antimicrobial silver in hydrophilic fibers. The reagents were prepared in the following fashion an observed for the formation of a fine precipitate after combination with either alcohol or water. 1) Add 0.177 g NaCl to 4 ml H 2 O 2) Add 6ml AgNO 3 sol (0.11325g/50ml H 2 O) 3) Add 0.015 g Na thiosulfate to dissolve AgCl 4) Add half to 90 ml H 2 O, half to 90 ml EtOH The test showed that the addition of the reagent with sodium thiosulfate with ethanol allowed the formation of a precipitate but none formed when the reagent was added to water. Solvent +AgCl(sol) 90 mL H 2 O no precipitate 90 mL EtOH preferred precipitate Sodium thiosulfate may interfere with nucleation of silver chloπde in hydrophilic fibers. . , D. The nucleation of silver chlonde colloid in the hydrophilic polymer was accomplished by prepanng an aqueous:alcohol solution of sodium chloπde in which vaπous hydrophilic matenals were immersed After an appropnate time an aqueous "alcohol solution containing silver nitrate was added The mateπals were then removed, blotted of excess mateπals and air dned They were then tested for antimicrobial activity against Staph aureus by zone inhibition assay, for skin staining properties and for discoloration in light. 1) Add 0.1777g NaCl to 2 ml H 2 O 2) Add 0.006795 g AgNO 3 to lOOμl Hf) 3) Add 25g EtOH to NaCl and AgNO 3 solutions 4) Place a 2x2 in. square of Tegagen, Algisite M, Aquacel, or Algisite Rope into the NaCl solutions 5) After a few seconds, add the AgNO 3 solution. 6) After a few seconds, remove dressings and blot dry 7) Test for sustained release on staph zone inhibition plates, for skin staining, expose to light. Antimicrobial Zone inhibition assay against Staph aureus m evaluation of sustained release over 3 days Senal transfer of antimicrobial activity Skm staining caused by the topical application of the mateπals to intact skin and then observing for the occurrence of darkening around the application sites: Dressing Matenals Skm staining Acticoat yes Ag-Aquacel no Acticoat wet yes Ag-Aquacel wet no The light stability of the matenals were evaluated after impregnation with silver either as dry substrate or after wetting with water. * This embodiment contains twice the amount of silver as the Ag Aquacel Overall Summary: Silver was incoφorated into hydrophilic fibers in amounts that allowed for sustained release IPA or acetone may be used with more soluble chlonde salts (CuCl 2 , FeCl 3 ) but ethanol is the preferred solvent when using sodium chlonde. The resulting matenals possess antimicrobial activity and do not appreciably discolor in the presence of light. EXAMPLE 25 Titration of the NaCl, Ag, Cu concentrations for effecting impregnation of stabilized silver into Aquacel This Example was designed to develop a method for incoφorating AgCl into Aquacel fibers to form a color stable, sustained release antimicrobial hydrophilic matenal for wound care applications. It is possible to add AgCl to fibers so that it may be released over a sustained penod of time. Sustained release characteπstics are imparted by the size and location of nucleated silver chlonde in the hydrophilic fibers. The stability of the mateπal to light is controlled by the amount of NaCl, and the location and concentration of Cu ions in the mateπal. The following ratios of reagents were prepared and used to impregnate 2 x 2 inch samples of carboxymethyl cellulose (Aquacel). The stock solution of silver used m these tests was 0.11325g Ag/50mL H 2 O. The stock solution of copper ions was 0.0495g Cu/lOg EtOH. a. 0.1777g NaCl in 2 ml H 2 O, add to 50g EtOH, add dressing, add 6mL AgNO 3 sol., add Oμl Cu b. 0.1777g NaCl in 2 ml H 2 O, add to 50g EtOH, add dressing, add 3mL AgNO 3 sol., add 0 μl Cu c. 0.1777g NaCl in 2 ml H 2 O, add to 50g EtOH, add dressing, add 6mL AgNO 3 sol., add 333 μl Cu d. 0.1777g NaCl in 2 ml H 2 O, add to 50g EtOH, add dressing, add 3mL AgNO 3 sol, add 333 μl Cu e. 0.0888g NaCl in 2 ml H 2 O, add to 50g EtOH, add dressing, add 6mL f. 0.0888g NaCl in 2 ml H 2 O, add to 50g EtOH, add dressing, add 6mL AgNO 3 sol., add 500 μl Cu g. 0.0888g NaCl in 2 ml H 2 O, add to 50g EtOH, add dressing, add 3mL AgNO 3 sol, add 0 μl Cu h. 0.0888g NaCl in 2 ml H 2 O, add to 50g EtOH. add dressing, add 3mL AgN0 3 sol, add 500 μl Cu i. 0.01359g AgNO 3 to 100 μl H 2 O, add to 25g EtOH/0.0888g NaCl in 2 ml H 2 O, add Oul Cu, add to 25g EtOH, add dressing, add AgNO 3 solution. j. 0.01359g AgNO 3 to 100 μl H.O, add to 25g EtOH/0.0888g NaCl in 2 ml H,O, add 500 μl Cu, add to 25g EtOH, add dressing, add AgNO 3 solution, k. 0.006795g AgNO 3 to 100 μl H 2 O, add to 25g EtOH/0.0888g NaCl in 2 ml H 2 0, add 0 μl Cu, add to 25g EtOH, add dressing, add AgNO3 solution. 1. 0.006795g AgNO 3 to 100 μl H 2 O, add to 25g EtOH/0.0888g NaCl in 2 ml H 2 O, add 500 μl Cu, add to 25g EtOH, add dressing, add AgNO 3 solution, m. 0.006795g AgNO, to 100 μl H 2 O, add to 25g EtOH, add dressing/,0888 NaCl in 2 ml H 2 O, add 0 μl Cu, add to 25g EtOH, add to AgNO 3 solution, n. 0.006795g AgNO 3 to 100 μl H 2 O, add to 25g EtOH, add dressing/0 NaCl in 2 ml H 2 O, add 0 μl Cu, add to 25g EtOH, add to AgNO 3 solution. Add 10 g H 2 O to 25 g EtOH, add dressing Samples were immersed then removed from the bathes and blotted then dried in air. A portion of each sample was exposed to light as weU as for antimicrobial activity against Staph. aureus. Results: Samples that contained higher concentrations of silver discolored more quickly in light with most samples eventually turning a puφlish color. The exceptions were samples "n" and "o" which remained white. With the exception of the sample developed from the combination in "o", the samples had an acceptable feel and texture. Sample "o" was stiff following processing. All samples produced the same size zone of inhibition on the staph plate except for sample "o", which had no zone of inhibition. L /3 EXAMPLE 26 A compaπson of silver chlonde nucleation in solutions containing both silver and chloπde ions vs. separation of the reagents Previous evaluations of the process incoφorated the silver into a bath that contained the hydrophilic fibrous mateπals This resulted in the formation of a desirable effect but had the disadvantage that solutions could not be re-used. This evaluation was undertaken to determine if nucleation occurred when matenals were first treated with chloπde ion containing reagent then πnsed before immersion into a silver ion containing reagent bath Experimental Design: Specimens of carboxymethylcellulose were impregnated with silver by the following methods 1) 2 x 2 inch specimen of Aquacel were impregnated with silver by: Prepare an aqueous:ethanol solution by adding 0.0888g NaCl in 2 ml H 2 O to 25g EtOH. Place a 2 x 2 in sample of Aquacel into the solution for 20 seconds and then remove. Rinse in ethanol 3 times to remove excess chloπde ions from the surface then place the sample in an aqueous:alcohol solution made by combining 0.006795 g AgNO 3 in 100 μl H 2 0 to 25g EtOH. Allow the specimen to stand for 10 seconds then remove, πnse and blot dry before testing for stability to light and for sustained release of antimicrobial activity. Prepare an aqueous-ethanol solution by adding 0 0888g NaCl in 2 ml H 2 O and 500 μl Cu solution (0.0495g Cu/lOg EtOH) to 25g EtOH. Place a 2 x 2 in sample of Aquacel into the solution for 20 seconds and then remove. Rinse m ethanol 3 times to remove excess chloπde ions from the surface then place the sample in an aqueous:alcohol solution made by combining 0.006795 g AgNO 3 in 100 μl H 2 O to 25 g EtOH. Allow the specimen to stand for 10 seconds then remove, nnse and blot dry before testing for stability to light and for sustained release of antimicrobial activity. Control samples were prepared by soaking specimens in aqueous:ethanol solutions made by adding 0.0888g NaCl in 2 ml H 2 O with either 500μl or 1000 μl Cu solution (0 0495g Cu/lOg EtOH) to 25g EtOH. After 10 seconds of soak the aqueous:alcohol solution was made by combining 0.006795 g AgNO 3 in 100 μl H 2 O to 25g EtOH was added directly to the first mixture, allowed to stand for 20 seconds before removal, blotting and drying 2) Blot to dry, expose to light and test for zones of inhibition with staph. tt> The results showed that chasing in silver ions after chloπde ion impregnation does lead to the development of antimicrobial activity. However the activity level was lower than that for matenals developed by adding the silver ion to the chlonde ion m the same batch EXAMPLE 27 Impregnation of vaπous hydrophilic and non-hydrophilic mateπals with the silver impregnation technology This Example was to determine whether the solvent precipitation method can be used on other fibrous mateπals Samples of a vaπety of mateπals were treated by the common bath impregnation methods to convert them into sustained release antimicrobial matenals The matenals were prepared into 2x2 inch pads and included Kaltostat alginate pad, Cunty gauze sponge, NuGauze, Telfa non-adherent pads, Kaltostat alginate rope, and Aquacel. The piocedure for impregnation was earned out as descnbed below. Where Cu was incoφorated into the procedure it was drawn from a stock solution at 0 0495g Cu/lOg EtOH Procedure: Samples were prepared by soaking specimens in aqueous:ethanol solutions made by adding 0.0888g NaCl in 2 ml H 2 O with 500 μl Cu solution to 25g EtOH. After 10 seconds of soak the aqueous:alcohol solution made by combining 0.006795g AgNO 3 in 100 μl H 2 O to 25g EtOH was added directly to the first mixture, allowed to stand for 20 seconds before removal, blotting and drying. B. Samples were prepared by soaking specimens aqueous solutions made by adding 0.0888g NaCl in 2 ml H 2 O with 500 μl Cu solution to 25g H 2 O. After 10 seconds of soaking, the aqueous solution made by combining 0.006795 g AgNO 3 ml 00 μl H 2 O to 25 g H 2 O was added directly to the first mixture, allowed to stand for 20 seconds before removal, blotting and drying. Results: Light stability testing- — Samples prepared by using fully aqueous soaks turned color quickly even when still et when exposed to light. By contrast the samples prepared using the aqueous:alcohol soak were more stable to light Telfa treated by the aqueous:alcohol bath method did not tum color at all The texture of dressings treated with aqueous:alcohol were supenor to those produced in the aqueous bath w hich were stiff and ngid. Antimicrobial Seπal Transfer: Test organism used was Staph. aureus. EXAMPLE 28 Stability of silver impregnated hydrophilic carboxymethyl cellulose to electron beam stenbzation methods. This Example was done to examine the effects of electron beam irradiation on silver treated Aquacel Expenmental Design: Samples of Aquacel were impregnated with silver along with vanous amounts of copper ions by the following methods: Samples were prepared by soaking specimens in aqueous: ethanol solutions made by adding 0.0888g NaCl m 2 ml H 2 O with 500 μl Cu solution (0.0495g Cu/lOg EtOH) to 25g EtOH. After 10 seconds of soak the aqueous:alcohol solution made by combining 0.006795g AgNO 3 in 100 μl H 2 O to 25 g EtOH was added directly to the first mixture, allowed to stand for 20 seconds before removal, blotting and drying. Samples were prepared by soaking specimens in aqueous :ethanol solutions made by adding 0.0888g NaCl in 2 ml H 2 O with 500 μl Cu solution (0.0495g Cu/lOg EtOH) to 25g EtOH. After 10 seconds of soak the aqueous:alcohol solution made by combining 0.01359g AgNO 3 in 100 μl H 2 O to 25g EtOH was added directly to the first mixture, allowed to stand for 20 seconds before removal, blotting and drying. Samples were prepared by soaking specimens in aqueous :ethanol solutions made by adding 0.0888g NaCl in 2 ml H 2 O to 25g EtOH. After 10 seconds of soak the aqueous: alcohol solution made by combining 0.006795 g AgNO 3 in 100 μl H 2 O to 25g EtOH was added directly to the first mixture, allowed to stand for 20 seconds before removal, blotting and drying. All samples were then placed in medical grade aluminum foil pouches, heat sealed and dispatched to e-beam for iπadiation. After their return they were tested for stability in light and for sustained release of antimicrobial activity. Results: Li ht stabilit reaction following e-beam iπadiation: The samples were equally stable against the effects of e-beam radiation regardless of the amount of copper present. Similarly increasing the dosage of silver did not increase the risk of discoloration by e-beam energy. Antimicrobial Serial Transfer: Test or anism used was Sta h. aureus. The articles retain their antimicrobial activity following e-beam irradiation. It should be understood that the foregoing relates only to preferred embodiments of the present invention and that numerous modifications or alterations may be made therein without departing from the spirit and the scope of the invention as set forth in the appended claims. i t

Claims: Claims What is claimed is- 1 A biocompatible polymeπc matπx, compπsing, a scaffolding polymer network and a non-gellable polysacchaπde, and having an active agent directly incoφorated therein. 2. The matnx of Claim 1, wherein the non-gellable polysacchaπde is a non-gellable galactomannan selected from the group consisting of guar gum, honey locust bean gum, white clover bean gum, and carob locust bean gum. 3. The matnx of Claim 1, wherein the non-gellable polysacchaπde 4. The matnx of Claim 1, wherein the polymer is polyacrylamide. 5. The matπx of Claim 1 further compπsing a water loss control agent, a plasticizer, and a hydration control agent. 6. The matπx of Claim 1, wherein the matπx is shaped as a wound dressin Όg device. 7. The matπx of Claim 1, wherein the active agent is selected from the group consisting of metals 8. The matπx of Claim 7, wherein the metal is silver. 9. The matπx of Claim 8, wherein the silver is a weakly soluble silver chloπde colloid. 10. A method of making a matπx, compπsing: (a) combining a polymer, cross-linking agent, non-gellable polysacchaπde and one or more active agents; (b) adding a cross-linking catalyst and TEMED and mixing; (c) pouπng the mixture into molds; (d) dehydrating and re-hydrating the sheet; 11. The method of Claim 10, wherein the active agent is metals. O 12. The method of Claim 10, further comprising adding a hydration control agent. 13. The method of Claim 10, further comprising a coating agent. 14. The method of Claim 10, further comprising adding a stabilizing solution to stabilize the active agent. 15. The method of Claim 14, wherein the stabilizing solution comprises ferric chloride. 16. The method of Claim 14, wherein the stabilizing solution comprises copper chloride. 17. A method for making a matrix having antimicrobial activity, comprising, a) adding , in no particular order, an anion-donating solution and a cation-donating solution, to a polymeric matrix to form an active agent on the polymeric matrix; b) adding to the polymeric matrix a stabilizing solution 18. The method of Claim 17, wherein the matrix is carboxymethyl cellulose. 19. The method of Claim 17, wherein the active agent is metals. 20. The method of Claim 19, wherein the metal is silver.

Inventors: GIBBINS BRUCE L, HOPMAN LANCE D, GIBBINS, BRUCE, L., HOPMAN, LANCE, D.
Applicants: ACRYMED, GIBBINS BRUCE L, HOPMAN LANCE D, GIBBINS, BRUCE, L., HOPMAN, LANCE, D.
Application year: 2000
Main classification: A61L15
IPC codes: A61K9, A61K47, A61L15