WO2006038866A1 - Revetement ameliore comprenant une proteine polyphenolique bioadhesive provenant d'une moule formant un byssus - Google Patents

Revetement ameliore comprenant une proteine polyphenolique bioadhesive provenant d'une moule formant un byssus Download PDF

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Publication number
WO2006038866A1
WO2006038866A1 PCT/SE2005/001458 SE2005001458W WO2006038866A1 WO 2006038866 A1 WO2006038866 A1 WO 2006038866A1 SE 2005001458 W SE2005001458 W SE 2005001458W WO 2006038866 A1 WO2006038866 A1 WO 2006038866A1
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Prior art keywords
mefp
medical device
qcm
coated
gold
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PCT/SE2005/001458
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English (en)
Inventor
Magnus Qvist
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Bio Polymer Products Of Sweden Ab
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Priority claimed from SE0402379A external-priority patent/SE0402379D0/xx
Application filed by Bio Polymer Products Of Sweden Ab filed Critical Bio Polymer Products Of Sweden Ab
Publication of WO2006038866A1 publication Critical patent/WO2006038866A1/fr

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    • 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
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/08—Materials for coatings
    • A61L31/10—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
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/28—Materials for coating prostheses
    • A61L27/34—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
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/54—Biologically active materials, e.g. therapeutic substances
    • 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
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/16—Biologically active materials, e.g. therapeutic substances
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
    • A61L2300/252—Polypeptides, proteins, e.g. glycoproteins, lipoproteins, cytokines
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/606—Coatings
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/606—Coatings
    • A61L2300/608—Coatings having two or more layers

Definitions

  • the present invention relates to surface treatments, preparations, or coatings which reduce the immunogenicity of medical devices and equipment. More specifically, the invention relates to surface treatments which reduce the immunogenicity of im ⁇ planted or implantable medical devices.
  • living cells may be cultured in laboratory equipment for medical use or further research; broken, deformed, or missing bones can be repaired with implanted plates, rods or pins; a defective or diseased organ such as a heart may be replaced with a mechanical, chimeric, or animal organ.
  • C3 Complement factor 3
  • QCM Quartz Crystal Microbalance
  • the other pathway of reaction to a foreign body is surface-associated blood coagula ⁇ tion.
  • Blood cells particularly platelets, can bind to the surface of certain materials. Depending on the size and location, such a coagulated surface can cause a thrombo ⁇ sis.
  • Assays utilizing platelets can be used to determine the likelihood of reaction of a proposed biomedical material.
  • US 6,497,729 discloses an implant coating comprising a bioactive polymer layer self-assembled with metal cations, wherein the bioactive polymer further contains at least one tissue response modifier.
  • the bioactive polymer is not crosslinked by oxi ⁇ dation.
  • WO 01/44401 relates to a bioadhesive composition comprising a polyphenolic pro ⁇ tein, and how the composition can be applied as an adhesive in ophthalmic therapy. None is disclosed about coating implants in order to reduce immunogenicity.
  • WO 03/051418 describes a method and kit for providing a bioadhesive binding or coating with polyphenolic mussel proteins in a strongly alkaline solution. None is mentioned about coating implants.
  • US 2002/0111694 Al relates to a method of joining biopolymers to a metal hydride surface by electrolysis.
  • the bioadhesive composition comprises a) a bioadhesive polyphenols protein derived from a byssus-forming mussel, which protein comprises 30-300 amino acids and consisting essentially of tandemly linked peptide repeats comprising 3-15 amino acid residues, wherein at least 3 % and pref ⁇ erably 6-30 % of the amino acid residues of said bioadhesive polyphenols protein are DOPA; and, in case the bioadhesive composition is not going to be coated by a further layer b) a non-enzymatic oxidising agent such as hydrogen peroxide, nitroprusside ions or periodate ions.
  • a non-enzymatic oxidising agent such as hydrogen peroxide, nitroprusside ions or periodate ions.
  • the bioadhesive composition may be oxidized or non-oxidized depend ⁇ ing on whether a further layer is to be coated on the bioadhesive composition.
  • the bioadhesive composition may is coated by a further layer comprising at least one compound selected from the group of heparin, hyalu ⁇ ronic acid, dextransulphate, heparansulphate, sulphated carbohydrates, non- sulphated carbohydrates, polyvinylpyrrolidone, chitosan, modified polyethylene species, fibrinogen and polyimine.
  • the implantable medical device is selected from the group consisting of stents, contact lenses, insulin pumps, pacemakers, implantable defibrillators, re ⁇ placement organs, dental implants, sutures and prosthetic devices.
  • the medical device that is covered with the bioadhesive composition may be com ⁇ prised of a material selected from the group consisting of polyethylene, polyethylene terephthalate, polystyrene, glass, gold, and titanium.
  • the implantable medical device may, of course be used in medical treatment.
  • certain terms employed in the specification, examples, and ap ⁇ pended claims are collected here.
  • animal refers to mammals, preferably mammals such as live stock or humans.
  • a "patient” or “subject” as described herein can mean either a human or non-human animal.
  • biomedical refers to a field of work which encompasses the medical arts, biotechnology, and all research and applications which have some relation to medical treatment.
  • the term includes materials research where the materials will be used in an application where they are in contact with living cells or tissues or with secondary materials which will later contact living cells or tissues. Examples of such materials research include contact lenses and syringes.
  • an “effective amount” refers to an amount of a coating material which, when ap ⁇ plied according to the present invention, provides a sufficient layer to render the coated surface sufficiently non-reactive as taught by the present invention.
  • immunogenic refers to items which trigger, cause or exacerbate an im ⁇ mune response in an animal. It also encompasses a coagulation response to foreign bodies.
  • antigenic can be used interchangeably.
  • non-immunogenic refers to items which do not independently trigger, cause or ex ⁇ acerbate in immune response in an animal.
  • a non-immunogenic material when in contact with living cells or tissues, is chemically and biologically inert to its sur ⁇ roundings and does not interact or react with the living tissue.
  • references to the present inventive materials as non-reactive or inert is a relative comparison and not necessarily an absolute property.
  • the terms "materials” and “materials, devices and equipment” re ⁇ fer to all compounds, preparations, items, and the like, which can be used as de ⁇ scribed herein.
  • “materials” includes various metals and plastics which may be used to make a medical or biomedical apparatus or tool. The terms also encompass all items which can or are utilized in a biomedical application. Examples include petri dishes, sutures, stents, contact lenses, dental implants, and transplant organs.
  • polyphenolic protein As disclosed herein, the terms "polyphenolic protein,” “mussel adhesive protein,” “MAP,” and “Mefp-1” relate to a protein which is synthesized, recombinantly produced, or derived from byssus-forming mussels. Examples of such mussels are mussels of the genera Mytilus, Geukensia, Aulacomya, Phragmatopoma, Dre- issenia and Brachiodontes. Suitable proteins have been disclosed in a plurality of publications, e.g.
  • a characteristic feature of such proteins is a comparatively high amount of positively charged lysine resi ⁇ dues, and in particular the unusual amino acid DOPA (L-3,4- dihydroxyphenylalanine).
  • a protein suitable for use in the present invention has an amino acid sequence in which at least 3 % and preferably 6 - 30 % of the amino acid residues are DOPA. Exemplary peptide units are noted below. The amino acid sequences of these proteins are variable; meaning the scope of the present invention is not limited to the exemplified sub sequences below. A skilled worker would recognize that other proteins from different sources, including re ⁇ combinantly produced proteins, can be regarded as equivalent.
  • Val-Gly-Gly-DOPA-Gly-DOPA-Gly-Ala-Lys b) Ala-Lys-Pro-Ser-Tyr-diHyp-Hyp-Thr-DOPA-Lys cO Thr-Gly-DOPA-Gly-Pro-Gly-DOPA-Lys d) Ala-Gly-DOPA-Gly-Gly-Leu-Lys e) Gly-Pro-DOPA-Val-Pro-Asp-Gly-Pro-Tyr-Asp-Lys f) Gly-Lys-Pro-Ser-Pro-DOPA-As ⁇ -Pro-Gly-DOPA-Lys g) Gly-DOPA-Lys h) Thr-Gly-DOPA-Ser-Ala-Gly-DOPA-Lys i) Gln-Thr-Gly-DOPA-Val-Pro-Gly-DOPA-Lys j
  • surface is to be interpreted broadly and may comprise virtually any face of any item. Examples of surfaces for which the invention is particularly well suited include the outer portion of a contact lens, the portion of a metal pin which will con ⁇ tact or be contacted by bodily substances when in use, and the lining of multi-well plates that will be contacted by test materials.
  • Figure 1 schematically represents adhesion of Mefp-1 to a hydrophobic QCM sur ⁇ face
  • Figure 2 depicts the dissipation results measured during binding of Mefp-1 to a QCM surface
  • Figure 3 depicts further dissipation results measured during binding of Mefp-1 to a QCM surface
  • Figure 4 presents in table form the average decrease in dissipation of a QCM surface after crosslinking the Mefp-1 layer with various agents
  • Figure 5 depicts the steps in evaluation the formation of an Mefp-1 layer on a gold QCM surface and the reaction of that layer with blood serum and antibodies;
  • Figure 6 schematically represents both oxidized (crosslinked) and non-oxidized
  • Mefp-1 layers adsorbing fibrinogen, heparin, or hyaluronic acid layers
  • Figure 7 depicts QCM mass measured for two control QCM surfaces containing only a gold layer
  • Figure 8 depicts QCM mass measured for two test QCM surfaces containing a gold layer and oxidized Mefp-1;
  • Figure 9 depicts QCM mass measured for two test QCM surfaces containing a gold layer, oxidized Mefp-1 and heparin;
  • Figure 10 depicts QCM mass measured for two test QCM surfaces containing a gold layer, oxidized Mefp-1 and fibrinogen;
  • Figure 11 depicts QCM mass measured for two test QCM surfaces containing a gold layer, non-oxidized Mefp-1 and hyaluronic acid;
  • Figure 12 depicts QCM mass measured for two test QCM surfaces containing a gold layer, oxidized Mefp-1 and hyaluronic acid;
  • Figure 13 shows QCM mass for a QCM crystal as a Mefp-1 layer is added, a further protein layer is added, then the surface is cross linked;
  • Figure 14 depicts QCM mass measured with variances in pH during Mefp-1 binding to a QCM surface
  • Figure 15 depicts QCM mass for QCM crystals with various coatings
  • Figure 16 tabulates the increase in mass measured for various QCM crystals as a percentage increase
  • Figure 17 tabulates the increase in mass measured for various QCM crystals as a measured amount increase
  • Figure 18 shows tabulated data of mass measured for selected device coatings.
  • Figure 19 shows tabulated data of mass measured for Mefp-1 and select common biomedical application materials.
  • the present invention describes biomedically-acceptable coating compositions and methods which could be used to coat any surface with such compositions.
  • Composi ⁇ tions according to the present invention are particularly useful when employed for materials which ideally are to be rendered non-immunogenic, non-toxic, non- irritating, and non-allergenic. Such materials are known in the art today and will continue to be developed as technology progresses.
  • Quartz Crystal Microbalance employs a piezoelectric quartz sensor that can indicate change in resonance using electric pulses. Adsorbed proteins increase the mass of the sensor surface, which relates to a decrease in reso ⁇ nance frequency. Properties of the sensor surface can be monitored, providing an indication of the immunogenicity or the likelihood to cause surface-related blood coagulation. These are often measured in terms of higher or lower immunogenicity or coagulability.
  • Hydrophilic titanium oxide surfaces generally have high activation of coagulation, but low immunogenicity.
  • titanium particles can be deposited on the crystal in a vacuum.
  • Hydrophobic polymer surfaces such as polystyrene, in contrast, have a low activation of coagulation, but high immuno ⁇ genicity.
  • Hydrophobic polymer coated crystals can be created by dropwise addition of a polystyrene solution on a sensor surface which is rotating at about 5000 rpm. This method deposits a thin layer of polystyrene on the crystal.
  • Example 2 Titanium or Polymer QCM with Optional Mefp-1 and Immunogenicity Thereof
  • Crystals with titanium or polystyrene coatings were prepared as described above.
  • a thin layer of Mefp-1 was adsorbed onto the titanium or polystyrene layers by incu ⁇ bating the titanium or polystyrene coated crystal with aqueous Mefp-1 (lOOug Mefp- 1/ml).
  • Sensors both those modified only with titanium or polystyrene layers and those with a further Mefp-1 layer were tested in QCM equipment.
  • Fresh human blood serum, which contains immune compliment components was placed on the surfaces for 30 minutes. Afterward, the surfaces were washed.
  • Rabbit anti-human C3 antibodies were added to the crystals. Thirty (30) minutes after the addition of the rabbit antibodies, the resonance frequency of the crystals was measured.
  • Mefp-1 coatings were considered able to render a surface less immunoreactive but potentially more likely to induce coagulation.
  • the properties of Mefp-1 coatings which could be crosslinked (e.g., oxidized) or non- crosslmked (non-oxidized), and potentially further coated with proteins were evalu ⁇ ated. Again, QCM-D measurements were conducted.
  • a crystal was coated with a self-assembly monolayer (SAM) of gold. The gold crystal was washed in a UV/ozone chamber for 10 minutes then placed in a 1 :1 :5 solution of 25% H 2 O 2 , 30% NH 3 and MQ, respectively, for 5 minutes at 7O 0 C.
  • the surface was made hydrophobic by incubating the crystal for at least 12 hours in HS(CH 2 )i 7 CH 3 dissolved in hexane. Care was taken to ensure the hexane did not evaporate and that the exposure time was sufficient.
  • the crystal was then placed in a QCM-D chamber and the chamber was pro ⁇ grammed.
  • Acetate buffer, 0.1 M (75 mM NaCl, pH 5.5) was added. Once a base line with up to 5 Hz frequency had been maintained over 5 minutes, the program was started. Afterward, the surface of the crystal was exposed to 1 ml Mefp-1 (25 ⁇ g/ml) dissolved in acetate buffer for 50 minutes. The surface was washed with 1 ml ace ⁇ tate buffer for 5 minutes.
  • FIG. 1 provides a schematic overview of Mefp-1 coating on a QCM surface, both oxidized and non-oxidized, and Figures 2 and 3 depict dissipation measured when various crosslinking agents were employed. Figure 4 shows those dissipation results in tabular form.
  • Figure 5 correlates the stages of Mefp-1 coating, crosslinking and reacting with blood to the measured mass of the QCM crystal.
  • Example 5 QCM with Gold, Mefp-1, and Fibrogen, Heparin, or Hyaluronic Acid
  • a coating which consisted of two ho ⁇ mogenous molecule layers.
  • the Mefp-1 was oxidized prior to the addition of the second layer, in others, not. By oxidizing the Mefp-1 layer, it is rendered relatively non-reactive. It is therefore easier to achieve molecular adher ⁇ ence to the Mef ⁇ -1 if it is non-oxidized. If the Mefp-1 layer is strongly oxidized, it shrinks and does not stay in contact with the gold surface. The Mefp-1 adheres bet ⁇ ter to polar surfaces, but will bind well to hydrophobic surfaces such as polystyrene.
  • Figure 6 provides a schematic overview of the process of adhering fibrinogen, hepa ⁇ rin, or hyaluronic acid to a Mefp-1 coated gold surface. To the left non-oxidized Mefp-1 is shown, to the right Mefp-1 is oxidized.
  • Example 6 Comparative Evaluations of QCM with Mefp- 1 Evaluations were made of non-oxidized Mefp-1 on gold, oxidized Mefp-1 on gold, and both oxidized and non-oxidized Mefp-1 on gold with a further layer of fibrino ⁇ gen, heparin, or hyaluronic acid. Evaluations were generally conducted in duplicate. As control, a plain QCM with gold SAM coating was measured under the same conditions as the actual experimental materials. Results are provided in Figure 7. Measurements were also taken of a QCM with gold and oxidized Mefp-1 surface, see Figure 8.
  • FIG. 13 illustrates QCM mass measurements where fibrinogen and hyaluronic acid were bound to non- oxidized Mef ⁇ -1, followed by subsequent oxidation. It illustrates that Mefp-1 will crosslink even if another molecule has bound to the Mefp-1.
  • the effect of pH is de ⁇ picted in Figure 14, which compares the mass of a QCM during the application of a Mefp-1 layer.
  • One line, that which rises higher, depicts a crystal where the Mefp-1 was deposited under pH 7.4 conditions, the lower line is a measurement with the same factors but for a pH of 3.5 in the reaction solution. With lower pH conditions, lower Mefp-1 protein binding is observed. At the higher pH more binding occurred, although after washing/crosslinking the excess protein dissipated.
  • Figure 15-17 depicts the measured mass of various QCM crystals.
  • Figure 16 presents the percentage increase in mass in tabular form, whereas Figure 17 depicts,, again in tabular form, the increase in mass in terms of actual values measured. All values represent an average of the duplicate experiments conducted for each QCM coating.
  • Figures 15-17 binding of C3 and subsequent binding of anti-C3 antibodies creates an increased mass.
  • Those QCM with higher measured mass values indicate higher relative immunogenicity of the monolayers formed thereon.
  • the gold SAM alone had the highest measured mass value, meaning it was the most immunogenic and therefore the least desirable coating for use in biomedical applications.
  • a gold SAM QCM with Mefp-1 and fibrinogen monolayers also generates a relatively high immune response.
  • Mefp-1 plus rooster hyaluronic acid monolayers provides less immunoreactiv- ity, Mefp-1 alone even less, heparin and human hyaluronic acid even less.
  • a Mefp-1 plus fibrinogen coating is preferred to a gold surface alone.
  • Mefp-1 with rooster hyaluronic acid is more preferred.
  • Mefp-1 alone is even more preferred.
  • Mefp-1 with heparin or human hyaluronic acid is most preferred in terms of providing the least immunogenic coating for a sur ⁇ face.
  • a gold SAM was used as the base layer.
  • a Mefp-1 layer was adsorbed thereon for 50 minutes followed by NaIO 4 crosslinking.
  • To the Mefp-1 layer one of the mac- romolecules heparin, fibrinogen, human hyaluronic acid and rooster hyaluronic acid were adsorbed for 15 minutes.
  • the surface was exposed to 5% sera for 20 minutes and the immune response evaluated with anti-C3 antibodies. Control surfaces in ⁇ cluded gold with Mefp-1, gold with heparin, gold with fibrinogen, gold with human hyaluronic acid, and gold with rooster hyaluronic acid. Evaluations were made in duplicate. Figure 18 presents the results of the evaluation.
  • a surface coated with Mefp- 1 as an anchor molecule can be used alone or as a base to produce surface coatings with different properties.
  • One contributing factor to the highly immunoreactive results with the control coatings is the relative inability of the large macromolecules to adhere to the hydrophobic cur- face without Mefp-l. This is particularly evident with heparin, where the measured result shows very little ability to bind and this is more indicative of the reactivity of the gold SAM alone than of gold coated with heparin. Where heparin is able to bind to Mefp-1 it can block the gold SAMs immunoreactivity and results in an overall low immunoreactivity, see Figure 18.
  • Example 8 Immunoreactivity of Mefp-1 as compared to other surfaces
  • the low immunoreactivity of Mefp-1 as a coating was compared to other surfaces commonly-used in biomedical material applications.
  • the binding of anti-C3 anti ⁇ bodies was used as a measure of the immune response provoked by certain materi ⁇ als.
  • Results are depicted in Figure 19, where PS represents polystyrene, G represents glass, SAM represents a gold SAM layer, PET represents polyethylene terephtha- late, PE represents polyethylene, Ti is titanium, and Au is gold.
  • Example 9 Further Coatings on a Gold/Mefp-1 QCM Crystal
  • further molecules could be used to form a second monolayer above the Mefp-1.
  • dextransulphate, heparansulphate, and other relevant sul- phated/non-sulphated carbohydrates, or other molecules or macromolecules such as PVP (polyvinylpyrrolidone), chitosan or modified polyethylene species.
  • Example 10 Mefp-1 and Secondary Monolayers on a Medical Device Surface As noted above, surfaces coated with Mefp-1, followed by optional crosslinking and then optional depositing of a second monolayer of heparin or hyaluronic acid pro ⁇ vide surprisingly good results in terms of low immunogenicity. This makes the ap ⁇ plication of such coatings to medical device surfaces desirable.
  • artifi ⁇ cial stents which are typically open-ended tubular structures, are commonly used to support tubular body conduits. Because their intended use includes long-term pres ⁇ ence inside a patient's body, and because their use is often in conjunction with treatment of a medical condition, it is critical that they are as biologically and chemically inert as possible as regards their bodily surroundings.
  • a commercially-available stent could be obtained, such as one made of titanium or a titanium alloy.
  • the stent could be coated with Mefp-1 as taught in the examples above. Such a stent could then be further reacted to form, for example, a heparin monolayer engulfing the outer surface of the stent. After coating, the stent could be used in a patient.
  • commercially-available stents could be so coated, the invention is particularly applicable to stents made from materials heretofore less suitable or unsuitable for medical applications because of their reactivity with living tissue. Such materials may be more readily available, cheaper, and/or easier to use than titanium, and would offer the same degree of inertness as titanium when pro ⁇ vided with a coating according to the present invention.
  • coatable devices include, but are not limited to, contact lenses, insulin pumps and other implantable pumps, pacemakers, implantable defibrillators, replacement organs, including synthetic, xenographic and allographic organs, dental implants, and prosthetic devices such as implants used in restorative or cosmetic surgery.

Abstract

Revêtement amélioré conçu pour des surfaces biomédicales et comprenant une protéine polyphénolique bioadhésive provenant d'une moule formant un byssus, par exemple, Mefp-1 (protéine-1 du pied de mytilus edulis) . Ce revêtement permet de limiter l'immunogénicité de la surface biomédicale revêtue. Cette protéine polyphénolique bioadhésive peut être oxydée ou non oxydée en fonction de la présence d'une autre couche de revêtement de la surface. Cette autre couche peut consister, par exemple, en héparine, acide hyaluronique ou fibrinogène.
PCT/SE2005/001458 2004-10-01 2005-10-03 Revetement ameliore comprenant une proteine polyphenolique bioadhesive provenant d'une moule formant un byssus WO2006038866A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US52243404P 2004-10-01 2004-10-01
SE0402379-2 2004-10-01
US60/522,434 2004-10-01
SE0402379A SE0402379D0 (sv) 2004-10-01 2004-10-01 Improved coating

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US8245473B2 (en) 2006-02-07 2012-08-21 Flooring Industries Limited, Sarl Finishing profile for a floor covering and methods for manufacturing such finishing profile
WO2012152781A1 (fr) * 2011-05-09 2012-11-15 Biopolymer Products Of Sweden Ab Revêtement adhésif apte au séchage
EP2617759A1 (fr) * 2012-01-19 2013-07-24 Acreo Swedish ICT AB Procédé de modification des propriétés d'une surface
US20130251968A1 (en) * 2008-12-04 2013-09-26 University Of Dayton Deposition of Nanocrystalline Calcite on Surfaces by a Tissue and Cellular Biomineralization
WO2014042875A1 (fr) * 2012-09-12 2014-03-20 Boston Scientific Scimed, Inc. Revêtement adhésif anti-migration pour endoprothèse vasculaire
WO2014065941A1 (fr) * 2012-10-25 2014-05-01 Boston Scientific Scimed, Inc. Endoprothèse doté d'un revêtement de silicone collant pour empêcher une migration d'endoprothèse
US8747596B2 (en) 2005-01-12 2014-06-10 Flooring Industries Limited, Sarl Finishing set for floor covering and holder, as well as finishing profile, for a finishing set, and method for manufacturing a finishing profile and a skirting board
WO2014191997A1 (fr) 2013-05-28 2014-12-04 Ramot At Tel-Aviv University Ltd. Microstructures et nanostructures auto-assemblées
WO2015020676A1 (fr) * 2013-08-08 2015-02-12 Boston Scientific Scimed, Inc. Polymère adhésif soluble ou dégradable pour prévenir la migration des stents
CN113209365A (zh) * 2021-05-31 2021-08-06 福州大学 一种多功能封闭止血伤口敷料及其制备方法
CN114452447A (zh) * 2021-08-03 2022-05-10 南京工业大学 贻贝蛋白-聚氨基酸涂层及其制备方法和应用
CN114712332A (zh) * 2022-03-15 2022-07-08 陕西师范大学 一种改性水性材料及其制备方法和应用

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US8747596B2 (en) 2005-01-12 2014-06-10 Flooring Industries Limited, Sarl Finishing set for floor covering and holder, as well as finishing profile, for a finishing set, and method for manufacturing a finishing profile and a skirting board
US8245473B2 (en) 2006-02-07 2012-08-21 Flooring Industries Limited, Sarl Finishing profile for a floor covering and methods for manufacturing such finishing profile
US8245474B2 (en) 2006-02-07 2012-08-21 Flooring Industries Limited, Sarl Finishing profile for a floor covering and methods for manufacturing such finishing profile
EP2036583A3 (fr) * 2007-09-14 2010-04-21 BIOTRONIK VI Patent AG Stent doté d'un revêtement
EP2036583A2 (fr) * 2007-09-14 2009-03-18 BIOTRONIK VI Patent AG Stent doté d'un revêtement
US9371451B2 (en) * 2008-12-04 2016-06-21 Clemson University Research Foundation Deposition of nanocrystalline calcite on surfaces by a tissue and cellular biomineralization
US20130251968A1 (en) * 2008-12-04 2013-09-26 University Of Dayton Deposition of Nanocrystalline Calcite on Surfaces by a Tissue and Cellular Biomineralization
US9260641B2 (en) 2011-05-09 2016-02-16 Biopolymer Products Of Sweden Ab Dryable adhesive coating
WO2012152781A1 (fr) * 2011-05-09 2012-11-15 Biopolymer Products Of Sweden Ab Revêtement adhésif apte au séchage
EP2617759A1 (fr) * 2012-01-19 2013-07-24 Acreo Swedish ICT AB Procédé de modification des propriétés d'une surface
US9993582B2 (en) 2012-09-12 2018-06-12 Boston Scientific Scimed, Inc. Adhesive stent coating for anti-migration
WO2014042875A1 (fr) * 2012-09-12 2014-03-20 Boston Scientific Scimed, Inc. Revêtement adhésif anti-migration pour endoprothèse vasculaire
US10980917B2 (en) 2012-09-12 2021-04-20 Boston Scientific Scimed, Inc. Adhesive stent coating for anti-migration
WO2014065941A1 (fr) * 2012-10-25 2014-05-01 Boston Scientific Scimed, Inc. Endoprothèse doté d'un revêtement de silicone collant pour empêcher une migration d'endoprothèse
WO2014191997A1 (fr) 2013-05-28 2014-12-04 Ramot At Tel-Aviv University Ltd. Microstructures et nanostructures auto-assemblées
EP3427766A1 (fr) * 2013-08-08 2019-01-16 Boston Scientific Scimed, Inc. Polymère adhésif dissoluble ou dégradable pour empêcher la migration d'une endoprothèse
CN105636616A (zh) * 2013-08-08 2016-06-01 波士顿科学国际有限公司 防止支架移位的可溶性或可降解粘合剂聚合物
WO2015020676A1 (fr) * 2013-08-08 2015-02-12 Boston Scientific Scimed, Inc. Polymère adhésif soluble ou dégradable pour prévenir la migration des stents
US11298442B2 (en) 2013-08-08 2022-04-12 Boston Scientific Scimed, Inc. Dissolvable or degradable adhesive polymer to prevent stent migration
CN113209365A (zh) * 2021-05-31 2021-08-06 福州大学 一种多功能封闭止血伤口敷料及其制备方法
CN113209365B (zh) * 2021-05-31 2022-04-01 福州大学 一种多功能封闭止血伤口敷料及其制备方法
CN114452447A (zh) * 2021-08-03 2022-05-10 南京工业大学 贻贝蛋白-聚氨基酸涂层及其制备方法和应用
CN114712332A (zh) * 2022-03-15 2022-07-08 陕西师范大学 一种改性水性材料及其制备方法和应用
CN114712332B (zh) * 2022-03-15 2024-01-30 陕西师范大学 一种改性水性材料及其制备方法和应用

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