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WO1997017025A1 - Procedes et articles permettant de fixer des couches matricielles renfermant des proteines non collagenes sur un tissu - Google Patents

Procedes et articles permettant de fixer des couches matricielles renfermant des proteines non collagenes sur un tissu Download PDF

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Publication number
WO1997017025A1
WO1997017025A1 PCT/US1996/017854 US9617854W WO9717025A1 WO 1997017025 A1 WO1997017025 A1 WO 1997017025A1 US 9617854 W US9617854 W US 9617854W WO 9717025 A1 WO9717025 A1 WO 9717025A1
Authority
WO
WIPO (PCT)
Prior art keywords
tissue
energy
matrix material
group
collagenous protein
Prior art date
Application number
PCT/US1996/017854
Other languages
English (en)
Inventor
Donald G. Wallace
Cary J. Reich
Greg Dapper
Original Assignee
Fusion Medical Technologies, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Fusion Medical Technologies, Inc. filed Critical Fusion Medical Technologies, Inc.
Priority to AU76711/96A priority Critical patent/AU7671196A/en
Publication of WO1997017025A1 publication Critical patent/WO1997017025A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/22—Polypeptides or derivatives thereof, e.g. degradation products
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/00491—Surgical glue applicators
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/001—Use of materials characterised by their function or physical properties
    • A61L24/0026—Sprayable compositions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/0047—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L24/0073—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material with a macromolecular matrix
    • A61L24/0094—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material with a macromolecular matrix containing macromolecular fillers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
    • A61L24/043—Mixtures of macromolecular materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
    • A61L24/10—Polypeptides; Proteins
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/26—Mixtures of macromolecular compounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/40—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L27/44—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L27/48—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix with macromolecular fillers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/00491—Surgical glue applicators
    • A61B2017/00495—Surgical glue applicators for two-component glue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/00491—Surgical glue applicators
    • A61B2017/00504—Tissue welding
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/00491—Surgical glue applicators
    • A61B2017/00504—Tissue welding
    • A61B2017/00508—Tissue welding using laser

Definitions

  • the present invention relates generally to methods and articles for fusing matrix materials to form layers over tissue. More particularly, the present invention relates to fusing matrix layers containing non-collagenous proteins to tissues for wound closure, and other purposes.
  • matrix materials may be applied to tissue in order to effect or enhance wound closure, to augment and repair tissue defects, and the like.
  • a variety of specific compositions and methods have been devised for such purposes.
  • the fusing of collagen and other proteins by the application of laser and other energy sources has been suggested for the closure of wounds. See, for example, U.S. Patent Nos. 5,156,613; 5,209,776; and 5,071,417.
  • the application of pre-polymer materials followed by light- induced cross-linking has also been proposed. See, for example, PCT publications WO 94/24962 and WO 94/21324.
  • the present invention provides improved methods and articles for fusing a matrix material to tissue for a variety of purposes, including wound closure, tissue augmentation, or the like.
  • the matrix material comprises a non-collagenous protein component which when placed over a target location on the tissue will fuse to the tissue upon the application of energy, such as radio frequency energy, laser energy, ultrasonic energy, heat, infrared, microwave or the like.
  • the energy will be applied in an amount sufficient to fuse the matrix material to the underlying tissue with a peel bond strength of at least about 0.03 N/cm.
  • the terms “fuse” and “fusing” will mean that the matrix material has been caused to adhere to the underlying tissue with a peel bond strength (defined below) of at least about 0.03 N/cm.
  • a peel bond strength defined below
  • the precise energy level will depend on the nature of the protein, the nature of the energy source and the nature of the underlying tissue, typically it will be in the range from about 1 W/cm 2 to about 100 W/cm 2 .
  • non-collagenous proteins include albumins, such as bovine serum albumin (BSA) , ovalbumin, human serum albumin (HSA) ; hemoglobins from human, bovine, and other sources; fibrinogens from human, bovine, and other sources; fibronectins from human, bovine, and other sources; elastins; keratins; laminins; and the like.
  • BSA bovine serum albumin
  • HSA human serum albumin
  • the matrix material may be applied (prior to exposure to energy) in a variety of forms, usually being a solid, mesh, or composite layer.
  • the matrix material may comprise a dispersible, non-solid phase, such as liquids, gels, sols, suspensions, powders, and the like.
  • the matrix material may comprise substantially pure protein, but in many cases it will be desirable to combine additional components, such as carrier materials, reinforcement materials, plasticizers, and the like. After the application of energy, a layer of the matrix material will usually fuse to the underlying tissue with the requisite peel bond strength.
  • the layer will typically have a thickness of at least about 0.01 mm, usually being in the range from about 0.05 mm to about 0.1 mm, and the layer will usually form a substantially continuous surface on the underlying tissue.
  • the area may vary widely, typically being at least about 0.05 cm 2 , usually being in the range from about 1 cm 2 to about 100 cm 2 .
  • Articles according to the present invention comprise a sheet of the matrix material generally as described above.
  • the sheets will usually be sterilized and present in a sterile package for distribution and storage prior to use.
  • FIG. 1 is a perspective view of a sheet of matrix material according to the present invention.
  • Fig. 2 is a top view of a package containing the matrix material of Fig. 1, shown with a portion broken away.
  • Fig. 3 is a schematic illustration of a region of tissue having a wound therein.
  • Fig. 4 illustrates the method of the present invention wherein a solid sheet of matrix material is placed over the wound of Fig. 3 and radio frequency (RF) energy is used to fuse the matrix material to the tissue.
  • RF radio frequency
  • Fig. 5 illustrates an alternative embodiment of the method of the present invention, wherein a liquid or gel matrix material is applied using a syringe to the wound in the tissue of Fig. 3.
  • Fig. 6 illustrates the application of RF energy to the liquid matrix material of Fig. 5.
  • Fig. 7 illustrates a resulting layer of matrix material which has been bonded to tissue according to the method of the present invention.
  • Tissues include virtually all human and animal body tissues, including the skin (epidermis) , as well as the external and internal surfaces of virtually all body organs.
  • the present invention is particularly useful for fusing matrix materials to fragile body organs, such as lungs, stomach, liver, spleen, intestines, colon, fallopian tubes, esophagus, ovary, uterus, bladder, and the like.
  • the matrix material may be applied for a variety of purposes, including wound closure, tissue augmentation, and the like. Wounds to be treated may result from accidental trauma, surgical intervention, or virtually any other cause.
  • Tissue augmentation will usually be performed to fill or cover regions of tissue where tissue has been lost or damaged, such as abrasions, burns, and the like.
  • the matrix materials of the present invention will comprise a non-collagenous protein component, as described in more detail below.
  • the non-collagenous protein will be selected to provide for bonding of the resulting layer of matrix material, typically providing a peel bond strength of at least about 0.03 N/cm, preferably at least about 0.07 N/cm, and usually in the range from about 0.07 N/cm to about 0.2 N/cm. Peel bond strength can be measured by conventional techniques. A particular method for measuring peel bond strength is as follows.
  • Pieces of the matrix material (1.5 cm x 3 cm) are cut and glued to a plastic tab (1.5 " cm x 3 cm) which overlaps the test material by 1 cm over the width (the 1.5 cm dimension) , using a cyanoacrylate glue.
  • a hole is pierced in the tab, and the test material bonded to the tissue in vivo or in vi tro .
  • a digital force gauge such as an Omega DF051-2 fitted with a 2 pound force transducer, Omega Instruments, Stamford, Connecticut, is attached to the plastic tab using a hook attachment which is secured to hole in the plastic tab.
  • a manual upward force is then applied on the force gauge, and the sample peeled off with an even rate of pull, typically about 3 cm per second. Peel strengths are recorded in force (Newtons) divided by the width of the sample (1.5 cm) in order to determine the peel bond strength. The peel bond strength is measured as a maximum.
  • the non-collagenous protein component may comprise one, two, or more individual proteins.
  • Exemplary non- collagenous proteins include albumins, such as bovine serum albumin (BSA) , ovalbumin, human serum albumin (HSA) ; hemoglobins from human, bovine, and other sources; fibrinogens from human, bovine, and other sources; fibronectins from human, bovine, and other sources; elastin; keratin; and laminin.
  • the proteins may comprise substantially all of the matrix material, or may comprise only a portion thereof. In the latter case, additional components may be included, such as carrier substances, reinforcing materials (e.g., reinforcing meshes, fibers, filaments, braids and the like) , and plasticizers.
  • Exemplary carrier substances include collagen, gelatin, fibrinogen, and elastin.
  • the matrix material will usually be in the form of a solid layer, e.g. , in the form of a sheet, film, patch, strip, mesh, or the like.
  • the use of a mesh allows tissue to form a coagulum within the interstices of the mesh as energy is applied, as described in copending application serial no. 08/303,336, the disclosure of which is incorporated herein by reference.
  • the solid phase forms of the matrix material may optionally be reinforced with filaments, braids, meshes, and other woven and non-woven reinforcement materials.
  • the reinforcement materials will be non- bioabsorbable so that they will remain even after the fusible material has been resorbed.
  • Exemplary reinforcement materials include polymeric braids or meshes, particularly composed of polypropylene (Marlex ® ) , fluorinated hydrocarbon polymers
  • the reinforcement materials may be biodegradable.
  • Exemplary biodegradable materials include polylactic acid, polyglycolic acid, copolymers of lactic acid and glycolic acid, polyhydroxybutyrate, other poly ( ⁇ -hydroxy acids) polydioxanone, and the like. Filaments, braids, meshes, woven and non-woven forms may be used.
  • Reinforced and non-reinforced matrix materials may be formed by conventional techniques for forming and solidifying proteins.
  • the proteins will be cross ⁇ linked to enhance structural integrity.
  • the proteins may be dissolved in water to form a gel .
  • the gel may then be layered over a flat surface to a desired thickness, and the gel dried to form a solid sheet.
  • Such sheets will typically have a thickness in the range from about 0.03 mm to about 0.15 mm, usually from about 0.05 mm to about 0.1 mm.
  • the sheets will preferably have an area of at least about 0.5 cm 2 , preferably at least about 1 cm 2 , and usually in the range from about 1 cm 2 to about 100 cm 2 . It will be appreciated that sheets of various sizes can be trimmed to an appropriate size and shape for a particular application.
  • the matrix materials may be applied to the target region on the tissue in a non-solid dispersible state, e.g., as a liquid, gel, paste, spray, sol or combination thereof.
  • a non-solid dispersible state e.g., as a liquid, gel, paste, spray, sol or combination thereof.
  • Such dispersible matrix materials may be applied using syringes, brushes, sprayers, spatulas, or other methods suitable for spreading or dispersing a layer of the material over the wound region.
  • the layer will have a thickness in the range from about 0.01 mm to about 5 mm, preferably from about 0.05 mm to about 1 mm.
  • the method of the present invention will utilize energy of a type and in an amount sufficient to fuse the matrix material including the non-collagenous protein to underlying tissue.
  • Suitable energy sources include electrical energy, particularly radio frequency (RF) energy, heat energy, laser energy, ultrasonic energy, infrared, microwave, and the like.
  • RF energy sources such as those available as electrosurgical power supplies from companies such as Valleylab, Boulder, Colorado, and Con-Med, Utica, New York, employing conventional RF-applying probes.
  • RF energy sources such as those available as electrosurgical power supplies from companies such as Valleylab, Boulder, Colorado, and Con-Med, Utica, New York, employing conventional RF-applying probes.
  • modified RF energy sources which provide for a dispersed or distributed current flow from a hand-held probe to the tissue.
  • a radio frequency inert gas device or inert gas beam coagulator which relies on flow of an inert ionizable gas, such as argon, for conducting current from the probe to the tissue.
  • inert gas beam coagulators are available commercially from suppliers such as Con-Med and Valleylab.
  • Energy from the energy source is typically directed to the tissue using a probe connected to an external power supply.
  • the treating physician usually directs the probe manually to apply energy over the surface of the matrix material and visually confirms that fusion has been achieved.
  • an energy output from about 2W to about 100W, preferably from about 20W to about 40W, will be used.
  • the fusible material will typically be exposed to the energy for a total time from about 5 seconds to about 120 seconds, usually from about 10 seconds to about 40 seconds, for material having an area from about 1 cm 2 to about 10 cm 2 . The precise timing will depend on the physician's visual assessment that the matrix material has fused to the underlying tissue. Referring now to Fig.
  • an article 10 comprising a solid sheet 12 of matrix material comprising a non-collagenous protein component according to the present invention is illustrated.
  • the sheet is square, but sheets having a variety of other regular and irregular geometries, such as rectangles, circles, ovals, and the like, could also be fabricated.
  • the surface area, thickness, and other characteristics of the sheet 12 are preferably (but not necessarily) as described above.
  • the solid sheet 12 is usually packaged in a manner suitable to facilitate use by the treating phys ' ician.
  • the sheet material is sterilized and packaged in a suitable container, such as a pouch, box, canister, bottle, or other conventional receptacle for medical products.
  • a suitable container such as a pouch, box, canister, bottle, or other conventional receptacle for medical products.
  • the sheet 12 is illustrated as packaged in a pouch comprising a front sheet 14 and back sheet 16, where the sheets are laminated together around the edge to seal the interior of the package.
  • the sheet material is rolled and packaged in order to provide larger areas of material. Sterilization of the sheet material 12 is accomplished, prior to, during, or after packaging. Suitable sterilization techniques include the use of sterilizing gases, sterilizing radiation, heat, or the like.
  • the solid sheet 12 or other form of the material of the present invention will be packaged together with written instructions setting forth the methods described herein, i.e. that the materials are to be placed over a target site in tissue and energy applied to effect bonding.
  • the instructions may be printed on the packaging material (e.g. on a box or on a pouch holding the material) or may be provided on a separate package insert which is placed in or on the product package.
  • a strip 20 of the matrix material of the present invention for covering and sealing a wound W in a region of tissue T is illustrated.
  • the strip 20, which has been be trimmed to size prior to use, is placed over the wound W as shown in Fig. 4.
  • energy such as radio frequency energy is applied over the strip using a hand-held probe 22, as illustrated in Fig. 4.
  • the energy is applied by passing the probe 22 over the upper, exposed surface of the strip to fuse the protein-containing strip to the underlying tissue. Exemplary power levels, exposure times, and the like, are described above.
  • Figs. 5 and 6 an alternative method for applying matrix material to the wound W on the region of tissue T is illustrated.
  • Liquid or gel matrix material 30 is applied using a syringe 32, typically in a series of parallel strips 34.
  • Other patterns of application could also be employed, such as circular, spiral, criss-crossed, and the like. It is generally desirable, however, that material be applied at a relatively uniform density over the tissue, so that, after application of energy, a generally continuous layer of matrix material 36 results, as shown in Fig. 6. Again, the energy is typically applied using the hand-held probe 22.
  • the matrix material is in the form of a generally continuous layer 40 of material which adheres to the upper surface S of the tissue T.
  • the layer 40 of material will adhere to the tissue T with a minimum peel bond strength as set forth above.
  • the layer 40 will have a relatively high tensile strength so that it can maintain the integrity of the tissue T over the wound W.
  • Patches were fabricated from bovine serum albumin, bovine fibrinogen, and bovine hemoglobin. Bonds were achieved with each of these patches, using an argon beam coagulator to deliver thermal energy.
  • the tissue model was porcine or bovine lung in vi tro .
  • Bovine hemoglobin (BHG, Sigma Chemical Co.) was dissolved in a buffer of 0.03M NaCl and 0.02M sodium phosphate, pH 6.8, to achieve a solution at 40 mg protein/ml.
  • the protein was cross-linked by adding di-glycidyl PEG 600MW (DPEG, Polysciences, Inc.) and heating.
  • One formulation was prepared by mixing 1.53 ml of BHG solution and 15.3 ul of a 10% (w/v) aqueous solution of DPEG in a polystyrene weighing boat (4.6 cm square) , covered with aluminum foil, and heated at 50°C overnight.
  • a second formulation was prepared in an aluminum sample pan and heated at 80°C in a water bath for 15 min.
  • Bovine serum albumin (0.5g, Sigma Chemical Co.) was mixed in a polystyrene weighing boat 4.6 cm square with 1.5 ml 0.9% saline and held at 5°C overnight. At this point, the albumin had dissolved to yield a viscous solution. Glutaraldehyde (37% aqueous, w/v; 14 ul) was added and stirred rapidly into the albumin solution. Within minutes the albumin formed a continuous gel. It was dried under ambient conditions to a moist film. At this point, the partially dried film was dislodged from the polystyrene boat and wrapped in plastic sheeting to prevent further drying.
  • the moist film and a fully hydrated film were tested. Conditions for welding were as described above, except that the time for treatment of patches with the argon beam was approximately 5 sec per cm 2 of patch.
  • the moist film yielded a bond strength (peel strength) of approximately 0.03 Newtons/cm; the fully hydrated film, approximately 0.01 Newtons/cm. Patches were removable as intact films (did not tear) .
  • Albumin-polyacrylamide composite patches were prepared by mixing 167 mg bovine serum albumin, 1.67 ml saline, 0.62 ml stock acrylamide (30% aqueous acrylamide, 0.8% bis-acrylamide, w/v) , 40 ul 10% (w/v) ammonium persulfate, and 8 ul TEMED (tetramethyl-ethylenediamine) .
  • the mixture was poured into several polystyrene weigh boats (4.6 cm square) and allowed to polymerize at room temperature. " Gels were allowed to dry at ambient to form moist mats and wrapped with plastic sheeting to prevent further drying.
  • Moist mats were bonded by argon beam to porcine lung in vi tro and yielded a peel strength of approximately 0.03 Newtons/cm; mats hydrated 5 min in saline did not bond after argon beam treatment. Mats were removable from the bond site in an intact state. Conditions for bonding with the argon beam were as for albumin patches as described above.
  • Bovine fibrinogen (Sigma Chemical co., 400 mg) was mixed with 9.6 ml of 0.3M NaCl, 0.02M sodium phosphate, pH 6.8, and held at 5°C for 16 hours to several days to permit dissolution of the fibrinogen (Dissolution was facilitated at the end by incubation at 37°C for 10 min) .
  • the solution was allowed to dry to a film with thickness of 0.04 to 0.05 mm.
  • the dry film yielded a bond peel strength of approximately 0.03 Newtons/cm and remained intact upon peeling. The hydrated film disintegrated and could not be welded. Conditions for bonding with the argon beam were the same as those used for albumin patches.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Epidemiology (AREA)
  • Surgery (AREA)
  • Chemical & Material Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Medicinal Chemistry (AREA)
  • Dermatology (AREA)
  • Materials Engineering (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Composite Materials (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Materials For Medical Uses (AREA)

Abstract

On procède à la fixation d'un matériau matriciel (12) renfermant un composant protéinique non collagène sur un tissu (T) en plaçant d'abord ce matériau matriciel (12) sur un emplacement cible (W) du tissu (T), puis en appliquant une énergie sur le matériau matriciel (12). Le composant protéinique non collagène est d'un type tel que, lorsque de l'énergie est appliquée en une quantité appropriée, il se produit une fixation de la matrice au tissu.
PCT/US1996/017854 1995-11-07 1996-11-06 Procedes et articles permettant de fixer des couches matricielles renfermant des proteines non collagenes sur un tissu WO1997017025A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU76711/96A AU7671196A (en) 1995-11-07 1996-11-06 Methods and articles for fusing matrix layers containing non-collagenous proteins to tissue

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US632295P 1995-11-07 1995-11-07
US60/006,322 1995-11-07

Publications (1)

Publication Number Publication Date
WO1997017025A1 true WO1997017025A1 (fr) 1997-05-15

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PCT/US1996/017854 WO1997017025A1 (fr) 1995-11-07 1996-11-06 Procedes et articles permettant de fixer des couches matricielles renfermant des proteines non collagenes sur un tissu

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Cited By (20)

* Cited by examiner, † Cited by third party
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FR2781358A1 (fr) * 1998-07-27 2000-01-28 Cird Galderma Dispositif pour l'assemblage des levres d'une plaie, piece de maintien et procede de traitement cosmetique
WO2000010618A1 (fr) * 1998-08-21 2000-03-02 Tissuemed Ltd. Feuille capable d'etre activee destinee a un usage topique et therapeutique
EP1018944A4 (fr) * 1997-09-26 2001-08-22 Cryolife Inc Technique anastomotique sans suture dans laquelle on utilise un bioadhesif et dispositif associe
AU767057B2 (en) * 1997-02-07 2003-10-30 Kenton W. Gregory Method of producing biomaterials
FR2895900A1 (fr) * 2006-01-09 2007-07-13 Alain Cornil Systeme pour le traitement de plaies de la peau,pansement et equipement d'activation biochimique pour la mise en oeuvre d'un tel systeme
FR2901466A1 (fr) * 2006-05-29 2007-11-30 Alain Cornil Systeme pour le traitement de plaies de la peau, pansement et equipement d'activation biochimique pour la mise en oeuvre d'un tel systeme
FR2911774A1 (fr) * 2007-01-29 2008-08-01 Heatwave Technology Sa Equipement de traitement de plaies et procede de commande d'un tel equipement
EP2311407A1 (fr) * 1999-05-18 2011-04-20 CryoLife, Inc. Méthode d'obtention d'un biomatériau autosupporté, faconné et tridimensionnel
US9265858B2 (en) 2012-06-12 2016-02-23 Ferrosan Medical Devices A/S Dry haemostatic composition
US9533069B2 (en) 2008-02-29 2017-01-03 Ferrosan Medical Devices A/S Device for promotion of hemostasis and/or wound healing
US9724078B2 (en) 2013-06-21 2017-08-08 Ferrosan Medical Devices A/S Vacuum expanded dry composition and syringe for retaining same
US10111980B2 (en) 2013-12-11 2018-10-30 Ferrosan Medical Devices A/S Dry composition comprising an extrusion enhancer
US10653837B2 (en) 2014-12-24 2020-05-19 Ferrosan Medical Devices A/S Syringe for retaining and mixing first and second substances
US10918796B2 (en) 2015-07-03 2021-02-16 Ferrosan Medical Devices A/S Syringe for mixing two components and for retaining a vacuum in a storage condition
US11046818B2 (en) 2014-10-13 2021-06-29 Ferrosan Medical Devices A/S Dry composition for use in haemostasis and wound healing
US11109849B2 (en) 2012-03-06 2021-09-07 Ferrosan Medical Devices A/S Pressurized container containing haemostatic paste
US11654428B2 (en) 2019-01-21 2023-05-23 Vias Partners, Llc Methods, systems and apparatus for separating components of a biological sample
US11801324B2 (en) 2018-05-09 2023-10-31 Ferrosan Medical Devices A/S Method for preparing a haemostatic composition
US12007382B2 (en) 2019-10-31 2024-06-11 Crown Laboratories, Inc. Systems, methods and apparatus for separating components of a sample
US12440835B2 (en) 2020-01-21 2025-10-14 Vias Partners, Llc Methods, systems and apparatus for separating components of a biological sample

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AU767057B2 (en) * 1997-02-07 2003-10-30 Kenton W. Gregory Method of producing biomaterials
EP1018944A4 (fr) * 1997-09-26 2001-08-22 Cryolife Inc Technique anastomotique sans suture dans laquelle on utilise un bioadhesif et dispositif associe
US6685726B2 (en) 1997-09-26 2004-02-03 Cryolife, Inc. Sutureless anastomotic technique using a bioadhesive and device therefor
EP0976362A1 (fr) * 1998-07-27 2000-02-02 Galderma Research & Development, S.N.C. Dispositif pour l'assemblage des levres d'une plaie, et piece de maintien
AU745747B2 (en) * 1998-07-27 2002-03-28 Galderma Research & Development, S.N.C. Apparatus for uniting the lips of a wound, a holding piece, and a cosmetic treatment method
FR2781358A1 (fr) * 1998-07-27 2000-01-28 Cird Galderma Dispositif pour l'assemblage des levres d'une plaie, piece de maintien et procede de traitement cosmetique
WO2000010618A1 (fr) * 1998-08-21 2000-03-02 Tissuemed Ltd. Feuille capable d'etre activee destinee a un usage topique et therapeutique
EP2311407A1 (fr) * 1999-05-18 2011-04-20 CryoLife, Inc. Méthode d'obtention d'un biomatériau autosupporté, faconné et tridimensionnel
US8997752B2 (en) 2006-01-09 2015-04-07 Vivatech Company Skin wound treatment method, dressing and biochemical activation device for the use of such a method
WO2007080239A1 (fr) * 2006-01-09 2007-07-19 Heatwave Technology Systeme pour le traitement de plaies de la peau, pansement et equipement d 'activation biochimique pour la mise en œuvre d'un tel systeme
US8449587B2 (en) 2006-01-09 2013-05-28 Vivatech Company Skin wound treatment system, dressing and biochemical activation device for the use of such a system
FR2895900A1 (fr) * 2006-01-09 2007-07-13 Alain Cornil Systeme pour le traitement de plaies de la peau,pansement et equipement d'activation biochimique pour la mise en oeuvre d'un tel systeme
FR2901466A1 (fr) * 2006-05-29 2007-11-30 Alain Cornil Systeme pour le traitement de plaies de la peau, pansement et equipement d'activation biochimique pour la mise en oeuvre d'un tel systeme
WO2007138217A1 (fr) * 2006-05-29 2007-12-06 Ekkyo Système pour le traitement de plaies de la peau, pansement et équipement d'activation biochimique pour la mise en œoeuvre d'un tel système
US9610123B2 (en) 2006-05-29 2017-04-04 Urgo Recherche Innovation Et Developpement System for treating skin wounds, bandaging and biochemical activation equipment for employing this system
FR2911774A1 (fr) * 2007-01-29 2008-08-01 Heatwave Technology Sa Equipement de traitement de plaies et procede de commande d'un tel equipement
WO2008107563A3 (fr) * 2007-01-29 2008-11-06 Heatwave Technology Équipement de traitement de plaies
US8246667B2 (en) 2007-01-29 2012-08-21 Ekkyo Equipment for treating wounds and method for the biochemical activation of healing
US9533069B2 (en) 2008-02-29 2017-01-03 Ferrosan Medical Devices A/S Device for promotion of hemostasis and/or wound healing
US11109849B2 (en) 2012-03-06 2021-09-07 Ferrosan Medical Devices A/S Pressurized container containing haemostatic paste
US9999703B2 (en) 2012-06-12 2018-06-19 Ferrosan Medical Devices A/S Dry haemostatic composition
US10799611B2 (en) 2012-06-12 2020-10-13 Ferrosan Medical Devices A/S Dry haemostatic composition
US9265858B2 (en) 2012-06-12 2016-02-23 Ferrosan Medical Devices A/S Dry haemostatic composition
US10595837B2 (en) 2013-06-21 2020-03-24 Ferrosan Medical Devices A/S Vacuum expanded dry composition and syringe for retaining same
US9724078B2 (en) 2013-06-21 2017-08-08 Ferrosan Medical Devices A/S Vacuum expanded dry composition and syringe for retaining same
US11103616B2 (en) 2013-12-11 2021-08-31 Ferrosan Medical Devices A/S Dry composition comprising an extrusion enhancer
US10111980B2 (en) 2013-12-11 2018-10-30 Ferrosan Medical Devices A/S Dry composition comprising an extrusion enhancer
US11046818B2 (en) 2014-10-13 2021-06-29 Ferrosan Medical Devices A/S Dry composition for use in haemostasis and wound healing
US10653837B2 (en) 2014-12-24 2020-05-19 Ferrosan Medical Devices A/S Syringe for retaining and mixing first and second substances
US10918796B2 (en) 2015-07-03 2021-02-16 Ferrosan Medical Devices A/S Syringe for mixing two components and for retaining a vacuum in a storage condition
US11801324B2 (en) 2018-05-09 2023-10-31 Ferrosan Medical Devices A/S Method for preparing a haemostatic composition
US11654428B2 (en) 2019-01-21 2023-05-23 Vias Partners, Llc Methods, systems and apparatus for separating components of a biological sample
US12007382B2 (en) 2019-10-31 2024-06-11 Crown Laboratories, Inc. Systems, methods and apparatus for separating components of a sample
US12440835B2 (en) 2020-01-21 2025-10-14 Vias Partners, Llc Methods, systems and apparatus for separating components of a biological sample

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