EP1587551A2 - Composite adhesif non actionne par la lumiere, systeme et procedes associes - Google Patents

Composite adhesif non actionne par la lumiere, systeme et procedes associes

Info

Publication number
EP1587551A2
EP1587551A2 EP04705242A EP04705242A EP1587551A2 EP 1587551 A2 EP1587551 A2 EP 1587551A2 EP 04705242 A EP04705242 A EP 04705242A EP 04705242 A EP04705242 A EP 04705242A EP 1587551 A2 EP1587551 A2 EP 1587551A2
Authority
EP
European Patent Office
Prior art keywords
scaffold
adhesive
composite
tissue
tensile strength
Prior art date
Legal status (The legal status 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 status listed.)
Withdrawn
Application number
EP04705242A
Other languages
German (de)
English (en)
Inventor
Karen M. Mcnally-Heintzelman
Douglas L. Heintzelman
Jeffrey N. Bloom
Mark T. Duffy
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Rose-Hulman Institute of Technology
Original Assignee
Rose-Hulman Institute of Technology
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
Priority claimed from US10/610,068 external-priority patent/US20050004599A1/en
Application filed by Rose-Hulman Institute of Technology filed Critical Rose-Hulman Institute of Technology
Publication of EP1587551A2 publication Critical patent/EP1587551A2/fr
Withdrawn legal-status Critical Current

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
    • A61L27/40—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
    • 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

Definitions

  • the present invention relates to the field of biological tissue repair and/or
  • wound closure e.g., after injury to the tissue or surgery. More particularly, the present
  • invention relates to the use of biological or biocompatible adhesive composites for the
  • Known methods of biological tissue repair include sutures, staples and clips,
  • sutures require technical skill for their application, they can result in uneven healing, and
  • Staples or clips are preferred over sutures, for example, in minimally invasive
  • Staples and clips require less time to apply than sutures, are
  • Sealants including fibrin-, collagen-, synthetic polymer- and protein-based sealants, act as a physical barrier to fluid and air, and can be used to promote wound healing, tissue regeneration and clot formation.
  • sealants are generally time-
  • sealants cannot be used in high-tension areas.
  • Adhesives for example, cyanoacrylate glues, have the advantage that they are
  • Cyanoacrylates also harden rapidly; therefore, the time available to the surgeon
  • Laser tissue solders or "light-activated adhesives," are a possible alternative for
  • soldering is a bonding technique in which a protein solder is applied to the surface of the
  • tissue(s) to be joined and laser energy is used to bond the solder to the tissue surface(s).
  • soldering techniques is the need to supply light energy to the repair site to activate the adhesive. As a result, such techniques are only suitable for a limited number of clinical
  • This composite has exhibited surprisingly good tensile strength and consistency when
  • adhesive sealing or repairing device for biological tissue. It may also be used as a depot
  • the composite can be any suitable material for drugs in providing medication to a wound or repair site.
  • the composite can be any suitable material for drugs in providing medication to a wound or repair site.
  • tissue- to-tissue or tissue-to-biocompatible implant precisely positioned across, on top of, or between two materials to be joined (i.e. tissue- to-tissue or tissue-to-biocompatible implant). Proper alignment is accomplished within
  • the composite can be applied to the time period before the adhesive sets or hardens.
  • the composite can be applied to the time period before the adhesive sets or hardens.
  • repair site more quickly and easily than sutures or adhesives alone.
  • application of the composite can provide a watertight seal at the repair site when required.
  • Examples of external or topical applications for the composite include, but are not limited to, wound closure from trauma or at surgical
  • the invention offers the potential for quick application in the field by less
  • the composition includes a scaffold including at least
  • non-light activated adhesive including at least one of a biological material, biocompatible
  • the non-light activated adhesive is combined with
  • the scaffold to form a composite that, when used to repair biological tissue, has a tensile
  • a method for repairing, joining, aligning, or sealing biological tissue includes the steps of
  • the product includes a
  • biodegradable non-light activated adhesive and means for coupling the scaffold and the
  • Fig. 1 is a graph summarizing results obtained during the studies described in
  • Example 1 comparing the maximum strength of repairs formed in organ specimens
  • Fig. 2 is a graph summarizing results obtained during the studies described in
  • Example 1 comparing the maximum strength of repairs formed in vascular specimens quoted as a percentage of native tissue strength
  • FIGs. 3 A-3B are photographs showing the surgical technique used in Example 2 to
  • Fig.4A-4C are photographs showing the surgical technique used in Example 2 to
  • Fig. 5 is a photograph of the incision sites on the dorsal skin of a rat taken immediately following the repair of each incision using one of the four techniques described in Example 3;
  • Fig. 6 is a graph summarizing results obtained during the studies described in
  • Example 3 showing the tensile strength of skin repairs performed using four different
  • Fig. 7 is a graph summarizing results obtained during the studies described in
  • Example 3 showing the time to failure of the skin repairs seven days postoperatively
  • Fig. 8A is a low magnification photomicrograph from Example 3 of rat skin
  • E keratinized squamous epithelium
  • D dermis
  • ST suture & suture tract
  • Fig. 8B is a low magnification photomicrograph from Example 3 of rat skin
  • D dermis
  • SIR superficial inflammatory reaction
  • M subdermal muscular layer
  • Fig. 8C is a low magnification photomicrograph from Example 3 of rat skin
  • D dermis
  • SIR superficial inflammatory reaction
  • M subdermal muscular layer
  • Fig. 9 is a graph summarizing results obtained during the studies described in
  • Example 3 showing the tensile strength of skin repairs performed using four different repair techniques fourteen days postoperatively;
  • Fig. 10 is a graph summarizing results obtained during the studies described in Example 3, showing the time to failure of the skin repairs fourteen days postoperatively;
  • Fig. 11 is a graph summarizing tensile strength data from the studies described in
  • Fig. 12 is a graph comparing time of failure for repairs tested in the studies
  • Fig. 13 A is an electron micrograph (magnification: 120x) of the smooth (intimal)
  • Fig. 13B is an electron micrograph (magnification: 120x) of the irregular surface
  • Fig. 14A is an electron micrograph (magnification: 120x) of the smooth (intimal)
  • Fig. 14B is an electron micrograph (magnification: 120x) of the irregular surface
  • Fig. 15 is a graph summarizing tensile strength results from the studies described
  • Fig. 16 is a graph summarizing time to failure results from the studies described in
  • Fig. 17 is a graph summarizing tensile strength results from the studies described in Example 6;
  • Fig. 18 is a graph summarizing time to failure results from the studies described in
  • Figs. 19A-19D are electron micrographs (magnification: 120x) of irregularities
  • Fig. 20 is a graph summarizing tensile strength results from the studies described
  • Fig.21 is a graph summarizing time to failure results from the studies described in
  • Figs. 22A-22G are photographs of example embodiments of the disclosed
  • Fig. 23 is a schematic representation of example embodiments of the disclosed
  • Figs. 24A and 24B are schematic representations of one embodiment of a form of
  • Fig. 25 is another embodiment of a form of packaging the composite, showing the
  • Figs. 26 A and 26B are an illustrated representation of an application of one
  • biologic j-uaterials may each be composed of either biologic or synthetic materials.
  • biologic j-uaterials that may be used as adhesives include, but are not limited to, serum albumin,
  • Examples of synthetic materials suitable for use as adhesives include, but are not limited
  • cyanoacrylate e.g., ethyl-, propyl-, butyl- and octyl- glues.
  • the biologic materials are,
  • cyanoacrylates are not in themselves biodegradable, but processes can be applied to make
  • an activator or initiator (other than laser energy) to cause or accelerate bonding.
  • polymerization of octyl-cyanoacrylates can be accelerated through contact with
  • the scaffold operates to ensure continuous, consistent alignment of the apposed
  • the scaffold also helps ensure that the tensile strength of the apposed edges is sufficient for healing to occur without the use of sutures, staples, clips, or other mechanical closures or means of reinforcement. By keeping the tissue edges in direct
  • the scaffold helps foster primary intention healing and direct re-apposition
  • the scaffold functions as a bridge or framework for the apposed edges of severed tissue.
  • the scaffold is either a synthetic or biological material.
  • suitable biological scaffold comprises SIS (small intestine submucosa), polymerized
  • synthetic materials suitable for use as a scaffold include, but are not limited to, various synthetic materials suitable for use as a scaffold.
  • poly(alpha ester)s such as poly(lactic acid) (PLA), poly(glycolic acid) (PGA), poly(L-
  • PLGA lactic-co-glycolic acid
  • PGA poly(.epsilon.-caprolactone)
  • glycol PEG
  • poly(alpha ester)s PEG
  • poly(ortho ester)s PEG
  • poly(anhydrides) PEG
  • the scaffold is engineered for specific applications of
  • the composite by adjusting one or more of its properties.
  • the scaffold by adjusting one or more of its properties.
  • the scaffold includes a smooth surface.
  • the scaffold includes an irregular
  • the scaffold Key properties of the scaffold are surface regularity or irregularity, elasticity, strength, porosity, surface area, degradation rate, and flexibility.
  • the scaffold is engineered to
  • antibiotics antibiotics, anesthetics, anti-inflammatories, bacteriostatic or bacteriocidals, chemotherapeutic agents, vitamins, anti- or pro- neo vascular or tissue cell growth factors,
  • hemostatic and thrombogenic agents This is accomplished by altering the
  • macromolecular structure of the scaffold in order to adjust, for example, its porosity and/or degradation rate.
  • Porous synthetic polymer scaffolds were prepared from poly(L-lactic-co-glycolic
  • the scaffolds were cast by dissolving 200mg PLGA
  • the salt was leached out of the polymer scaffolds by immersion in filtered deionized
  • the PLGA scaffolds used for incision repair were cut into rectangular pieces with dimensions of 12 ⁇ 2 mm long by 5 ⁇ 1 mm wide.
  • the scaffolds used for Group I were
  • BSA bovine serum albumin
  • cyanoacrylate (Vetbond, 3M) was applied to the scaffolds used for Group II using a 22-G
  • Porcine tissue specimens were harvested approximately 30 minutes after sacrificing the animals. Tissue specimens were stored in phosphate buffered saline for a
  • the laser light was coupled into a 660- ⁇ m diameter silica fiber bundle and focused onto the scaffold surface with an imaging hand-piece connected at the end of the fiber.
  • the laser beam was delivered through the same fiber as the 808-nm beam.
  • the laser beam was delivered through the same fiber as the 808-nm beam.
  • microscissors were used to cut in from each edge with care to leave a 5 ⁇ 1 mm bridge of
  • Group I repairs formed on the ureter were the most successful followed by the small intestine, sciatic nerve, spleen, atrium, kidney, muscle, skin and ventricle.
  • the repairs on the ureter, small intestine and sciatic nerve achieved 81 - 83 % of the strength of native tissue while repairs on the spleen, atrium and kidney attained approximately 66- 72% of the strength of native tissue.
  • Group I repairs performed on the liver, pancreas, lung and gallbladder specimens resulted in a very weak bond between the scaffold- enhanced solder and tissue, at only approximately 24-33% of the strength of native specimens.
  • the strongest Group I vascular repairs were achieved in the carotid arteries, aorta (adventitia) and femoral arteries where breaking strengths of approximately 83%, 78% and 77% of their native tissue specimens, respectively, were achieved.
  • Group H repairs utilizing the cyanoacrylate-scaffold composite all performed extremely well. Bonds formed using the Group H composites were on average 34% stronger than Group I and HI organ repairs and 24% stronger than Group I and HI vascular repairs.
  • Group HI repairs performed utilizing a single 4-0 suture revealed the high variability in tensile strength associated with this repair technique. This method is highly dependent upon operator skill and technique as indicated by the large standard deviations seen within each tissue group; as well as, tissue type.
  • organ repairs Fig. 1 only: mean standard deviations for all tissue types in Group I, Group H and Group HI, were 7%, 6% and 30%, respectively.
  • vascular repairs Fig. 2 only: mean standard deviations for all tissue types in Group I, Group H and Group HI, were 6%, 6% and 22%, respectively.
  • the 'Glue' group utilized 2-octyl-cyanoacrylate applied directly to the sclera with the spread-out tendon (superior rectus muscle) held in the desired position (Fig. 3 A)
  • poly(L-lactic-co-glycolic acid) membrane to act as a scaffold for the glue between the
  • FIGs. 3B and 4C show the typical postoperative appearance of the
  • the 'Composite' group provided a
  • SIS small intestinal submucosa
  • SIS small intestinal submucosa
  • a synthetic biodegradable material fabricated from poly(L-lactic-co-glycolic acid)
  • Porous synthetic polymer scaffolds were prepared from PLGA, with a
  • the scaffolds were cast by dissolving 200mg PLGA (Sigma Chemical
  • the polymer solution was then spread to cover the bottom surface of a
  • the scaffolds were then air dried and stored at room temperature until required.
  • the PLGA scaffolds were cut into rectangular pieces with dimensions of 15 ⁇ 0.5 mm
  • the average thickness of the scaffolds determined by
  • the scaffolds Prior to use for tissue repair, the scaffolds were soaked in saline for a period of at least
  • SIS is prepared from decellularized porcine submucosa, which essentially contains intact extracellular matrix proteins, of which collagen is the most prevalent.
  • Sheets of SIS with surface dimensions of 50 x 10 cm and an average thickness of
  • each rat using a #15 scalpel blade (1) left rostral parasagital; (2) right rostral parasagital;
  • Dermabond ( ⁇ 0.035mL) were applied to the irregular surface of the scaffolding using a
  • Fig. 5 shows a photograph of
  • Hematoxylin and Eosin were used as controls
  • SIR inflammatory reaction
  • Dermabond acts as a brittle scaffold that
  • Cyanoacrylate is brittle and tends to lose adhesion either through
  • COMPOSITE The composite acts to keep the dermis in tight apposition
  • apposed edges may allow the apposed edges to move in conjunction with each other as a unit for a longer period of time and over a greater range of stresses than cyanoacrylate alone.
  • SIS small intestinal submucosa
  • Porous synthetic polymer scaffolds were prepared from PLGA, with a
  • the scaffolds were cast by dissolving 200mg PLGA (Sigma Chemical
  • the polymer solution was then spread to cover the bottom surface of a
  • the scaffolds were then air dried and stored at room temperature until required.
  • the PLGA scaffolds were cut into square pieces with dimensions of 10 ⁇ 0.5 mm long by
  • the scaffolds were soaked in saline for a period of at least
  • SIS is prepared from decellularized porcine submucosa, which essentially contains intact extracellular matrix proteins, of which collagen is the most prevalent.
  • Sheets of SIS with surface dimensions of 50 x 10 cm and an average thickness of
  • saline for at least 10 minutes prior to being using for tissue repair.
  • MTS Material Strength Testing Machine (858 Table Top System, MTS, Eden Prairie,
  • the composite formed of either a biocompatible (i.e. PLGA) or biological (i.e. SIS) scaffold and an adhesive provided significantly enhanced tensile strength of the
  • the composite including either a biocompatible (i.e. PLGA) or biological (i.e.
  • the composite provides a stronger, more durable and consistent adhesion than the adhesive alone.
  • This theory is also supported by several ex vivo experiments demonstrating enhanced tensile strength of irregular porous versus smooth surface
  • PLGA PLGA
  • SIS small intestinal submucosa
  • Porous synthetic polymer scaffolds were prepared from PLGA, with a
  • the scaffolds were cast by dissolving 200mg PLGA (Sigma Chemical
  • the polymer solution was then spread to cover the bottom surface of a
  • the PLGA scaffolds were cut into square pieces with dimensions of 10 ⁇ 0.5 mm long by 10 ⁇ 0.5 mm wide.
  • the scaffolds were soaked in saline for a period of at least
  • SIS is prepared from decellularized porcine submucosa, which essentially
  • Sheets of SIS with surface dimensions of 50 x 10 cm and an average thickness of
  • saline for at least 10 minutes prior to being using for tissue repair.
  • Bovine tissue specimens were harvested approximately 30 minutes after
  • Tissue specimens were stored in phosphate buffered saline for a
  • tissue specimen was cut into small rectangular pieces with dimensions of about 20 mm long by 10 mm
  • thoracic aorta included the thoracic aorta, liver, spleen, small intestine, and lung.
  • MTS Material Strength Testing Machine (858 Table Top System, MTS, Eden Prairie,
  • SIS scaffolds are shown in Figs. 13 A and 13B, respectively. Electron micrographs of both the smooth and irregular surfaces of the PLGA polymer scaffolds are shown in Figs. 14A
  • the smooth surface of the SIS scaffolds represents the luminal
  • the smooth surface of the PLGA scaffolds represents the side of the scaffold that was cast against the surface of the glass Petri dish.
  • the irregular, rough surface of the composite provides a greater tensile strength immediately after the adhesion is initiated than does the cyanoacrylate alone,
  • the smooth surface of the composite provides a small increase in tensile strength
  • wound edges are only apposed by whatever artificial means was employed to repair the incision; these methods are subject to the limitations of how they grasp the tissues and anchor them together; b) during the early surgical period, there has not been significant
  • tissue repair can achieve a tissue repair
  • Biodegradable polymer scaffolds of controlled porosity were fabricated with poly(L-lactic-co-glycolic acid) and salt particles
  • the scaffolds were doped with
  • Ethicon 's DermabondTM a 2-octyl-cyanoacrylate adhesive.
  • the tensile strength of repairs performed on bovine thoracic aorta and small intestine were measured and the time to failure was recorded.
  • Data relating to Example 6 is shown in Tables J- 1 and J-2 of the Appendix, and in
  • lactic:glycolic acid ratio of 50:50 using a solvent-casting and particulate leaching technique.
  • the scaffolds were cast by dissolving 200mg PLGA (Sigma Chemical
  • the polymer solution was then spread to cover the bottom surface of a
  • the scaffolds were then air dried and stored at room temperature until required.
  • the PLGA scaffolds were cut into rectangular pieces with the desired surface dimensions
  • the scaffolds were soaked in saline for a period of at least 10 minutes.
  • Bovine tissue specimens were harvested approximately 30 minutes after sacrificing the animal. Tissue specimens were stored in phosphate buffered saline for a
  • MTS Material Strength Testing Machine (858 Table Top System, MTS, Eden Prairie,
  • tissue specimens were kept moist during the procedure.
  • the composite structure allows for distribution of forces across the entire repair
  • Geometry may not be completely unimportant (as one would expect when dealing
  • Example 7 Composites Containing Cyanoactylate Adhesives and Biodegradable Scaffolds: Custom Manufactured Scaffold Surfaces for Improved Tissue Repair
  • Porous PLGA scaffolds were fabricated using four different
  • Figs. 19A - 19D show electron micrographs of the irregularities added to the
  • Synthetic polymer scaffolds were prepared from PLGA, with a lactic :glycolic acid
  • the scaffolds were cast by dissolving 250mg PLGA in 2.5ml
  • the PLGA scaffolds were cut into square pieces with dimensions of 10 ⁇ 0.5 mm
  • the average thickness of the scaffolds determined by
  • the scaffolds Prior to use for tissue repair, the scaffolds were soaked in saline for a period of at least 10 minutes.
  • Bovine tissue specimens were harvested approximately 30 minutes after
  • Tissue specimens were stored in phosphate buffered saline for a
  • Example 3 are also included for comparison. 7.4 Discussion
  • irregular scaffold surfaces can be
  • scaffolds may be custom manufactured, including porosity (including pore size and
  • the composite exhibits more favorable
  • bioadhesives e.g., cyanoacrylate
  • bioadhesives alone e.g., cyanoacrylate
  • Patches prepared using the adhesive composites can be used in a non-
  • Figs. 22A-22G show photographs of exemplary embodiments of a scaffold
  • the scaffold has a rectangular or square shape.
  • Fig. 22A shows that the scaffold may take the
  • Fig. 22B shows that at least a portion of the scaffold's surface may be irregular
  • Fig. 22C shows that at least a portion of the scaffold surface may be smooth.
  • composite may take a variety of forms and/or shapes.
  • Figs. 22D and 22E show that the scaffold may be rolled in a tight roll (Fig. 22D)
  • Fig. 22E shows how the scaffold may retain its rolled shape after
  • Fig. 22G shows that the scaffold may be unrolled after being rolled
  • Fig. 23 shows a schematic representation of
  • the composite of the present invention may be created by a variety of methods or
  • a physician or other health care provider may place the scaffold
  • the adhesive may be applied to the scaffold and then the
  • the adhesive may be placed at the repair site first and then the scaffold applied.
  • Additional adhesive material may be applied to the site before or after the scaffold is
  • the composite of the present invention may be designed and packaged in a variety
  • the composite is packaged in an inert cellophane-like material.
  • the inert material peels off the surface of the composite to
  • the packaged item may be made available in a variety of sizes and shapes as appropriate for various uses or applications.
  • the composite is supported by one or two rollers made of
  • rollers may be configured to be disposable or reusable.
  • the composite is wrapped around the roller or rollers to form a scroll.
  • the scroll is unrolled to apply the composite to a wound or repair site; for example, a curved or irregular
  • a double roller scroll is particularly advantageous in a non-sterile setting (such as
  • a single roller scroll is
  • Yet another alternative packaging technique involves positioning a thin,
  • the membrane protects the composite until it is ready to be used. Upon application of the composite to a wound or repair site, the expendable membrane ruptures or fractures, for
  • a grip for example a ring (similar to that used in laser printer cartridges), is attached.
  • a grip for example a ring (similar to that used in laser printer cartridges), is attached.
  • a separator is positioned between the scaffold and the adhesive to isolate the
  • the separator is positioned between the adhesive and an adhesive activator to isolate the adhesive from its activator until the
  • a saline or protein is needed for use (Fig. 25).
  • a saline or protein is needed for use (Fig. 25).
  • VEGF vascular endothelial growth factor
  • the right-hand side of Fig. 25 shows how the packaged composite may be stacked for storage.
  • two separators may be provided.
  • first separator may be positioned between the scaffold and the adhesive, and a second
  • one grip may be provided, which operates to remove both separators at once.
  • the composite can be modified to provide biologically active materials to biological tissue.
  • the controlled release of various dopants including hemostatic and nicotine
  • thrombogenic agents antibiotics, anesthetics, various growth factors, enzymes, anti- inflammatories, bacteriostatic or bacteriocidal factors, chemotherapeutic agents, anti-
  • angiogenic agents and vitamins can be added to the composite to assist in the therapeutic
  • the degradation rate of the composite, and consequently the drug delivery rate can be controlled by altering the macromolecular structure of the device or a portion thereof.
  • Figs. 26 A and 26B show an example of how the composite may be used to deliver
  • VEGF vascular endothelial growth factor
  • the composite When combined with the adhesive to form the composite, the composite is then
  • the elasticity, strength, and flexibility of the composite can be

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  • Health & Medical Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Composite Materials (AREA)
  • Veterinary Medicine (AREA)
  • Epidemiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Materials Engineering (AREA)
  • Public Health (AREA)
  • Surgery (AREA)
  • Dermatology (AREA)
  • Medicinal Chemistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Materials For Medical Uses (AREA)
  • Adhesives Or Adhesive Processes (AREA)

Abstract

L'invention concerne un composite adhésif non actionné par la lumière ainsi qu'un procédé et un système convenant à des applications médicales et chirurgicales. Ce composite comprend un échafaudage et un adhésif non actionné par la lumière. Cet échafaudage et cet adhésif non actionné par la lumière comprennent des matériaux biologiques, biocompatibles ou biodégradables.
EP04705242A 2003-01-24 2004-01-26 Composite adhesif non actionne par la lumiere, systeme et procedes associes Withdrawn EP1587551A2 (fr)

Applications Claiming Priority (5)

Application Number Priority Date Filing Date Title
US44248503P 2003-01-24 2003-01-24
US442485P 2003-01-24
US10/610,068 US20050004599A1 (en) 2003-06-30 2003-06-30 Non-light activated adhesive composite, system, and methods of use thereof
US610068 2003-06-30
PCT/US2004/001945 WO2004067045A2 (fr) 2003-01-24 2004-01-26 Composite adhesif non actionne par la lumiere, systeme et procedes associes

Publications (1)

Publication Number Publication Date
EP1587551A2 true EP1587551A2 (fr) 2005-10-26

Family

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Family Applications (1)

Application Number Title Priority Date Filing Date
EP04705242A Withdrawn EP1587551A2 (fr) 2003-01-24 2004-01-26 Composite adhesif non actionne par la lumiere, systeme et procedes associes

Country Status (2)

Country Link
EP (1) EP1587551A2 (fr)
WO (1) WO2004067045A2 (fr)

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4837285A (en) * 1984-03-27 1989-06-06 Medimatrix Collagen matrix beads for soft tissue repair
US5292362A (en) * 1990-07-27 1994-03-08 The Trustees Of Columbia University In The City Of New York Tissue bonding and sealing composition and method of using the same
AU1461592A (en) * 1991-02-07 1992-09-07 Fibratek, Inc. Fibrinogen based adhesive
US6015474A (en) * 1997-06-20 2000-01-18 Protein Polymer Technologies Methods of using primer molecules for enhancing the mechanical performance of tissue adhesives and sealants
US6544541B1 (en) * 1999-06-02 2003-04-08 Cardiovascular Solutions, Inc. Devices and compounds for treating arterial restenosis
US6592890B1 (en) * 1999-10-20 2003-07-15 Oxibio, Inc. Conveyance of anti-infective activity to wound dressings
HUP0302301A2 (hu) * 2000-05-22 2003-10-28 Arthur C. Coffey SIS és vákuumos kötés kombinációja, és az ilyen kötést hasznosító eljárás sebek kezeléséhez

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO2004067045A3 *

Also Published As

Publication number Publication date
WO2004067045A2 (fr) 2004-08-12
WO2004067045A3 (fr) 2004-11-18

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