|Publication number||US3800792 A|
|Publication date||Apr 2, 1974|
|Filing date||Apr 17, 1972|
|Priority date||Apr 17, 1972|
|Publication number||US 3800792 A, US 3800792A, US-A-3800792, US3800792 A, US3800792A|
|Inventors||Knight J Mc, J Guldalian|
|Original Assignee||Johnson & Johnson|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (10), Referenced by (228), Classifications (14)|
|External Links: USPTO, USPTO Assignment, Espacenet|
LAMINATED COLLAGEN FILM DRESSING Inventors: James J. McKnight, Martinsville;
Jack Guldalian, Jr., Laurence Twp., Mercer County, both of NJ.
 Assignee: Johnson & Johnson, New
 Filed: Apr. 17, 1972  Appl. No.: 244,439
 U.S. Cl 128/156, l28/DIG. 8, 260/114  Int. Cl A611 15/00  Field of Search 128/156, 334, DIG. 8; 260/114; 264/28  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.
. 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.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2194677 *||Dec 19, 1938||Mar 26, 1940||Herman J Schneiderwirth||Silver animal mucin and process for producing same|
|US2272728 *||Jan 13, 1941||Feb 10, 1942||Sam Rosenzweig||Process for imparting bactericidal and sterilizing properties to natural sponges|
|US2785153 *||Sep 13, 1954||Mar 12, 1957||Crookes Barnes Lab Inc||Silver protein|
|US2785154 *||Sep 13, 1954||Mar 12, 1957||Crookes Barnes Lab Inc||Process of producing a stable silver protein composition|
|US2858830 *||Oct 1, 1956||Nov 4, 1958||Frank C Lowe||Surgical dressing|
|US3113568 *||Dec 26, 1961||Dec 10, 1963||Eric K Erskine||Styptic bandage|
|US3471598 *||Feb 14, 1966||Oct 7, 1969||Fmc Corp||Method of producing absorbent mats|
|US3491760 *||Jul 6, 1966||Jan 27, 1970||Braun Intern Gmbh B||Wound coverings|
|US3628974 *||Feb 9, 1970||Dec 21, 1971||Fmc Corp||Microcrystalline collagen, an ionizable partial salt of collagen and foods, pharmaceuticals and cosmetics containing same|
|GB1195062A *||Title not available|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3896802 *||Apr 19, 1974||Jul 29, 1975||American Cyanamid Co||Flexible flocked dressing|
|US3903882 *||Apr 19, 1974||Sep 9, 1975||American Cyanamid Co||Composite dressing|
|US3949742 *||Sep 20, 1974||Apr 13, 1976||Frigitronics, Inc.||Medical dressing|
|US4060081 *||Jul 15, 1975||Nov 29, 1977||Massachusetts Institute Of Technology||Multilayer membrane useful as synthetic skin|
|US4233969 *||Nov 10, 1977||Nov 18, 1980||Lock Peter M||Wound dressing materials|
|US4306563 *||Nov 28, 1979||Dec 22, 1981||Firma Pfrimmer & Co. Pharmazeutische Werke Erlangen Gmbh||Catheter for introduction into body cavities|
|US4505266 *||Apr 17, 1984||Mar 19, 1985||Massachusetts Institute Of Technology||Method of using a fibrous lattice|
|US4554317 *||Oct 6, 1983||Nov 19, 1985||David Behar||Synthetic wound covering|
|US4703108 *||Mar 26, 1986||Oct 27, 1987||University Of Medicine & Dentistry Of New Jersey||Biodegradable matrix and methods for producing same|
|US4728323 *||Jul 24, 1986||Mar 1, 1988||Minnesota Mining And Manufacturing Company||Antimicrobial wound dressings|
|US4759354 *||Nov 26, 1986||Jul 26, 1988||The Kendall Company||Wound dressing|
|US4837285 *||Sep 8, 1987||Jun 6, 1989||Medimatrix||Collagen matrix beads for soft tissue repair|
|US4846164 *||Aug 7, 1987||Jul 11, 1989||Martz Joel D||Vapor permeable dressing|
|US4847049 *||Mar 20, 1987||Jul 11, 1989||Vitaphore Corporation||Method of forming chelated collagen having bactericidal properties|
|US4991574 *||Aug 15, 1990||Feb 12, 1991||Dow Corning Corporation||Surgical dressing|
|US4997425 *||Mar 29, 1990||Mar 5, 1991||Nippon Zeon Co., Ltd.||Wound dressing|
|US5061258 *||Apr 3, 1990||Oct 29, 1991||Martz Joel D||Vapor permeable dressing with releasable medication|
|US5149469 *||Mar 26, 1991||Sep 22, 1992||Nippon Zeon Co., Ltd.||Method of manufacturing a wound dressing|
|US5196185 *||Sep 11, 1989||Mar 23, 1993||Micro-Collagen Pharmaceutics, Ltd.||Collagen-based wound dressing and method for applying same|
|US5298015 *||Mar 20, 1992||Mar 29, 1994||Nippon Zeon Co., Ltd.||Wound dressing having a porous structure|
|US5514657 *||Nov 8, 1994||May 7, 1996||Yissum Research Development Company Of The Hebrew University||Topical antibacterial preparation|
|US5516395 *||Dec 23, 1993||May 14, 1996||Lts Lohmann Therapie-Systeme Gmbh & Co. Kg||Process for the production of collagen foams in the form of continuous tapes and their use in medicine, cosmetics and hygiene|
|US5554106 *||Oct 13, 1994||Sep 10, 1996||Quinton Instrument Company||Hydrocolloid exit site dressing|
|US5569207 *||Oct 13, 1994||Oct 29, 1996||Quinton Instrument Company||Hydrocolloid dressing|
|US5593395 *||Sep 6, 1994||Jan 14, 1997||Martz; Joel D.||Vapor permeable dressing|
|US5676967 *||Apr 18, 1995||Oct 14, 1997||Brennen Medical, Inc.||Mesh matrix wound dressing|
|US5709934 *||Nov 22, 1994||Jan 20, 1998||Tissue Engineering, Inc.||Bipolymer foams having extracellular matrix particulates|
|US5814094 *||Mar 28, 1996||Sep 29, 1998||Becker; Robert O.||Iontopheretic system for stimulation of tissue healing and regeneration|
|US5814328 *||Jan 13, 1997||Sep 29, 1998||Gunasekaran; Subramanian||Preparation of collagen using papain and a reducing agent|
|US5868778 *||May 5, 1997||Feb 9, 1999||Vascular Solutions, Inc.||Vascular sealing apparatus and method|
|US5891558 *||Nov 21, 1996||Apr 6, 1999||Tissue Engineering, Inc.||Biopolymer foams for use in tissue repair and reconstruction|
|US5948429 *||Nov 16, 1995||Sep 7, 1999||Tissue Engineering, Inc.||Methods for preparing biopolymer foams|
|US5957952 *||Mar 31, 1997||Sep 28, 1999||Vascular Solutions, Inc.||Vascular sealing device|
|US6007563 *||Oct 7, 1998||Dec 28, 1999||Kensey Nash Corporation||Method of deploying percutaneous puncture closure|
|US6017359 *||Jun 17, 1997||Jan 25, 2000||Vascular Solutions, Inc.||Vascular sealing apparatus|
|US6022557 *||Oct 10, 1997||Feb 8, 2000||Naturin Gmbh & Co.||Material on the basis of collagen fibers for covering wounds|
|US6080490 *||Nov 3, 1997||Jun 27, 2000||Westaim Technologies Inc.||Actively sterile surfaces|
|US6103369 *||May 21, 1992||Aug 15, 2000||3M Innovative Properties Company||Multi-layered dressing|
|US6153292 *||Mar 30, 1999||Nov 28, 2000||Tissue Engineering, Inc.||Biopolymer foams for use in tissue repair and reconstruction|
|US6296658||Jan 25, 2000||Oct 2, 2001||Vascular Solutions, Inc.||Vascular sealing apparatus|
|US6365220||Jan 7, 2000||Apr 2, 2002||Nucryst Pharmaceuticals Corp.||Process for production of actively sterile surfaces|
|US6548077||Oct 3, 2000||Apr 15, 2003||Subramanian Gunasekaran||Purifying type I collagen using two papain treatments and reducing and delipidation agents|
|US6582713||Mar 30, 2001||Jun 24, 2003||Univ. Of Colorado - Colorado Springs||Compositions and methods for promoting wound healing|
|US6680113||Feb 10, 2000||Jan 20, 2004||3M Innovative Properties Company||Multi-layered dressing|
|US6692773||Jul 27, 2001||Feb 17, 2004||Nucryst Pharmaceuticals Corp.||Treatment of hyperproliferative skin disorders and diseases|
|US6719987||Apr 16, 2001||Apr 13, 2004||Nucryst Pharmaceuticals Corp.||Antimicrobial bioabsorbable materials|
|US6723350||Apr 23, 2002||Apr 20, 2004||Nucryst Pharmaceuticals Corp.||Lubricious coatings for substrates|
|US6861570||Mar 21, 2000||Mar 1, 2005||A. Bart Flick||Multilayer conductive appliance having wound healing and analgesic properties|
|US6939568||Apr 23, 2002||Sep 6, 2005||Nucryst Pharmaceuticals Corp.||Treatment of inflammatory skin conditions|
|US6989156||Apr 23, 2002||Jan 24, 2006||Nucryst Pharmaceuticals Corp.||Therapeutic treatments using the direct application of antimicrobial metal compositions|
|US6989157||Oct 22, 2002||Jan 24, 2006||Nucryst Pharmaceuticals Corp.||Dry powders of metal-containing compounds|
|US7001617||May 30, 2002||Feb 21, 2006||Nueryst Pharmaceuticals Corp.||Method of induction of apoptosis and inhibition of matrix metalloproteinases using antimicrobial metals|
|US7005556||Sep 3, 1996||Feb 28, 2006||Argentum Medical||Multilayer wound dressing|
|US7008647||Apr 23, 2001||Mar 7, 2006||Nucryst Pharmaceuticals Corp.||Treatment of acne|
|US7041868||Dec 19, 2001||May 9, 2006||Kimberly-Clark Worldwide, Inc.||Bioabsorbable wound dressing|
|US7078060||Feb 12, 2003||Jul 18, 2006||Nucryst Pharmaceuticals Corp.||Solutions and aerosols of metal-containing compounds|
|US7087249||Apr 23, 2002||Aug 8, 2006||Nucryst Pharmaceuticals Corp.||Treatment of mucosal membranes|
|US7137968||Mar 13, 2000||Nov 21, 2006||Nucryst Pharmaceuticals Corp.||Transcutaneous medical device dressings and method of use|
|US7157614||Dec 21, 2001||Jan 2, 2007||Fountainhead, Llc||Treatment devices providing targeted antimicrobial action|
|US7201925||Feb 2, 2004||Apr 10, 2007||Nueryst Pharmaceuticals Corp.||Treatment of ungual and subungual diseases|
|US7214847||Jul 11, 2000||May 8, 2007||Argentum Medical, L.L.C.||Multilayer conductive appliance having wound healing and analgesic properties|
|US7230153||Apr 29, 2005||Jun 12, 2007||Argentum International, Llc||Multilayer conductive appliance having wound healing and analgesic properties|
|US7255881||Oct 22, 2003||Aug 14, 2007||Nucryst Pharmaceuticals Corp.||Metal-containing materials|
|US7285576||Mar 12, 2003||Oct 23, 2007||3M Innovative Properties Co.||Absorbent polymer compositions, medical articles, and methods|
|US7291762||Sep 11, 2003||Nov 6, 2007||Argentum International, Llc||Multilayer conductive appliance having wound healing and analgesic properties|
|US7358284||Jan 20, 2005||Apr 15, 2008||Lifecell Corporation||Particulate acellular tissue matrix|
|US7427416||Oct 22, 2003||Sep 23, 2008||Nucryst Pharmaceuticals Corp.||Methods of treating conditions using metal-containing materials|
|US7429241||Sep 29, 2005||Sep 30, 2008||Codman & Shurtleff, Inc.||Dural graft and method of preparing the same|
|US7470437||Nov 10, 2004||Dec 30, 2008||Nucryst Pharmaceuticals Corp.||Methods of treating conditions with a metal-containing material|
|US7517536||Feb 3, 2006||Apr 14, 2009||Feng Chia University||Antimicrobial compositions and wound dressings|
|US7662409||Feb 28, 2001||Feb 16, 2010||Gel-Del Technologies, Inc.||Protein matrix materials, devices and methods of making and using thereof|
|US7732655||Dec 6, 2002||Jun 8, 2010||Systagenix Wound Management (Us), Inc.||Controlled release therapeutic wound dressings|
|US7745509||Dec 5, 2003||Jun 29, 2010||3M Innovative Properties Company||Polymer compositions with bioactive agent, medical articles, and methods|
|US7777090||Oct 23, 2003||Aug 17, 2010||Biopol Co., Ltd.||Polyurethane foam dressing for wound filler and method for manufacturing thereof|
|US7777091 *||Jan 26, 2007||Aug 17, 2010||Biopol Co., Ltd.||Polyurethane foam dressing with improved moisturization|
|US7867510||Jan 11, 2011||BioLargo Life Technologies, Inc||Material having antimicrobial activity when wet|
|US7989674||Oct 30, 2007||Aug 2, 2011||Argentum Medical, Llc||Multilayer conductive appliance having wound healing and analgesic properties|
|US8029774 *||Oct 4, 2011||University Of Pittsburgh||Wound healing polymeric networks|
|US8039591||Oct 18, 2011||Codman & Shurtleff, Inc.||Flowable collagen material for dural closure|
|US8057818 *||Nov 15, 2011||Cryolife, Inc.||Methods of making expandable foam-like biomaterials|
|US8071124 *||Dec 6, 2011||Cryolife, Inc.||Methods of using expandable foam-like biomaterials|
|US8071135||Oct 4, 2007||Dec 6, 2011||Anthrogenesis Corporation||Placental tissue compositions|
|US8093444||May 7, 2007||Jan 10, 2012||Argentum Medical, Llc||Multilayer conductive appliance having wound healing and analgesic properties|
|US8105634||Jan 31, 2012||Anthrogenesis Corporation||Umbilical cord biomaterial for medical use|
|US8118791||Oct 31, 2007||Feb 21, 2012||Argentum Medical, Llc||Medical device|
|US8177931||Nov 8, 2006||May 15, 2012||Molnlycke Health Care Ab||Method for perforating heat meltable material|
|US8192764||Jan 10, 2007||Jun 5, 2012||3M Innovative Properties Company||Silver-containing antimicrobial articles and methods of manufacture|
|US8193267||Jun 5, 2012||3M Innovative Properties Company||Polymer compositions with bioactive agent, medical articles, and methods|
|US8226964||Jul 24, 2012||Biolargo Life Technologies, Inc.||Systems and methods for cleaning liquid carriers related applications data|
|US8269058||Sep 18, 2012||Hemcon Medical Technologies, Inc.||Absorbable tissue dressing assemblies, systems, and methods formed from hydrophilic polymer sponge structures such as chitosan|
|US8283513||Oct 9, 2012||Argentum Medical, Llc||Multilayer wound dressing|
|US8293964||Oct 23, 2012||Argentum Medical, Llc||Multilayer laminate wound dressing|
|US8313474||Dec 17, 2007||Nov 20, 2012||Hemcon Medical Technologies, Inc.||Method for preparing a compressed wound dressing|
|US8399027||Jan 13, 2006||Mar 19, 2013||3M Innovative Properties Company||Silver coatings and methods of manufacture|
|US8449514||May 28, 2013||Argentum Medical, Llc||Conductive wound dressings and methods of use|
|US8455710 *||Apr 23, 2003||Jun 4, 2013||Argentum Medical, Llc||Conductive wound dressings and methods of use|
|US8465537||Jun 17, 2004||Jun 18, 2013||Gel-Del Technologies, Inc.||Encapsulated or coated stent systems|
|US8529939||Dec 8, 2004||Sep 10, 2013||Gel-Del Technologies, Inc.||Mucoadhesive drug delivery devices and methods of making and using thereof|
|US8574610||Jan 10, 2011||Nov 5, 2013||Biolargo Life Technologies, Inc.||Material having antimicrobial activity when wet|
|US8623393||Apr 29, 2003||Jan 7, 2014||Gel-Del Technologies, Inc.||Biomatrix structural containment and fixation systems and methods of use thereof|
|US8668924||Oct 18, 2010||Mar 11, 2014||Providence Health System—Oregon||Wound dressing and method for controlling severe, life-threatening bleeding|
|US8741335||Jul 13, 2006||Jun 3, 2014||Hemcon Medical Technologies, Inc.||Hemostatic compositions, assemblies, systems, and methods employing particulate hemostatic agents formed from hydrophilic polymer foam such as Chitosan|
|US8795710||Aug 22, 2008||Aug 5, 2014||Codman & Shurtleff, Inc.||Collagen device and method of preparing the same|
|US8801681||Oct 21, 2005||Aug 12, 2014||Argentum Medical, Llc||Medical device|
|US8821857||Aug 18, 2011||Sep 2, 2014||Anthrogenesis Corporation||Human placental collagen compositions and methods of making and using the same|
|US8871267||Feb 5, 2010||Oct 28, 2014||Gel-Del Technologies, Inc.||Protein matrix materials, devices and methods of making and using thereof|
|US8877180||May 9, 2012||Nov 4, 2014||Anthrogenesis Corporation||Human placental collagen compositions, and methods of making and using the same|
|US8920443||Feb 17, 2005||Dec 30, 2014||Cook Biotech Incorporated||Medical devices and methods useful for applying bolster material|
|US8920444||Aug 4, 2006||Dec 30, 2014||Cook Biotech Incorporated||Medical devices and methods useful for applying bolster material|
|US8920514||Dec 20, 2007||Dec 30, 2014||Providence Health System—Oregon||Systems and methods for introducing and applying a bandage structure within a body lumen or hollow body organ|
|US8951565||Apr 17, 2014||Feb 10, 2015||Hemcon Medical Technologies, Inc.||Hemostatic compositions, assemblies, systems, and methods employing particulate hemostatic agents formed from hydrophilic polymer foam such as chitosan|
|US9004918||Jul 12, 2010||Apr 14, 2015||Hemcon Medical Technologies, Inc.||Compositions, assemblies, and methods applied during or after a dental procedure to ameliorate fluid loss and/or promote healing, using a hydrophilic polymer sponge structure such as chitosan|
|US9089366||Dec 18, 2013||Jul 28, 2015||Steven Garner-Richards||System for tracking surgical objects|
|US9132206||Jan 5, 2015||Sep 15, 2015||Hemcon Medical Technologies, Inc.||Hemostatic compositions, assemblies, systems, and methods employing particulate hemostatic agents formed from hydrophilic polymer foam such as chitosan|
|US9186140||Apr 25, 2008||Nov 17, 2015||Cook Biotech Incorporated||Medical devices and methods useful for applying bolster material|
|US9204957||Mar 17, 2005||Dec 8, 2015||Hemcon Medical Technologies, Inc.||Systems and methods for hemorrhage control and or tissue repair|
|US9205170||May 1, 2009||Dec 8, 2015||Hemcon Medical Technologies, Inc.||Wound dressing devices and methods|
|US9289450||May 1, 2012||Mar 22, 2016||3M Innovative Properties Company||Silver-containing antimicrobial articles and methods of manufacture|
|US20020013300 *||Mar 16, 2001||Jan 31, 2002||Avocet Polymer Technologies, Inc.||Methods for improving size and appearance of a wound|
|US20020028243 *||Feb 28, 2001||Mar 7, 2002||Masters David B.||Protein matrix materials, devices and methods of making and using thereof|
|US20020173806 *||Apr 12, 2002||Nov 21, 2002||Verigen Transplantation Service International (Vtsi) Ag||Method for autologous transplantation|
|US20030007991 *||Aug 3, 2001||Jan 9, 2003||Masters David B.||Devices including protein matrix materials and methods of making and using thereof|
|US20030021854 *||Apr 23, 2002||Jan 30, 2003||Burrell Robert Edward||Method of induction of apoptosis and inhibition of matrix metalloproteinases using antimicrobial metals|
|US20030180378 *||Oct 22, 2002||Sep 25, 2003||Gillis Scott H.||Dry powders of metal-containing compounds|
|US20030203046 *||Feb 12, 2003||Oct 30, 2003||Burrell Robert E.||Solutions and aerosols of metal-containing compounds|
|US20030206966 *||Oct 22, 2002||Nov 6, 2003||Burrell Robert E.||Methods of inducing apoptosis and modulating metalloproteinases|
|US20030211793 *||Mar 5, 2001||Nov 13, 2003||Eugene Bell||Injectable bio-compatible material and methods of use|
|US20040030276 *||Apr 23, 2003||Feb 12, 2004||Flick Bart A.||Conductive wound dressings and methods of use|
|US20040048796 *||Mar 26, 2003||Mar 11, 2004||Hariri Robert J.||Collagen biofabric and methods of preparation and use therefor|
|US20040049145 *||Sep 11, 2003||Mar 11, 2004||Flick A. Bart||Multilayer conductive appliance having wound healing and analgesic properties|
|US20040129112 *||Oct 22, 2003||Jul 8, 2004||Gillis Scott H.||Metal-containing materials|
|US20040131698 *||Oct 22, 2003||Jul 8, 2004||Gillis Scott H.||Methods of treating conditions using metal-containing materials|
|US20040136968 *||Sep 26, 2003||Jul 15, 2004||Verigen Ag||Autologous cells on a support matrix for tissue repair|
|US20040176312 *||Feb 2, 2004||Sep 9, 2004||Gillis Scott H.||Treatment of ungual and subungual diseases|
|US20040180093 *||Dec 5, 2003||Sep 16, 2004||3M Innovative Properties Company||Polymer compositions with bioactive agent, medical articles, and methods|
|US20040258738 *||Jul 8, 2004||Dec 23, 2004||Kania Bruce G.||Treatment devices providing targeted antimicrobial action|
|US20050123590 *||Dec 5, 2003||Jun 9, 2005||3M Innovative Properties Company||Wound dressings and methods|
|US20050123621 *||Dec 5, 2003||Jun 9, 2005||3M Innovative Properties Company||Silver coatings and methods of manufacture|
|US20050124724 *||Dec 5, 2003||Jun 9, 2005||3M Innovative Properties Company||Polymer compositions with bioactive agent, medical articles, and methods|
|US20050147690 *||Oct 12, 2004||Jul 7, 2005||Masters David B.||Biocompatible protein particles, particle devices and methods thereof|
|US20050158364 *||Jan 26, 2005||Jul 21, 2005||Cryolife, Inc.||Methods of making expandable foam-like biomaterials|
|US20050159695 *||Dec 6, 2002||Jul 21, 2005||Cullen Breda M.||Controlled release therapeutic wound dressings|
|US20050163817 *||Apr 29, 2003||Jul 28, 2005||Masters David B.||Biomatrix structural containment and fixation systems and methods of use thereof|
|US20050163819 *||Jan 26, 2005||Jul 28, 2005||Cryolife, Inc||Methods of using expandable foam-like biomaterials|
|US20050196440 *||Dec 8, 2004||Sep 8, 2005||Masters David B.||Mucoadhesive drug delivery devices and methods of making and using thereof|
|US20050244484 *||Apr 29, 2005||Nov 3, 2005||Flick A B||Multilayer conductive appliance having wound healing and analgesic properties|
|US20050283256 *||Jun 30, 2005||Dec 22, 2005||Codman & Shurtleff, Inc.||Collagen device and method of preparing the same|
|US20060004314 *||Aug 12, 2005||Jan 5, 2006||Hemcon, Inc.||Antimicrobial barriers, systems, and methods formed from hydrophilic polymer structures such as chistosan|
|US20060004407 *||Feb 17, 2005||Jan 5, 2006||Hiles Michael C||Medical devices and methods useful for applying bolster material|
|US20060025786 *||Oct 12, 2004||Feb 2, 2006||Verigen Transplantation Service International (Vtsi) Ag||Method for autologous transplantation|
|US20060034899 *||Aug 12, 2004||Feb 16, 2006||Ylitalo Caroline M||Biologically-active adhesive articles and methods of manufacture|
|US20060035039 *||Aug 12, 2004||Feb 16, 2006||3M Innovative Properties Company||Silver-releasing articles and methods of manufacture|
|US20060083777 *||Nov 22, 2005||Apr 20, 2006||Nucryst Pharmaceuticals Corp.||Treatment of acne|
|US20060083792 *||Nov 22, 2005||Apr 20, 2006||Nucryst Pharmaceuticals Corp.||Therapeutic treatments using the direct application of antimicrobial metal compositions|
|US20060149040 *||May 20, 2003||Jul 6, 2006||John Snowden||Collagen and method for producing same|
|US20060167540 *||Jun 17, 2004||Jul 27, 2006||Masters David B||Encapsulated or coated stent systems|
|US20060173087 *||Mar 12, 2003||Aug 3, 2006||Hyde Patrick D||Absorbent polymer compositions, medical articles, and methods|
|US20060204591 *||May 16, 2006||Sep 14, 2006||Nucryst Pharamaceuticals Corp., A Canadian Corporation||Treatment of mucosal membranes|
|US20060210960 *||Jul 7, 2005||Sep 21, 2006||Lifecell Corporation, A Texas Corporation||Method for processing and preserving collagen-based tissues for transplantation|
|US20060211973 *||Mar 17, 2005||Sep 21, 2006||Gregory Kenton W||Systems and methods for hemorrhage control and or tissue repair|
|US20060233889 *||Jan 13, 2006||Oct 19, 2006||3M Innovative Properties Company||Silver coatings and methods of manufacture|
|US20060264796 *||Oct 21, 2005||Nov 23, 2006||Argentum Medical, Llc||Medical device|
|US20070010778 *||Aug 24, 2006||Jan 11, 2007||Nucryst Pharmaceuticals Corp., A Canadian Corporation||Transcutaneous medical device dressings and method of use|
|US20070014755 *||Jul 1, 2006||Jan 18, 2007||Beckman Eric J||Wound healing polymeric networks|
|US20070027472 *||Aug 4, 2006||Feb 1, 2007||Hiles Michael C||Medical devices and methods useful for applying bolster material|
|US20070038298 *||Jun 29, 2006||Feb 15, 2007||Sulner Joseph W||Repair of tympanic membrane using placenta derived collagen biofabric|
|US20070073415 *||Sep 29, 2005||Mar 29, 2007||Codman And Shurtleff, Inc.||Dural graft and method of preparing the same|
|US20070166399 *||Jan 13, 2006||Jul 19, 2007||3M Innovative Properties Company||Silver-containing antimicrobial articles and methods of manufacture|
|US20070179522 *||Sep 6, 2005||Aug 2, 2007||Argentum Medical, Llc||Multilayer wound dressing|
|US20070212396 *||May 10, 2007||Sep 13, 2007||Verigen Ag||Autologous cells on a support matrix for tissue repair|
|US20080014286 *||Aug 14, 2007||Jan 17, 2008||Nucryst Pharmaceuticals Corp., A Canada Corporation||Metal-containing materials|
|US20080033506 *||May 7, 2007||Feb 7, 2008||Argentum International, Llc||Multilayer Conductive Appliance Having Wound Healing and Analgesic Properties|
|US20080063694 *||Sep 7, 2006||Mar 13, 2008||Biolargo Life Technologies, Incorporated||Material having antimicrobial activity when wet|
|US20080069895 *||Aug 15, 2007||Mar 20, 2008||Qing Liu||Umbilical cord biomaterial for medical use|
|US20080114279 *||Oct 29, 2007||May 15, 2008||Argentum Medical, Llc||Multilayer laminate wound dressing|
|US20080121592 *||Jan 18, 2008||May 29, 2008||Biolargo Life Technologies, Incorporated||Systems and methods for cleaning liquid carriers related applications data|
|US20080131522 *||Oct 3, 2007||Jun 5, 2008||Qing Liu||Use of placental biomaterial for ocular surgery|
|US20080146983 *||Jan 26, 2007||Jun 19, 2008||Biopol Co., Ltd.||Polyurethane foam dressing with improved moisturization|
|US20080146984 *||Dec 17, 2007||Jun 19, 2008||Hemcon Medical Technologies, Inc.||Method for preparing a compressed wound dressing|
|US20080181935 *||Oct 9, 2007||Jul 31, 2008||Mohit Bhatia||Human placental collagen compositions, and methods of making and using the same|
|US20080200949 *||Apr 25, 2008||Aug 21, 2008||Hiles Michael C||Medical devices and methods useful for applying bolster material|
|US20080208359 *||May 1, 2008||Aug 28, 2008||Codman & Shurtleff, Inc.||Dural graft and method of preparing the same|
|US20080279960 *||Jan 10, 2007||Nov 13, 2008||Burton Scott A||Silver-Containing Antimicrobial Articles and Methods of Manufacture|
|US20080287907 *||Dec 20, 2007||Nov 20, 2008||Providence Health System-Oregan D/B/A Providence St. Vincent Medical Center||Systems and methods for introducing and applying a bandage structure within a body lumen or hollow body organ|
|US20090018479 *||Jul 16, 2008||Jan 15, 2009||Hemcon Medical Technologies, Inc.||Absorbable tissue dressing assemblies, systems, and methods formed from hydrophilic polymer sponge structures such as chistosan|
|US20090028915 *||Jul 24, 2008||Jan 29, 2009||Biolargo Life Technologies, Incorporated||Material having antimicrobial activity when wet|
|US20090030526 *||Aug 22, 2008||Jan 29, 2009||Codman & Shurtleff, Inc.||Collagen device and method of preparing the same|
|US20090069736 *||Oct 23, 2003||Mar 12, 2009||Biopol Co., Ltd.||Polyurethane Foam Dressing for Wound Filler and Method for Manufacturing Thereof|
|US20090128716 *||Nov 3, 2008||May 21, 2009||Funai Electric Co., Ltd.||Projector and method for projecting image|
|US20090211693 *||Nov 8, 2006||Aug 27, 2009||Molynlycke Health Care Ab||Method for perforating heat meltable material|
|US20090269413 *||Oct 29, 2009||Codman & Shurtleff, Inc.||Flowable collagen material for dural closure|
|US20100098949 *||Oct 16, 2007||Apr 22, 2010||Burton Scott A||Antimicrobial articles and method of manufacture|
|US20100143487 *||Dec 26, 2008||Jun 10, 2010||Gel-Del Technologies, Inc.||Biocompatible protein-based particles and methods thereof|
|US20100172958 *||May 1, 2009||Jul 8, 2010||Hemcon Medical Technologies, Inc.||Wound dressing devices and methods|
|US20100196478 *||Aug 5, 2010||Gel-Del Technologies, Inc.||Protein matrix materials, devices and methods of making and using thereof|
|US20100233273 *||May 19, 2010||Sep 16, 2010||3M Innovative Properties Company||Polymer compositions with bioactive agent, medical articles, and methods|
|US20110034410 *||Feb 10, 2011||Mccarthy Simon J||Wound dressing and method for controlling severe, life-threatening bleeding|
|US20110104303 *||May 5, 2011||Biolargo Life Technologies, Inc.||Material having antimicrobial activity when wet|
|US20110118818 *||Jun 17, 2005||May 19, 2011||Gel-Del Technologies ,Inc. a corporation||Encapsulated or coated stent systems|
|US20110143312 *||Jul 12, 2010||Jun 16, 2011||Hemcon Medical Technologies, Inc.||Compositions, assemblies, and methods applied during or after a dental procedure to ameliorate fluid loss and/or promote healing, using a hydrophilic polymer sponge structure such as chitosan|
|US20150125512 *||Feb 26, 2013||May 7, 2015||Aap Biomaterials Gmbh||Antibacterial sheet material that can be used as a wound dressing and method for producing same|
|US20160129151 *||Nov 6, 2014||May 12, 2016||Case Western Reserve University||Protein based materials|
|DE4227681A1 *||Aug 21, 1992||Feb 24, 1994||Becker & Co Naturinwerk||Wundabdeckungsmaterial auf der Basis von Kollagenfasern|
|DE202011100392U1||May 7, 2011||Jun 9, 2011||Neubauer, Norbert, 38820||Brandwundenauflage|
|EP0006714A1 *||Jun 13, 1979||Jan 9, 1980||Johnson & Johnson||Balanced environment wound dressing|
|EP0068777A2 *||Jun 21, 1982||Jan 5, 1983||Minnesota Mining And Manufacturing Company||Composite wound dressing|
|EP0167828A1 *||Jun 4, 1985||Jan 15, 1986||Koken Co. Ltd.||A man-made skin composed of two layers:Collagen and a poly-alpha-amino acid|
|EP0227955A2 *||Jul 20, 1983||Jul 8, 1987||University of Strathclyde||Composite wound dressing|
|EP0371736A2 *||Nov 28, 1989||Jun 6, 1990||Mitsubishi Kasei Corporation||Wound covering|
|EP0371736A3 *||Nov 28, 1989||Dec 27, 1990||Mitsubishi Kasei Corporation||Wound covering|
|EP0422046A1 *||May 10, 1989||Apr 17, 1991||Kensey Nash Corp||Device for sealing percutaneous puncture in a vessel.|
|EP0431479A1 *||Nov 30, 1990||Jun 12, 1991||Hoechst Japan Limited||Wound surface-covering sheets|
|EP0653214A1 *||Nov 10, 1994||May 17, 1995||YISSUM RESEARCH DEVELOPMENT COMPANY of the Hebrew University of Jerusalem||Topical antibacterial preparation|
|EP0666082A1 *||Feb 3, 1995||Aug 9, 1995||Pharmalett International B.V.||Laminate for treating wounds|
|EP1435911A1 *||Feb 1, 2002||Jul 14, 2004||Gel-Del Technologies, Inc.||Devices including protein matrix materials and methods of making and using same|
|EP1864634A2||Sep 22, 1998||Dec 12, 2007||Argentum International, LLC||Multilayer conductive appliance having wound healing and analgesic properties|
|EP2315555A2 *||Jul 27, 2009||May 4, 2011||Manuela Singer||Reusable medical protective clothing for pets and farm animals after surgeries and with skin diseases|
|EP2316524A1||Sep 22, 1998||May 4, 2011||Argentum International, LLC||Multilayer conductive appliance having wound healing and analgesic properties|
|EP2664341A2||Oct 9, 2007||Nov 20, 2013||Anthrogenesis Corporation||Native (telopeptide) placental collagen compositions|
|EP2664342A2||Oct 9, 2007||Nov 20, 2013||Anthrogenesis Corporation||Native (telopeptide) placental collagen compositions|
|EP2700309A1||Mar 26, 2003||Feb 26, 2014||Anthrogenesis Corporation||Collagen biofabric and methods of preparation and use therefor|
|EP2702871A1||Mar 26, 2003||Mar 5, 2014||Anthrogenesis Corporation||Collagen biofabric and methods of preparation and use therefor|
|WO2003047643A1 *||Dec 6, 2002||Jun 12, 2003||Johnson & Johnson Medical Limited||Controlled release therapeutic wound dressings|
|WO2003099230A2 *||May 28, 2003||Dec 4, 2003||Virginia Commonwealth University Intellectual Property Foundation||Electroprocessed collagen and tissue engineering|
|WO2003099230A3 *||May 28, 2003||Jun 10, 2004||Gary L Bowlin||Electroprocessed collagen and tissue engineering|
|WO2008065329A2 *||Oct 23, 2007||Jun 5, 2008||Systagenix Wound Management Ip Co. B.V.||Protein sheet material|
|WO2008065329A3 *||Oct 23, 2007||Jan 8, 2009||Ethicon Inc||Protein sheet material|
|WO2013135478A1 *||Feb 26, 2013||Sep 19, 2013||Aap Biomaterials Gmbh||Antibacterial sheet material that can be used as a wound dressing and method for producing same|
|U.S. Classification||602/50, 530/356, 602/58, 128/DIG.800|
|International Classification||A61L15/42, A61L15/32, A61L15/26|
|Cooperative Classification||Y10S128/08, A61L15/26, A61L15/325, A61L15/425|
|European Classification||A61L15/26, A61L15/42E, A61L15/32A|