Search Images Maps Play YouTube News Gmail Drive More »
Sign in
Screen reader users: click this link for accessible mode. Accessible mode has the same essential features but works better with your reader.


  1. Advanced Patent Search
Publication numberUS3800792 A
Publication typeGrant
Publication dateApr 2, 1974
Filing dateApr 17, 1972
Priority dateApr 17, 1972
Publication numberUS 3800792 A, US 3800792A, US-A-3800792, US3800792 A, US3800792A
InventorsKnight J Mc, J Guldalian
Original AssigneeJohnson & Johnson
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Laminated collagen film dressing
US 3800792 A
A surgical dressing that is particularly useful for the treatment of burn wounds is disclosed made from a thicker layer of a collagen compressed foam film to which has been laminated, without any adhesive, a thin continuous layer of an inert polymer material, such as polyurethane, having a moisture vapor transmission rate slightly higher than that of human skin and which preferably also contains finely divided silver metal impregnated in the collagen layer.
Previous page
Next page
Claims  available in
Description  (OCR text may contain errors)

LAMINATED COLLAGEN FILM DRESSING Inventors: James J. McKnight, Martinsville;

Jack Guldalian, Jr., Laurence Twp., Mercer County, both of NJ.

[73] Assignee: Johnson & Johnson, New

Brunswick, NJ.

[22] Filed: Apr. 17, 1972 [21] Appl. No.: 244,439

[52] U.S. Cl 128/156, l28/DIG. 8, 260/114 [51] Int. Cl A611 15/00 [58] Field of Search 128/156, 334, DIG. 8; 260/114; 264/28 [56] References Cited UNITED STATES PATENTS 3,491,760 l/l970 Braum et al. 128/334 2,194,677 3/1940 Schneiderwirth 260/14 3,471,598 10/1969 Battista 264/28 3,628,974 12/1971 Battista 128/156 3,113,568 12/1963 Robins 128/156 Primary Examiner-Richard A. Gaudet Assistant Examiner-J. Yasko Attorney, Agent, or Firm-Herbert l. Sherman [57 ABSTRACT A surgical dressing thatv is particularly useful for the treatment of burn wounds is disclosed made from a thicker layer of a collagen compressed foam film to which has been laminated, without any adhesive, a thin continuous layer of an inert polymer material,

, such as polyurethane, having a moisture vapor transmission rate slightly higher than that of human skin and which preferably also contains finely divided silver metal impregnated in the collagen layer.

7 Claims, 3 Drawing Figures LAMINATED COLLAGEN FILM DRESSING BACKGROUND AND SUMMARY OF THE INVENTION In the treatment of severe burn wounds, i.e. second and third degree burn wounds, the patient passes through a number of different treatment phases. The first phase is to clean and stabilize the wound area and control the bacterial flora at the wound site. This treatment is carried out by debridement of the wound site, maintaining an electrolyte balance and by the topical application of antibacterial medications such as silver nitrate, silver sulfadiazine and other similar medications. The wound then passes through development of a granulation bed. Once this phase of the treatment is under control, the status quo of the wound site must be maintained awaiting autografting to complete the treatment. Since in many cases a period of time will pass before autografting is possible, the maintenance of the status quo wound site, i.e. the granulation bed, is an absolute necessity. The present methods used to maintain the status quo are by the repeated applications of wet gauze dressings or by employing a temporary homograft or heterograft. The repeated application of wet dressings is not particularly satisfactory as these dressings require frequent changes within any 24-hour period and tend to add to the discomfort of the patient. Homografts and heterografts have been found to be effective, but they are not readily available.

An object of the present invention is therefore to develop a material which can be considered a substitute for a homograft or a heterograft and which will maintain the wound site, i.e. the granulation bed, in a status quo condition until an autograft becomes feasible.

The requirements for a substitute homograft or heterograft, which the dressing of the present invention meets, are the following:

1. It should be a readily available material.

2. It should be capable of being applied to the wound site so as to completely isolate the wound site from the environment.

3. It must have sufficient strength to be secured over the wound area by sutures, clips, gauze, or with adhesive bandages.

4. It must be capable of being sterilized and easily stored.

5. It must have no antigenic properties.

6. It must have a moisture vapor transmission rate which will allow the proper moisture balance in the repairing wound, i.e. to prevent both hydration and dessication of the repairing tissue.

Moisture vapor transmission rate is the weight of water lost by evaporation through a film membrane at 37C over a period of 24 hours. The weight loss is determined using a Twing Albert permeability cap in a Blue M Electric Company Model POM-203A forced air oven at 37C. The weight loss is observed periodically over a 24 to 48 hour period. This moisture vapor transmission rate figure will vary if measured by other possible procedures, and all rates described herein are those measured by the above method.

It was formerly thought that this rate should be similar to that of human skin, i.e. about 1-1.5 milligrams per hour per centimeter squared, but we have learned that the rate should be slightly higher, i.e. about 2-7 milligrams per hour per centimeter squared mglhrlcm We have developed a simple dressing that meets these requirements. Our dressing is composed of a thicker layer (that which will be placed on the skin in actual use) of reconstituted collagen formed into a compressed tanned collagen foam film to which is laminated a thinner outer layer of an inert polymer plastic material, preferably polyurethane. A greatly preferred embodiment contains finely divided silver impregnated and distributed through the collagen layer.

Our new dressing can be 3-30 mils thick and is preferably about 18 mils thick. The dressing of our invention can have a moisture vapor transmission rate of from 2 to 7 mg/hr/cm and preferably has a rate of 3 mg/hr/cm.

DISCUSSION OF PRIOR ART Collagen in various forms has been used together with various other materials in the treatment of wounds and of burns. Braun, US. Pat. No. 3,491,760, discloses a skin used in heterotransplantation which is made from two different tanned collagen gel layers. The material is used to produce a heteroplastic skin by acting as a suitable nutrient medium. The layer next to the skin has a large-celled, foamy consistency (but is not a compressed foam), and it is covered by a collagen film which is very tough, elastic, and almost leathery to prevent the drying out of the first film. The patent-teaches v the optional cementing of an adhering plastic film, such as polyvinylchloride foil, over the leathery collagen film to prevent drying out of the collagen gel. The heteroplastic skin thus formed is fairly thick (the collagen foamy layer being well over mils thick and much thicker than that which applicants use). The various layers are cemented together with adhesives. A collagen foil dressing product that appears to be made by this method has been sold in Germany. This prior art dressing appears to have a moisture vapor transmission rate different from that of the instant invention.

Battista US. Pat. No. 3,471,598 discloses freeze drying a dispersion of a microcrystalline collagen to form a mat, which can be used in various applications including surgical dressings.

British Pat. No. 1,195,062, entitled Structures Comprising Microcrystalline Collagen and Methods of Forming Them,'discloses the use of microcrystalline colloidal dispersions and gels to produce films, which may then be applied to coat various types of fibers including fibers of various organic polymers such as polyurethane.

Schulte, US. Pat. No. 2,202,566, discloses the use of collagen fibers in a bandage.

Robbins, US. Pat. No. 3,113,568, discloses the use of a polyurethane foam in a special type of bandage.

None of the art specificallydiscloses the concept of the present invention of dressing made from a particular type of collagen formed into a layer of compressed collagen foam having laminated thereto a polyurethane film which has a moisture vapor transmission slightly higher than that of skin.

Reference is now made to the drawings wherein are set forth by way of illustration and examples certain embodiments of the present invention.

Referring to the drawings:

FIG. 1 is a plan view of a microphotograph showing the top 10 (i.e. the part away from the skin in actual use) of the surgical dressing of the present invention taken at 3,000 times magnification, and it shows the outer surface of the thinner polyurethane layer 12, which contains a great many microscopic pores 14.

FIG. 2 is an inverted plan view of a microphotograph showing the bottom 20 (i.e. the part which goes next to the skin in actual use) of the surgical dressing of the present invention taken at 10,000 times magnification, and it shows the outer. surface of the thicker compressed collagen foam 22, which contains a network of collagen fibers or fibrils 24 with pores or open spaces 26 between the collagen fibers or'fibrils.

FIG. 3 is a diagrammatic cross-section view on line 3-3 from FIG. 1 showing a side view through the center of the surgical dressing of the present invention. It shows the polyurethane layer laminated to the compressed collagen foam layer 20. Also visible in FIG. 3 are the pores 14 in the polyurethane, the collagen fibers 24 and the open spaces 26 between the collagen fibers, and the particles of silver metal 28 impregnated in the collagen foam 20.

THE STARTING COLLAGEN The compressed collagen foam film used in the surgical dressing of the instant invention may be made from collagen obtained from various sources as long as it has the necessary properties hereinafter described. Bovine collagen is the most common source. In particular, we have found satisfactory results may be obtained from a commercial product which is marketed by FMC Corporation under the trademark Avitene" or very small, fine, fluffy, collagen fiber particles which are relatively soft and not degraded, made as described in US. Pat. No. 3,471,598 and other patents assigned to FMC Corporation. Other usable collagen fibers are those used in the gels from which collagen sausage casings are extruded, which have been ground or milled to the smaller, fine, fiuffy sizes used here. Bovine hide-dried, ground, or milled-can also be used to make the gel from which the compressed foam of the present invention is made.

PREPARATION OF COLLAGEN GEL The starting collagen is separated into very fine, fluffy fibers (dry to feel and touch) on the order of 25, 35, and 50 mesh size. Avitene is sold as a dry fibrous blend of finely divided collagen fibers. These are screened through various sized sieves to separate the collagen into fibers of the same relative size on the order of 25-50 mesh. While specific size and mixtures of size is not critical and smaller or larger pieces of collagen could be used, we prefer to use equal parts of several different sizes, e.g. of 25, 35, and 50 mesh, blended together. The collagen fibers are then made into an aqueous dispersion with water, which dispersion contains about 3.5 percent by weight of said collagen fibers. The dispersion is homogenized and allowed to stand. The time of standing is not critical, but we have found 1 hour to be satisfactory. Then a fast evaporating organic solvent such as petroleum ether is added to the amount of about percent by volume. The purpose of using the organic solvent is to prevent complete selfbonding of the fibers in the reconstituted product. When Avitene collagen is used, the petroleum ether is added to the initial aqueous dispersion. Where a dry collagen other than Avitene has been used, the resultant blend is then acid swollen in the well known fashion (we prefer to use 0.8 percent by weight of lactic acid, but other acids or amounts should work also) and allowed to stand. Where Avitene is used, this step is omitted since the material is already in the acid state. The fibers are swollen by the action of the lactic acid and take up the liquid present in the dispersion to form a gel. The gel is preferably permitted to stand long enough to attain equilibrium, e.g. for an hour, before being used in the next step of the process.

PREPARATION OF COLLAGEN FOAM FILM The above gel, which contains acid swollen collagen, is spread into a thick wet film on the order of about 25 to mils, preferably 50 mils thick. The thickness of this thick wet gel film can vary, of course, depending on the desired thickness of the collagen layer in the desired end product dressing. It is next desired to impart further porosity to the collagen film so it will be somewhat foamy and also to tan (i.e. to cross-link) the collagen. Various foaming agents and tanning agents could be used. We prefer to soak the wet film in a 5 percent sodium bicarbonate solution which also contains 400 parts per million or more glutaraldehyde for a period of 1 hour. The glutaraldehyde is the tanning agent. The sodium bicarbonate is used to control the porosity of the film since it introduces uniform size gas bubbles while the acid swollen film is being neutralized with bicarbonate ions.

The resultant porous collagen film which has now been neutralized with bicarbonate, has had its constituent collagen deswollen so it now has a lesser thickness about one-half its former swollen size. It is then dried, e.g. by air drying. The resultant dried porous collagen film is well rinsed with water. We prefer a rinsing time of 1 hour. The water-rinsed film is then plasticized slightly. A suitable method is by soaking in 20 percent glycerol for 15 minutes.

Because the glutaraldehyde present in the sodium bicarbonate serves as a tanning agent (cross-linking agent), the dried film contains an excess of glutaraldehyde. The wet plasticized porous collagen film is dried and is also slightly compressed, i.e. to about onequarter of its original wet thickness (referring to the gel stage), for example, by being force dried on a heated cam under slight pressure. A typical thickness of the dried compressed collagen foam film at this point is about 12.5 mils.

The compressed collagen foam has been fairly well tanned so that it will not have antigenic activity. One method of determining the sufficiency of amount of tanning is by its resistance to collagenase attack. Here resistance to collagenase attack is assayed according to a procedure described by Mandl, I. in the J. Clinical lnvestigation, 32, I323 (1953). We have found that our cross-linked collagen is essentially resistant to hydrolysis by the enzyme collagenase from Cl. histolyticum. We have reduced the ability of the enzyme to attack the collagen by greater than percent.

ADDITION OF SILVER Where the preferred embodiment is desired, i.e. the use of a fine dispersion of silver throughout the collagen film, one way of adding it is by the use of Tollens reagent; e.g. the dried compressed foam collagen film can be soaked in Tollens reagent for 5 minutes. Tollens reagent, which has the formula Ag(NH Ol-l, is a reducing agent for aldehyde groups, and it serves to oxidize the excess glutaraldehyde and also to deposit silver metal on the accessible surfaces of the collagen fibers throughout the film. The specific amount of silver deposited or impregnated is that which is equivalent to the amount of excess aldehyde which has been oxidized to carboxyl. The silver acts as an antibacterial agent and is especially effective in amounts of from 1.5 mg silver per square inch to 0.5 mg silver per square inch when applied and impregnated in the manner herein suggested.

The collagen film, after being soaked in Tollens reagent for 5 minutes, is then rinsed in water for about an hour and finally plasticized, e.g. by being soaked in 20 percent glycerol for minutes, and it is then air dried.

While there can be a fair amount of variation, a typical compressed collagen foam film formed at this point might have a density of 1.8285 grams per cubic centimeter, a porosity of 76.4 percent, and a measured pore volume of 0.608 cubic centimeters per gram (as determined in the well-known manner on a Porosimeter, the particular machine being that manufactured by the American Instrument Company as their Aminco Digital Readout Porosimeter, 15,000 PSI Motor Driven).

LAMINATION TO THIN PLASTIC FILM The plasticized compressed collagen foam film is now ready to be coated with a plasticfilm. While it is physically possible to utilize various adhesives to attach the plastic film to the collagen film, animal tests have shown the resultant dressing to be unsatisfactory since they delaminated in actual use, wherefore the plastic film used in the present invention is laminated to the collagen film without any adhesive. While this can be accomplished various ways, we have found solvent casting to be quite satisfactory, i.e. dissolving the plastic in a solvent and then cast coating the collagen film with the dissolved plastic. The plastic we prefer is polyurethane, although other plastics ought work provided they give the desired moisture vapor transmission rates (slightly higher than that of skin) and do not release toxic or irritant chemiclas to the wound bed. The particular preferred polyurethane is a thermoplastic polyurethane sold by the B. F. Goodrich Chemical Company as Tuftane packaging film and which has high elongation and excellent stretch recovery properties as well as good strength and toughness. We have used their Tuftane No. 1 1O film in 1.0 mil thickness and dissolved it in an organic solvent, such as tetrahydrofuran. A dispersion of percent polyurethane in tetrahydrofuran was found particularly suitable. This was used to coat the compressed collagen foam film using a number 60 Meyer Rod to apply five coatings. The number of coatings could vary since the real control is obtaining the desired moisture vapor transmission rate. This rate will decrease as the plastic film is made thicker.

Naturally the dressing should be sterilized before use. Cobalt irradiation is the method of choice, but other methods could be used also.

Typical examples of dressings of this invention such as illustrated in the drawings and their construction are as follows.

Example 1 Dressing With Silver Starting with the collagen sold as Avitene by FMC Corporation, an equal parts blend of 25, 35, and 50 mesh collagen fibers are made into a 3.5 percent by weight aqueous dispersion containing 15 percent by volume petroleum ether, which immediately forms a gel. The fibers in the gel are subjected to attrition for 30 seconds at high speed in a Waring-blender. The dispersion of fibers still in the gel state is allowed to standfor one hour. The resultant gel is spread into a 50 mil thick wet film. This wet film is soaked in a 5 percent sodium bicarbonate solution containing 400 ppm glutaraldehyde for 1 hour, which makes the wet film porous. The bicarbonate neutralized porous collagen film is' then air dried. The dried film is rinsed with water for 1 hour and is then soaked in 20 percent glycerol for 15 minutes. The film is then force dried on a heated cam under slight pressure using a Bessler photographic dryer which used a coarse mesh nylon belt (in place of the usual cotton belt) to provide faster heat exchange. The dried film is soaked in Tollens reagent, Ag( NH OH, for 5 minutes, rinsed in water for 1 hour, and finally soaked in 20 percent glycerol for 15 minutes. It is then air dried. The resultant dried compressed tanned collagen foam film, which is about 12-15 mils thick, is then coated 5 times (with air drying after each coat) with a dispersion of 20 percent Tuftane l 10 polyurethane in tetrahydrofuran using a No. Meyer rod, which resulted in the addition to the collagen layer of a polyurethane film about 3-5 mils thick. This was then dried. The resultant laminated film of polyurethane on a compressed foam collagen film has a moisture vapor transmission rate of about 3 mg/hr/cm The dressing was sterilized by being subjected to 2.5 megarods of cobalt irradiation and was then suitable for use as a surgical dressing, particularly for burns.

The above dressing was tested on a Aminco Porosimeter and the collagen portion was found to have a porosity of 75.7 percent, of which 51 percent was from pores having pore diameters larger than 95.264 microns, and the other 24.7 percent was fairly well distributed among a very wide range of smaller pores, e.g. 6.3 percent was from pores ranging from 14.71 down to 10.13 microns, and there were 0.2 percent pores as small as 0.0160.013 microns. This indicates a welldistributed porous collagen structure with varying size pores.

Example 2 Dressing Without Silver Example 1 was repeated except that no silver metal was impregnated in the collagen layer, i.e. the step of soaking in Tollens reagent was omitted. The resultant dressing was substantially identical to that of Example 1 except that it does not contain any silver.

The bacteriostatic activity advantage of the silverimpregnated dressing of Example 1 over the non-silver dressing of Example 2 is unexpectedly high and is demonstrated dramatically by a zone of inhibition microbiological test procedure wherein a culture is made from beef serum containing some 6,000 viable cells of Pseudomonas aeruginosa, which has been incubated and placed on an agar plate, and 1 inch discs of the dressing of Example 1 and of the dressing of Example 2 are placed, collagen side down, on the surface of the agar. The zone of inhibition for the Example I silver-- containing dressing disc was 32.3 mm. while that for the Example 2 non-silver impregnated dressing disc was 0.

RELATED UNSUCCESSFUL PRODUCTS Similar materials to those used in the dressing of our invention have been used by us in dressings made by different constructions, for example, through the use of adhesives, and these have failed because of delamination in animal tests. Collagen films have also been made by us as dense continuous sheets which were de-aired in the gel state before they were cast into a film and so lacked the porosity of the present collagen film. These nonporous collagen films failed in critical tests on certain species of experimental animals although they appeared satisfactory on other species of animals.

The dressings of the present invention have been successfully evaluated on a number of different experimental animals. The dressings were evaluated on full thickness skin injuries using rats and rabbits. Dressings were applied and the healing response was observed over a 4-7 day period. The results indicated a wound bed suitable for grafting.

The dressings of the present invention are elastic, pliable, flexible, soft, and have the ability when wet out to conform to the topography of the wound site.

Particular embodiments of the invention have been used to illustrate the same. The invention, however, is not limited to these specific embodiments. In view of the foregoing disclosure, variations or modifications thereof will be apparent, and it is intended to include within the invention all such variations and modifications except as do not come within the scope of the appended claims.

We claim:

. l. A pliable, surgical dressing especially useful in the treatment of burns, comprising a thicker layer of a compressed, tanned collagen foam film and laminated to one surface of said compressed foam, a thinner layer of plastic film having a moisture vapor transmission rate from 2-7 mglhr/cm 2. The dressing of claim 1 wherein the plastic film is polyurethane.

3. The dressing 'of claim 1 wherein the compressed collagen foam layer is 3-30 mils thick.

4. A pliable, surgical dressing especially useful in the treatment of burns, comprising a thicker layer of compressed, tanned collagen foam film having silver metal impregnated therein and laminated to one surface of said compressed foam, an outer thinner layer of plastic film having a moisture vapor transmission rate from 2-7 mg/hr/cm 5. The dressing of claim 4 wherein the plastic film is polyurethane.

6. The dressing of claim 4 wherein the amount of silver metal is from 0.5-1.5 mg silver per square inch of collagen film.

7. The dressing of claim 4 wherein the compressed collagen foam layer is 3-30 mils thick.

Patent Citations
Cited PatentFiling datePublication dateApplicantTitle
US2194677 *Dec 19, 1938Mar 26, 1940Herman J SchneiderwirthSilver animal mucin and process for producing same
US2272728 *Jan 13, 1941Feb 10, 1942Sam RosenzweigProcess for imparting bactericidal and sterilizing properties to natural sponges
US2785153 *Sep 13, 1954Mar 12, 1957Crookes Barnes Lab IncSilver protein
US2785154 *Sep 13, 1954Mar 12, 1957Crookes Barnes Lab IncProcess of producing a stable silver protein composition
US2858830 *Oct 1, 1956Nov 4, 1958Frank C LoweSurgical dressing
US3113568 *Dec 26, 1961Dec 10, 1963Eric K ErskineStyptic bandage
US3471598 *Feb 14, 1966Oct 7, 1969Fmc CorpMethod of producing absorbent mats
US3491760 *Jul 6, 1966Jan 27, 1970Braun Intern Gmbh BWound coverings
US3628974 *Feb 9, 1970Dec 21, 1971Fmc CorpMicrocrystalline collagen, an ionizable partial salt of collagen and foods, pharmaceuticals and cosmetics containing same
GB1195062A * Title not available
Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US3896802 *Apr 19, 1974Jul 29, 1975American Cyanamid CoFlexible flocked dressing
US3903882 *Apr 19, 1974Sep 9, 1975American Cyanamid CoComposite dressing
US3949742 *Sep 20, 1974Apr 13, 1976Frigitronics, Inc.Medical dressing
US4060081 *Jul 15, 1975Nov 29, 1977Massachusetts Institute Of TechnologyMultilayer membrane useful as synthetic skin
US4233969 *Nov 10, 1977Nov 18, 1980Lock Peter MWound dressing materials
US4306563 *Nov 28, 1979Dec 22, 1981Firma Pfrimmer & Co. Pharmazeutische Werke Erlangen GmbhCatheter for introduction into body cavities
US4505266 *Apr 17, 1984Mar 19, 1985Massachusetts Institute Of TechnologyMethod of using a fibrous lattice
US4554317 *Oct 6, 1983Nov 19, 1985David BeharSynthetic wound covering
US4703108 *Mar 26, 1986Oct 27, 1987University Of Medicine & Dentistry Of New JerseyBiodegradable matrix and methods for producing same
US4728323 *Jul 24, 1986Mar 1, 1988Minnesota Mining And Manufacturing CompanyAntimicrobial wound dressings
US4759354 *Nov 26, 1986Jul 26, 1988The Kendall CompanyWound dressing
US4837285 *Sep 8, 1987Jun 6, 1989MedimatrixCollagen matrix beads for soft tissue repair
US4846164 *Aug 7, 1987Jul 11, 1989Martz Joel DVapor permeable dressing
US4847049 *Mar 20, 1987Jul 11, 1989Vitaphore CorporationMethod of forming chelated collagen having bactericidal properties
US4991574 *Aug 15, 1990Feb 12, 1991Dow Corning CorporationSurgical dressing
US4997425 *Mar 29, 1990Mar 5, 1991Nippon Zeon Co., Ltd.Wound dressing
US5061258 *Apr 3, 1990Oct 29, 1991Martz Joel DVapor permeable dressing with releasable medication
US5149469 *Mar 26, 1991Sep 22, 1992Nippon Zeon Co., Ltd.Heating, freeze drying
US5196185 *Sep 11, 1989Mar 23, 1993Micro-Collagen Pharmaceutics, Ltd.Collagen-based wound dressing and method for applying same
US5298015 *Mar 20, 1992Mar 29, 1994Nippon Zeon Co., Ltd.Wound dressing having a porous structure
US5514657 *Nov 8, 1994May 7, 1996Yissum Research Development Company Of The Hebrew UniversityWound healing, silver sulfadiazine, collagen
US5516395 *Dec 23, 1993May 14, 1996Lts Lohmann Therapie-Systeme Gmbh & Co. KgProcess for the production of collagen foams in the form of continuous tapes and their use in medicine, cosmetics and hygiene
US5554106 *Oct 13, 1994Sep 10, 1996Quinton Instrument CompanyHydrocolloid exit site dressing
US5569207 *Oct 13, 1994Oct 29, 1996Quinton Instrument CompanyHydrocolloid dressing
US5593395 *Sep 6, 1994Jan 14, 1997Martz; Joel D.For use on human and animal skin
US5676967 *Apr 18, 1995Oct 14, 1997Brennen Medical, Inc.Polyester mesh netting, coating of mixture of beta-glucan and a collagen, polymeric film comprising high vapor permeable material
US5709934 *Nov 22, 1994Jan 20, 1998Tissue Engineering, Inc.Bipolymer foams having extracellular matrix particulates
US5814094 *Mar 28, 1996Sep 29, 1998Becker; Robert O.Iontopheretic system for stimulation of tissue healing and regeneration
US5814328 *Jan 13, 1997Sep 29, 1998Gunasekaran; SubramanianPreparation of collagen using papain and a reducing agent
US5868778 *May 5, 1997Feb 9, 1999Vascular Solutions, Inc.Vascular sealing apparatus and method
US5891558 *Nov 21, 1996Apr 6, 1999Tissue Engineering, Inc.Biopolymer foams for use in tissue repair and reconstruction
US5948429 *Nov 16, 1995Sep 7, 1999Tissue Engineering, Inc.Methods for preparing biopolymer foams
US5957952 *Mar 31, 1997Sep 28, 1999Vascular Solutions, Inc.Vascular sealing device
US6007563 *Oct 7, 1998Dec 28, 1999Kensey Nash CorporationMethod of deploying percutaneous puncture closure
US6017359 *Jun 17, 1997Jan 25, 2000Vascular Solutions, Inc.Vascular sealing apparatus
US6022557 *Oct 10, 1997Feb 8, 2000Naturin Gmbh & Co.Material on the basis of collagen fibers for covering wounds
US6080490 *Nov 3, 1997Jun 27, 2000Westaim Technologies Inc.Biologically dynamic environment; alloy
US6103369 *May 21, 1992Aug 15, 20003M Innovative Properties CompanyPolymeric backing layer, high moisture vapor transmission layer, and skin contacting adhesive layer wherein said high moisture vapor transmission layer is a polymeric film backing material that has a high moisture vapor transmission rate
US6153292 *Mar 30, 1999Nov 28, 2000Tissue Engineering, Inc.Biopolymer foams for use in tissue repair and reconstruction
US6296658Jan 25, 2000Oct 2, 2001Vascular Solutions, Inc.Vascular sealing apparatus
US6365220Jan 7, 2000Apr 2, 2002Nucryst Pharmaceuticals Corp.Layer of antimicrobial active metal element, layer of second element being electrochemically nobler than the first, first element releases ions of the metal element when an electrolyte containing biological fluid is brought into contact
US6548077Oct 3, 2000Apr 15, 2003Subramanian GunasekaranPurifying type I collagen using two papain treatments and reducing and delipidation agents
US6582713Mar 30, 2001Jun 24, 2003Univ. Of Colorado - Colorado SpringsCompositions and methods for promoting wound healing
US6680113Feb 10, 2000Jan 20, 20043M Innovative Properties CompanyPolymeric backing layer, moisture vapor transmission layer and skin contacting adhesive layer
US6692773Jul 27, 2001Feb 17, 2004Nucryst Pharmaceuticals Corp.Treatment of hyperproliferative skin disorders and diseases
US6719987Apr 16, 2001Apr 13, 2004Nucryst Pharmaceuticals Corp.Sustained release of metal microbiocides
US6723350Apr 23, 2002Apr 20, 2004Nucryst Pharmaceuticals Corp.Powder of one or more antimicrobial metals formed with atomic disorder; coating becomes antimicrobial and anti-inflammatory when wet.
US6861570Mar 21, 2000Mar 1, 2005A. Bart FlickMultilayer conductive appliance having wound healing and analgesic properties
US6939568Apr 23, 2002Sep 6, 2005Nucryst Pharmaceuticals Corp.Hydrated dressing containing metal microbiocide
US6989156Apr 23, 2002Jan 24, 2006Nucryst Pharmaceuticals Corp.Forming a free- standing powder comprising at least one antimicrobial metal with atomic disorder; and injecting the free-standing powder in therapeutically effective amounts to the tissue which is to be treated
US6989157Oct 22, 2002Jan 24, 2006Nucryst Pharmaceuticals Corp.Microbiocides; bactericides; antiinflammatory agents; fungicides; viricides
US7001617May 30, 2002Feb 21, 2006Nueryst Pharmaceuticals Corp.Method of induction of apoptosis and inhibition of matrix metalloproteinases using antimicrobial metals
US7005556Sep 3, 1996Feb 28, 2006Argentum MedicalMultilayer wound dressing
US7008647Apr 23, 2001Mar 7, 2006Nucryst Pharmaceuticals Corp.Treatment of acne
US7041868Dec 19, 2001May 9, 2006Kimberly-Clark Worldwide, Inc.First bioabsorbable, porous layer as scaffold for cell attachment and proliferation, and a second layer of an absorbent, gel forming material that serves as barrier to cell adhesion and penetration
US7078060Feb 12, 2003Jul 18, 2006Nucryst Pharmaceuticals Corp.Contacting an area with a solution of atomically disordered, nanocrystalline metal, metal alloy or metal compound; drug delivery; microbiocides; bactericides; fungicides; anticarcinogenic, -tumor and -inflammatory agents; viricides
US7087249Apr 23, 2002Aug 8, 2006Nucryst Pharmaceuticals Corp.Nanocrystalline antimicrobial metals (noble metals)formed with atomic disorder are capable of releasing highly active clusters of the antimicrobial metal sufficient to cause microbiocidal effect; anti-inflammatory activity
US7137968Mar 13, 2000Nov 21, 2006Nucryst Pharmaceuticals Corp.Transcutaneous medical device dressings and method of use
US7157614Dec 21, 2001Jan 2, 2007Fountainhead, LlcLayer of polymeric gel block copolymer and mineral oil, and a second layer containing bactericidal silver metal in nylon fabric; dentistry, periodontal disease; appliances for mouth, nose, or other body cavity; bite blocks or plates, caps, braces
US7201925Feb 2, 2004Apr 10, 2007Nueryst Pharmaceuticals Corp.Treatment of ungual and subungual diseases
US7214847Jul 11, 2000May 8, 2007Argentum Medical, L.L.C.Multilayer conductive appliance having wound healing and analgesic properties
US7230153Apr 29, 2005Jun 12, 2007Argentum International, LlcDressing for a living organism of a layer of conformable, conductive fabric of a biologically inert polymer uniformly coated with a metal or a metal alloy; dressing alters the electrodynamic processes with the pathologic condition to promote healing and pain relief when placed on periphery of wound
US7255881Oct 22, 2003Aug 14, 2007Nucryst Pharmaceuticals Corp.For therapy of undesirable skin conditions
US7285576Mar 12, 2003Oct 23, 20073M Innovative Properties Co.Absorbent polymer compositions, medical articles, and methods
US7291762Sep 11, 2003Nov 6, 2007Argentum International, LlcMultilayer conductive appliance having wound healing and analgesic properties
US7358284Jan 20, 2005Apr 15, 2008Lifecell CorporationParticulate acellular tissue matrix
US7427416Oct 22, 2003Sep 23, 2008Nucryst Pharmaceuticals Corp.Methods of treating conditions using metal-containing materials
US7429241Sep 29, 2005Sep 30, 2008Codman & Shurtleff, Inc.Dural graft and method of preparing the same
US7470437Nov 10, 2004Dec 30, 2008Nucryst Pharmaceuticals Corp.Utilizing nanocrystalline silver metal, alloy or compound for mucosal, serosal, respiratory, circulatory and/or musculo-skeletal conditions
US7517536Feb 3, 2006Apr 14, 2009Feng Chia UniversityFlexible base layer coated with silver, gold, palladium, platinum, copper, and/or zinc supported on activated carbon powder, activated carbon particle, and/or activated carbon fiber
US7662409Feb 28, 2001Feb 16, 2010Gel-Del Technologies, Inc.Biocompatible protein materials compressed with one or more biocompatible solvents to remove bulk solvent and form an interacting protein matrix material.
US7732655Dec 6, 2002Jun 8, 2010Systagenix Wound Management (Us), Inc.Controlled release therapeutic wound dressings
US7745509Dec 5, 2003Jun 29, 20103M Innovative Properties CompanyPolymer compositions with bioactive agent, medical articles, and methods
US7777090Oct 23, 2003Aug 17, 2010Biopol Co., Ltd.Polyurethane foam dressing for wound filler and method for manufacturing thereof
US7777091 *Jan 26, 2007Aug 17, 2010Biopol Co., Ltd.Hydrophilic dressing material in which a wound contact layer, having a sponge structure composed of multiple open cells and pores that make a tunnel from cell to cell, is laminated with a protective film
US7867510Sep 7, 2006Jan 11, 2011BioLargo Life Technologies, IncMaterial having antimicrobial activity when wet
US7989674Oct 30, 2007Aug 2, 2011Argentum Medical, LlcMultilayer conductive appliance having wound healing and analgesic properties
US8029774 *Jul 1, 2006Oct 4, 2011University Of PittsburghWound healing polymeric networks
US8039591Apr 21, 2009Oct 18, 2011Codman & Shurtleff, Inc.Flowable collagen material for dural closure
US8057818 *Jan 26, 2005Nov 15, 2011Cryolife, Inc.Methods of making expandable foam-like biomaterials
US8071124 *Jan 26, 2005Dec 6, 2011Cryolife, Inc.Methods of using expandable foam-like biomaterials
US8071135Oct 4, 2007Dec 6, 2011Anthrogenesis CorporationPlacental tissue compositions
US8093444May 7, 2007Jan 10, 2012Argentum Medical, LlcMultilayer conductive appliance having wound healing and analgesic properties
US8105634Aug 15, 2007Jan 31, 2012Anthrogenesis CorporationMammalian membrane ; dry flat or tube; shaping to fit body structure; isolation, decellularization
US8118791Oct 31, 2007Feb 21, 2012Argentum Medical, LlcMedical device
US8177931Nov 8, 2006May 15, 2012Molnlycke Health Care AbMethod for perforating heat meltable material
US8192764Jan 10, 2007Jun 5, 20123M Innovative Properties CompanySilver-containing antimicrobial articles and methods of manufacture
US8193267May 19, 2010Jun 5, 20123M Innovative Properties CompanyPolymer compositions with bioactive agent, medical articles, and methods
US8226964Jan 18, 2008Jul 24, 2012Biolargo Life Technologies, Inc.Systems and methods for cleaning liquid carriers related applications data
US8269058Jul 16, 2008Sep 18, 2012Hemcon Medical Technologies, Inc.Absorbable tissue dressing assemblies, systems, and methods formed from hydrophilic polymer sponge structures such as chitosan
US8283513Sep 6, 2005Oct 9, 2012Argentum Medical, LlcMultilayer wound dressing
US8293964Oct 29, 2007Oct 23, 2012Argentum Medical, LlcMultilayer laminate wound dressing
US8313474Dec 17, 2007Nov 20, 2012Hemcon Medical Technologies, Inc.Method for preparing a compressed wound dressing
US8399027Jan 13, 2006Mar 19, 20133M Innovative Properties CompanySilver coatings and methods of manufacture
US8449514Oct 29, 2007May 28, 2013Argentum Medical, LlcConductive wound dressings and methods of use
US8455710 *Apr 23, 2003Jun 4, 2013Argentum Medical, LlcMultilayer dressing containing absorber layer; controlling moisture; microbiocide barrier
US8465537Jun 17, 2004Jun 18, 2013Gel-Del Technologies, Inc.Encapsulated or coated stent systems
US8529939Dec 8, 2004Sep 10, 2013Gel-Del Technologies, Inc.Purified protein(s) combined with drug(s) and biocompatible solvent(s) to form a coatable mixture; reduction to form a cohesive body or solidified cohesive mass that is formed into a mucoadhesive device havinghomogenous distribution; ovalbumin combined with glycerol; bonding strength
US8574610Jan 10, 2011Nov 5, 2013Biolargo Life Technologies, Inc.Material having antimicrobial activity when wet
US8623393Apr 29, 2003Jan 7, 2014Gel-Del Technologies, Inc.Biomatrix structural containment and fixation systems and methods of use thereof
US8668924Oct 18, 2010Mar 11, 2014Providence Health System—OregonWound dressing and method for controlling severe, life-threatening bleeding
US8741335Jul 13, 2006Jun 3, 2014Hemcon Medical Technologies, Inc.Hemostatic compositions, assemblies, systems, and methods employing particulate hemostatic agents formed from hydrophilic polymer foam such as Chitosan
US8795710Aug 22, 2008Aug 5, 2014Codman & Shurtleff, Inc.Collagen device and method of preparing the same
US8801681Oct 21, 2005Aug 12, 2014Argentum Medical, LlcMedical device
US8821857Aug 18, 2011Sep 2, 2014Anthrogenesis CorporationHuman placental collagen compositions and methods of making and using the same
US20050147690 *Oct 12, 2004Jul 7, 2005Masters David B.Biocompatible purified proteins combined with biocompatible solvent(s) to form a cohesive body that is subsequently solidified and processed into particles; may also include drugs or adjuvants; biointegration and remodeling by host tissue; structural scaffold; moldability; mimetics; drug delivery
DE4227681A1 *Aug 21, 1992Feb 24, 1994Becker & Co NaturinwerkWundabdeckungsmaterial auf der Basis von Kollagenfasern
DE202011100392U1May 7, 2011Jun 9, 2011Neubauer, Norbert, 38820Brandwundenauflage
EP0006714A1 *Jun 13, 1979Jan 9, 1980Johnson & JohnsonBalanced environment wound dressing
EP0068777A2 *Jun 21, 1982Jan 5, 1983Minnesota Mining And Manufacturing CompanyComposite wound dressing
EP0167828A1 *Jun 4, 1985Jan 15, 1986Koken Co. Ltd.A man-made skin composed of two layers:Collagen and a poly-alpha-amino acid
EP0227955A2 *Jul 20, 1983Jul 8, 1987University of StrathclydeComposite wound dressing
EP0371736A2 *Nov 28, 1989Jun 6, 1990Mitsubishi Kasei CorporationWound covering
EP0422046A1 *May 10, 1989Apr 17, 1991Kensey Nash CorpDevice for sealing percutaneous puncture in a vessel.
EP0431479A1 *Nov 30, 1990Jun 12, 1991Hoechst Japan LimitedWound surface-covering sheets
EP0653214A1 *Nov 10, 1994May 17, 1995YISSUM RESEARCH DEVELOPMENT COMPANY of the Hebrew University of JerusalemTopical antibacterial preparation
EP0666082A1 *Feb 3, 1995Aug 9, 1995Pharmalett International B.V.Laminate for treating wounds
EP1435911A1 *Feb 1, 2002Jul 14, 2004Gel-Del Technologies, Inc.Devices including protein matrix materials and methods of making and using same
EP1864634A2Sep 22, 1998Dec 12, 2007Argentum International, LLCMultilayer conductive appliance having wound healing and analgesic properties
EP2315555A2 *Jul 27, 2009May 4, 2011Manuela SingerReusable medical protective clothing for pets and farm animals after surgeries and with skin diseases
EP2316524A1Sep 22, 1998May 4, 2011Argentum International, LLCMultilayer conductive appliance having wound healing and analgesic properties
EP2664341A2Oct 9, 2007Nov 20, 2013Anthrogenesis CorporationNative (telopeptide) placental collagen compositions
EP2664342A2Oct 9, 2007Nov 20, 2013Anthrogenesis CorporationNative (telopeptide) placental collagen compositions
EP2700309A1Mar 26, 2003Feb 26, 2014Anthrogenesis CorporationCollagen biofabric and methods of preparation and use therefor
EP2702871A1Mar 26, 2003Mar 5, 2014Anthrogenesis CorporationCollagen biofabric and methods of preparation and use therefor
WO2003047643A1 *Dec 6, 2002Jun 12, 2003Breda Mary CullenControlled release therapeutic wound dressings
WO2003099230A2 *May 28, 2003Dec 4, 2003Gary L BowlinElectroprocessed collagen and tissue engineering
WO2008065329A2 *Oct 23, 2007Jun 5, 2008Ethicon IncProtein sheet material
WO2013135478A1 *Feb 26, 2013Sep 19, 2013Aap Biomaterials GmbhAntibacterial sheet material that can be used as a wound dressing and method for producing same
U.S. Classification602/50, 530/356, 602/58, 128/DIG.800
International ClassificationA61L15/42, A61L15/32, A61L15/26
Cooperative ClassificationY10S128/08, A61L15/26, A61L15/325, A61L15/425
European ClassificationA61L15/26, A61L15/42E, A61L15/32A